TomoTherapy - Carpeta de Producto by deleccientifica

Verd a d e ra y ú n i c a ra d i ote ra pi a h e l i c o i d a l . L a te cn ol og í a m á s p re ci s a d e l m u n d o qu e a p l i ca a tod o t i p o d e tu m ores.

CONTENIDO CONTENIDO T O M O T H E R A P Y 5 ¿QUÉ ES EL SISTEMA TOMOTHERAPY?

D E L E C C I E N T Í F I C A 8 A B O C A D O S A L A I N N O VA C I Ó N

C O N S U LT O R Í A I N T E G R A L

APLICACIONES CLÍNICAS

S E R V I C I O T É C N I C O P O S V E N TA

¿POR QUÉ ELEGIRLO?

S O B R E A C C U R AY Y T O M O T H E R A P Y

P I L A R E S F U N D A M E N TA L E S

AMIGABLE CON EL USUARIO

P R E C I S I Ó N S I N C O M PA R A C I Ó N

VERDADERA EXACTITUD

COMPONENTES DEL SISTEMA

SISTEMA DE IMÁGENES

¿ Q U É P A C I E N T E S S E P U E D E N T R ATA R ?

C A R A C T E R Í S T I C A S D E L T R ATA M I E N T O

DISEÑO DEL BÚNKER

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ENTRENAMIENTO

BIBLIOGRAFÍA

C O M P A R AT I VA S 7 7 PUBLICACIONES CIENTÍFICAS

Esta carpeta fue generada por el equipo de consultores de DeLeC Científica. 2021. DeLeC Científica Uruguaya - Representante Regional Exclusivo Fco. García Cortina 2357 – Piso 1. Montevideo - Uruguay Tel: (+598) 2711 4466 DeLeC Científica Argentina – Agente Comercial Local Aráoz 821 -C1414DPQ - Buenos Aires – Argentina. Tel: (+54-11) 4775 5844 2

A lo largo de la historia, las patologías oncológicas han representado uno de los desafíos más importantes a los que se enfrenta la medicina y la industria asociada.

no tenían solución, y a la vez se integra a las instituciones con bajos requerimientos de instalación, aportando velocidad en los flujos de trabajo y seguridad para los profesionales que lo usan.

Con la premisa de controlar estas enfermedades con el mínimo impacto negativo sobre la calidad de vida de los pacientes, las instituciones han destinado cuantiosos recursos a la investigación y el tratamiento oncológico en todas las áreas clínicas involucradas: la cirugía, la quimioterapia y la radioterapia (RT).

TomoTherapy permite tratar tumores frecuentes o complejos con la misma seguridad, con un nivel de precisión sub-milimétrico y verificación en tiempo real para reducir al máximo los efectos sobre los órganos involucrados, en sesiones que no superan los quince minutos, algo impensado antes de la radioterapia helicoidal.

En el ámbito de la RT, donde la eficiencia, la exactitud y la precisión juegan un papel fundamental, se han logrado numerosos avances con el desarrollo de soluciones tecnológicas realmente innovadoras.

Es el equipo que cubre el mayor campo de trabajo gracias a su geometría helicoidal, lo que es fundamental para pacientes que ameriten irradiación de volúmenes tumorales extensos o tratamientos de irradiación corporal total (TBI).

En DeLeC Científica S.A., vamos de la mano de los avances del siglo XXI y nos preocupamos por seleccionar las tecnologías que destacan y encabezan estos avances con soluciones reales para los pacientes oncológicos: • TomoTherapy / Radixact: el único sistema para radioterapia y radiocirugía helicoidal. Aplica especialmente para el caso de metástasis y masas tumorales grandes. • CyberKnife: el único sistema de radiocirugía robótica y radioterapia. Aplica para masas tumorales pequeñas en cualquier parte del cuerpo (intra y extracraneal), especialmente aquellas ubicadas en órganos con movimiento. • RayStation: el mejor software de planificación de tratamientos que integra en una misma plataforma aceleradores de cualquier casa comercial; • Xoft: primer sistema de braquiterapia electrónica; • Liac HWL: sistema más eficiente para radioterapia intraoperatoria con electrones.

Los softwares de planificación de tratamientos y operación del equipo son intuitivos y de fácil manejo, aprovechan al máximo la fidelidad de la tecnología y minimizan los posibles errores humanos al garantizar flujos de trabajo rápidos y dinámicos.

TomoTherapy es la nueva concepción de terapias radiantes capaz de brindar soluciones personalizadas y efectivas contra el cáncer. A nivel clínico, permite tratar tumores y lesiones oncológicas que

Además, posee ventajas que aceleran la logística para las instituciones. Al ser un acelerador monoenergético (6MV) y poseer una barrera de protección contra la radiación en su interior, se minimizan los requerimientos del búnker, pudiendo incluso adecuarse a las instalaciones de las viejas bombas de cobalto. En caso de tener que construir uno nuevo, bastará con paredes de 1.07 metros de espesor (la mitad de cualquier acelerador lineal común), reduciendo los costos de construcción. Viene pre-comisionado de fábrica, lo que permite poner en marcha al equipo en 30 días. En DeLeC Científica S.A. estamos seguros que el TomoTherapy es el equipo más seguro, eficiente y versátil para la entrega de tratamientos de radioterapia externa en tumores grandes y pequeños. Es un paso hacia el futuro en la lucha contra el cáncer para la comunidad médica y científica, y nuestra recomendación más enfática en la decisión de brindar un servicio de radioterapia con el nivel más alto de excelencia.

MSc Miguel Yanez Director de Radioterapia y Radiocirugía DeLeC Científica

RADIOTERAPIA HELICOIDAL DE ALTA PRECISIÓN

¿Qué es el sistema TomoTherapy?

El sistema TomoTherapy es la primera y única plataforma para radioterapia helicoidal, que integra la planificación del tratamiento, la verificación de la posición del paciente, la administración de la dosis y el monitoreo del haz de radiación durante la entrega. Usa un revolucionario colimador multiláminas binario con el cual es posible modular la intensidad de un haz de radiación de entrega helicoidal, rotatorio y continuo. El haz es generado en un acelerador lineal instalado en un gantry de morfología anular, obteniendo altos índices de conformabilidad en el blanco, distribuciones de dosis homogéneas y altos gradientes dosimétricos, optimizando el rango terapéutico. El sistema proporciona imágenes volumétricas de TAC de las estructuras de interés inmediatamente antes del tratamiento, permitiendo en tiempo real verificar la posición del paciente, y con esto la localización del blanco y de los órganos en riesgo. También permite adaptar el tratamiento de radioterapia de acuerdo a las posibles modificaciones que ocurren durante el tiempo de tratamiento en la morfología, tamaño y movilidad del tumor. El sistema TomoTherapy es el resultado del perfeccionamiento de la radioterapia. Este equipo es fácil de instalar, de operar y permite a los responsables de los servicios de terapia radiante conseguir las mejores performances en tratamientos personalizados para todo tipo de tumores.

Hoy es posible ganarle al cáncer con las terapias personalizadas de TomoTherapy. 7

DeLeC Científica, abocados a la innovación

En DeLeC Científica hicimos de la innovación tecnológica el combustible para impulsar la modernización de los sistemas de salud y la calidad de los servicios médicos. Trabajamos acercando las innovaciones tecnológicas más destacadas del siglo XXI a los hospitales y clínicas de la región, desde la consultoría, la comercialización y el desarrollo de programas médicos integrales que permiten garantizar servicios médicos de excelencia. Nuestra firma comercializa la mayoría de sus productos en Argentina, Uruguay, Paraguay y Bolivia, y cuenta con representaciones que alcanzan Chile, Perú, Ecuador y Brasil.

Misión Nos hemos propuesto hacer foco en lo especial y proveer soluciones a problemas de los que nadie se ha ocupado. Por eso aportamos equipamiento y asesoramiento para hacer factibles y seguros los nuevos paradigmas en el ámbito de la salud, como son los tratamientos personalizados, con mayor seguridad y una experiencia más confortable para los pacientes. Nos interesan los procesos y sus resultados. Por eso trabajamos junto a nuestros partners desde el diseño de sus propuestas, con consultorías especializadas, asesoramiento y asistencia técnica oficial, garantizando la ejecución de proyectos exitosos.

Consultoría integral

Nuestra experiencia en el ámbito de la innovación tecnológica en salud nos dice que, tan importante como el equipamiento son las etapas de formación, la comprensión de la tecnología, el acompañamiento clínico, el asesoramiento y los objetivos que orientan la práctica. Por eso en DeLeC Científica acompañamos a las instituciones desde el desarrollo de los proyectos, el diseño de nuevas áreas o servicios de salud, el asesoramiento en la adquisición de nuevas tecnologías, el seguimiento clínico con especialistas en radioterapia, los requerimientos normativos y legales, la diagramación logística, el mantenimiento y el monitoreo del uso. Un asesoramiento adecuado es clave para:

Obtener planificaciones que permitan optimizar el tiempo de los proyectos,

Implementar know how para conseguir mejores resultados,

Aplicar estrategias para retorno de la inversión,

Visualizar un camino de crecimiento con fundamentos sólidos y desarrollo de valor.

Con el fin de asesorar, tomando como referencia los máximos estándares de calidad, los consultores de DeLeC nos actualizamos de acuerdo a los programas de formación de las firmas que representamos y participamos de forma activa en la agenda más relevante de la innovación tecnológica médica a nivel global.

Acompañamiento desde Aplicaciones Clínicas

DeLeC Científica se destaca por ser la única em-

Nuestro personal de Aplicaciones Clínicas brindará

presa capaz de proveer un servicio de aplicaciones

capacitación y entrenamiento a los equipos de salud,

clínicas completo, que va desde la etapa de consul-

con orientaciones prácticas y teóricas para aprove-

toría hasta la docencia post instalación de manera

char al máximo la potencialidad de la tecnología.

continua. Este equipo conformado por especialistas con una amplia experiencia clínica en radioterapia, capacitados por fábrica y con actualizaciones permanentes, asisten a las instituciones en el diseño de programas médicos de excelencia que mejoran de forma exponencial los flujos de trabajos asocia-

Con este programa de acompañamientos, brindamos a nuestros partners la seguridad de estar alineados con las mejores prácticas de cada especialidad, favoreciendo una mayor seguridad tanto para los usuarios como para los pacientes.

dos a la práctica de la radioterapia. De esta forma, las tecnologías seleccionadas se logran implementar con los mejores resultados, favoreciendo una práctica médica integral que seguramente superará los objetivos clínicos y económicos de los proyectos. El acompañamiento a nuestros clientes no conoce distancias. Implementamos plataformas, videoconferencias y aplicamos un cronograma de visitas para anticiparnos a las necesidades de consultas y actualización.

Servicio técnico especializado

Todos nuestros proyectos de consultoría están respaldados por la dirección de Servicio Técnico. El área se compone de ingenieros biomédicos y bio-ingenieros capacitados por las fábricas para brindar asistencia local de alta performance. Trabaje seguro con equipamiento único en el mundo, contando con un grupo de especialistas que le garantizará continuidad de servicio y respaldo los 365 días del año.

Ofrecemos un servicio técnico de alta performance, alineado tanto a las exigencias y estándares de las marcas con las que trabajamos, como a los requerimientos de nuestros clientes.

El equipo técnico asiste en la interpretación de los requerimientos previos (condiciones eléctricas, infraestructura, etc.), se ocupa de la instalación, cuando el equipo lo requiere, y luego monitorea el funcionamiento y el uso para garantizar el desempeño óptimo de la tecnología.

Nuestros ingenieros deben cumplir con un cronograma de formación y capacitación anual, en las casas matrices de las firmas que representamos. Por lo tanto, desde DeLeC Cientíífica ofrecemos una asistencia de instalación y posventa certificada por fábrica.

Servicio oficial de instalaciones

Staff

Ofrecemos el servicio de instalación oficial de los

• División de Radioterapia y Radiocirugía: Desarrolla proyec-

equipos de las firmas que representamos en Ar-

tos llave en mano para el tratamiento de tumores malignos y

gentina, Uruguay, Paraguay, Bolivia y Chile. Nues-

benignos, previendo todas las dimensiones vinculadas: consul-

tro servicio cumple con todos los procesos reco-

toría, docencia, comercialización, servicio de Aplicaciones Clí-

mendados por la fábrica.

nicas pos-venta completo. Brinda servicio docente a los usua-

Contar con el certificado y la habilitación de servicio

rios para asegurar su correcta utilización y las buenas prácticas.

La firma cuenta con seis áreas:

oficial garantiza a nuestros clientes seguridad y calidad a lo largo del proceso de instalación de los siste-

• División de Sistemas Médicos: Provee la mejor tecnología de

mas, contemplando los más altos estándares a nivel

punta para cubrir necesidades de equipamiento de diagnósti-

mundial. La formación constante en fábrica de nues-

co. Busca optimizar resultados clínicos y mejorar la calidad de

tros ingenieros se traslada en mejoras continuas en

la experiencia vivida por los pacientes.

los procesos de instalación. El Servicio Técnico de instalaciones combina la mejor tecnología disponible

• División de Simulación Clínica: Pone a disposición de la co-

en la actualidad, respaldo y experiencia.

munidad médica un catálogo de simuladores que abarca desde soluciones sencillas hasta las más completas que existen en el mercado. Esta versatilidad nos permite ofrecer proyectos a medida y escalables. • División de Ingeniería y Servicio Técnico: Lleva a cabo todas las acciones de logística necesarias para la importación de las distintas tecnologías. Asegura que el funcionamiento de los equipos instalados sea igual que el de origen, en fábrica. Controla y monitorea el funcionamiento de la base de instalada, con mantenimiento preventivo y correctivo, y actualización continua. • División de Comunicación y RSE: Genera contenidos para favorecer el conocimiento de las innovaciones tecnológicas que representamos. Asimismo, promovemos eventos de divulgación, demostraciones y acciones para conectar con nuestra audiencia. • División de Administración, Personal y Finanzas: Optimiza los resultados económicos de la empresa, cuidando que haya una distribución equitativa de los recursos entre los proveedores, clientes, personal, accionistas, bancos/inversores y el fisco. Su objetivo principal es velar por una gestión eficiente y ecuánime al momento de crear valor económico produciendo, al mismo tiempo, valor social.

Tecnología

Representamos exclusivamente equipos que son seguros y están debidamente certificados y aprobados por los organismos internacionales de control -FDA y CE- y también los nacionales -ANMAT y ARN-. Además, brindamos un soporte pre y post venta de excelencia para garantizar la funcionalidad una vez instalados. Nuestro diferencial es que no sólo proveemos equipos, sino que desarrollamos programas médicos de excelencia, acompañando al cliente desde la etapa embrionaria del proyecto hasta su optimización operativa. Trabajamos codo a codo con las instituciones, haciendo transferencia de tecnología desde el servicio técnico, el acompañamiento clínico, la comunicación y la consultoría integral. Así logramos que las inversiones en equipamiento, se conviertan en mejoras en la calidad de vida de los pacientes.

Nuestro lema es ganar cuando el cliente también gana, cumplir con lo prometido y hacerlo a tiempo.

Potenciamos desde la comunicación

En DeLeC no hablamos de clientes sino de partners. Nuestro modelo de innovación y comunicación nos vincula a todas las organizaciones e instituciones que integran la comunidad médica regional. En este marco, brindamos soporte de comunicación y marketing a nuestros parterns. Sabemos que toda innovación tecnológica, para ser capitalizada debidamente, requiere un trabajo de divulgación y comunicación. Por eso nuestro equipo en Argentina y Uruguay genera materiales atractivos de todos los sistemas y equipos que representamos. Desarrollamos eventos propios, workshops, webinars con finalidades formativas y de divulgación. Son abiertos y de fácil acceso. Potenciamos los proyectos a través de diferentes estrategias de comunicación:

•

Marketing digital

•

SEO y datos

•

Contenidos originales

• Videos

•

Ciclos temáticos

•

Eventos y conferencias

•

Proyectos con instituciones

Nuestros representados

A Subsidiary of Samsung Electronics Co. , Ltd

¿Por q ué e legirlo?

Sobre Accuray y TomoTherapy

Accuray es una compañía especializada en radio-on-

con el fin de fundar una compañía de excelencia en te-

cología, que desarrolla, fabrica y ofrece sistemas de

rapia radiante. Durante los años 2011 y 2016 Accuray

innovación tecnológica que proporcionan las mejores

se dedicó a perfeccionar el sistema TomoTherapy de

soluciones de tratamiento para pacientes oncológi-

manera de incorporar la mejor tecnología en sus equi-

cos en el ámbito de la radioterapia y de la radiocirugía.

pos de terapia radiante.

A partir de 1997, la empresa TomoTherapy Inc. en Wis-

El sistema TomoTherapy HDA fue diseñado para per-

consin, emprendió el desarrollo de un sistema que com-

mitir a los médicos brindar de manera más eficien-

bina la Radioterapia de Intensidad Modulada (IMRT)

te y efectiva tratamientos de radiación mucho más

con la capacidad de obtener imágenes de tomografía

precisos a más pacientes con una amplia variedad de

computada a partir de Megavoltaje (MVCT), con el fin

cánceres, de los más comunes hasta los más comple-

de garantizar una precisión inigualable en cada fracción

jos. El gantry de TomoTherapy combina imágenes de

del tratamiento. A mediados de 2003 fueron aproba-

Tomografía Computada con IMRT con el fin de pro-

dos por la FDA y CE, y vendieron más de 300 unidades

porcionar tratamientos de radiación más sofisticados,

en todo el mundo. A principios del 2011 Accuray, líder

con mayor velocidad y precisión, reduciendo la expo-

en el campo de radiocirugía, adquirió TomoTherapy Inc.

sición a la radiación del tejido sano circundante.

Pilares fundamentales INTEGRACIÓN COMPLETA Ofrece un proceso de tratamiento totalmente integrado para la terapia de cáncer. Incorpora un software muy fácil de usar para la planificación del tratamiento, control de calidad, configuración y administración del tratamiento. Debido a que toda la información de cada paciente y los registros de entrega de dosis se almacenan en un solo lugar, el riesgo de errores de transferencia de datos se reduce al mínimo.

LÍDER EN LA INDUSTRIA DE PRECISIÓN Brinda una modalidad de tratamiento helicoidal real (continua 360°) que garantiza una precisión submilimétrica en la entrega de tratamiento a través del sistema único de colimación multi-lámina que divide el haz de tratamiento en miles de beamlets dirigidos al tumor para optimizar la dosis total al mismo protegiendo al máximo los tejidos sanos

PRECISIÓN VERDADERA El sistema TomoTherapy/Radixact viene integrado con la tecnología CTrue™, la cual permite a los médicos adquirir imágenes TC todos los días para cada paciente. Éstas últimas desempeñan un rol fundamental en el posicionamiento del paciente, en el análisis dosimétrico y en la modificación del tratamiento en cualquier momento de la terapia.

CTRUE™ Permite a los médicos comparar el volumen tumoral original a partir de imágenes precisas y reconstrucciones en 3D. Luego, pueden determinar rápidamente si se requieren ajustes para asegurarse de que la dosis prescripta en el tumor se administre con precisión durante todo el tratamiento.

Pilares fundamentales

POTENTE SISTEMA DE PLANIFICACIÓN El software PreciseART™ permite lograr una verdadera radioterapia adaptativa. Mediante el uso de imágenes en 3D para el posicionamiento del paciente todos los días, los médicos son capaces de visualizar la dosis que realmente se entregará al paciente ese día.

ADMINISTRACIÓN DE LA DOSIS ADAPTABLE Permite el análisis cuantitativo, dosimétrico y la modificación del tratamiento de un paciente, durante el curso del mismo, ajustándolo a los cambios en la anatomía y el tamaño del tumor. Como resultado, los pacientes pueden estar seguros de que están recibiendo la dosis prescrita.

ASEGURAMIENTO DE LA CALIDAD INTEGRADO La aplicación TomoQuality Assurance (TQA™) simplifica la recopilación y el análisis de la información del rendimiento del sistema, ofrece información de tendencias y de los parámetros que permitirán a los físicos controlar el rendimiento del equipo.

TRATAMIENTOS EFICACES Brinda dos modalidades de tratamiento: TomoDirect (opción de entrega no rotativa), la cual se basa en ángulos discretos, con las capacidades de la radioterapia 3D conformada; TomoHelical, que permite la rotación alrededor del cuerpo y multiplica la cantidad de posiciones del gantry.

Planifique el tratamiento desde un software poderoso e intuitivo. 21

Amigable con el usuario

Con sus equipos de radioterapia y radiocirugía, Accuray logró un cambio fundamental en las salas de terapia radiante: hacer las cosas mejor, en menos tiempo. En este paso, el sistema de planificación Presicion cumple un rol determinante: facilita la actividad de los equipos interdisciplinarios, optimiza los planes de tratamiento y reduce errores. El sistema de planificación incorpora: 1. Software de planificación del tratamiento fácil de utilizar. Los controles de calidad, el posicionamiento del paciente y la administración del tratamiento se efectúan con una única base de datos centralizada. El fácil uso del software de planificación permite al personal de la unidad tratar a más pacientes y dedicarle mayor tiempo a cada uno de ellos. Las capacidades clave incluyen fusión de imágenes multimodalidad con deformación patentada, un conjunto de opciones de contorneado, y herramientas de comparación y suma del plan. 2. La planificación de los tratamientos está centralizada en un solo lugar, el iDMs. Es posible conectar múltiples sistemas de entrega de tratamiento Accuray y administrar toda la planificación del tratamiento desde un único punto de control.

CONFIDENCE IN CONNECTIVITY

Customer Backup

RaySta n® System

™ Accuray Precision Treatment Planning System

Gateway

Internet / Accuray Service

iDMS ™

Treatment Planning CT

Data Management System Oncology Informa on System

Delivery Analysis

® TomoTherapy Treatment Delivery System

Radixact Treatment Delivery System

CyberKnife® Treatment Delivery System

™

DATA ENCRYPTION

SECURE FIREWALL

Precisión sin comparación

Los aceleradores lineales de otras casa comerciales no pueden realizar una radioterapia helcioidal, limitando sus opciones de tratamiento a un tamaño de campo cuadrado, haciendo que tratamientos extensos sean divididos en varios isocentros para cubrir la región a tratar y poniendo en riesgo la efectividad del tratamiento mediante flujos de trabajos complicados. El sistema de tratamiento TomoTherapy emite radiación continua desde todos los ángulos alrededor del paciente, implementando una innovación en los MLC de forma binaria creada específicamente para brindar un mejor tratamiento de IMRT (Zaleska et al. 2017; Hsu et al. 2017). El modo TomoHelical permite la irradiación continua alrededor de los 360º del paciente a medida que la camilla avanza hacia dentro del equipo, lo que permite entregar un tratamiento en forma helicoidal único. Con esta modalidad se pueden tratar volúmenes tumorales muy grandes en una única y sencilla configuración, posibilitando tratar cualquier región del paciente dentro de un volumen cilíndrico de 80 cm de diámetro transversal y 135 cm de largo. Otro modo de tratamiento es el TomoDirect™ que nos permite realizar, a través de diferentes ángulos de gantry fijos, una entrega de dosis de forma más directa. En ambos casos, los volúmenes reales de tratamiento son variables dependiendo de la posición de la camilla y la configuración del ancho de campo (Saw et al. 2018). La precisión del tratamiento se logra gracias a las decenas de miles de beamlets que surgen como resultado de una optimización del plan dirigiendo el 100% de la dosis al tumor. Cabe destacar que un beamlet corresponde a la radiación emitida a través de una hoja abierta del sistema de MLC patentado con el acelerador en un ángulo dado y durante una determinada rotación.

Entrega tratamiento de forma helicoidal abarcando un campo de 135 cm.

Verdadera exactitud

El sistema de tratamiento viene integrado con la tec-

rador lineal, pero con una energía de 3.5 MV (MVCT),

nología CTrue™ que permite a los médicos adquirir

entregando dosis adicional de solamente entre 1 y

imágenes de TC todos los días para cada paciente.

2 cGy (Ding et al. 2018). En cada fracción del trata-

Éstas pueden ser utilizadas con fines de posiciona-

miento, el equipo brinda la posibilidad de visualizar

miento, permitiendo un análisis cuantitativo, dosi-

la anatomía en los planos axiales, coronales, sagita-

métrico y la modificación del tratamiento en cual-

les y correlacionarlos con las imágenes adquiridas

quier momento durante el curso del mismo (Ramsey

mediante un tomógrafo convencional. Mediante el

et al. 2006; Kim et al. 2018).

registro automatizado de imágenes se pueden deter-

La tomografía computada es una herramienta fundamental en el diagnóstico del cáncer, así como en la delimitación de objetivos, los órganos de riesgo y la

minar rápidamente los ajustes necesarios y realizar de manera precisa el corrimiento on-line de la camilla para ubicarla en la posición óptima del tratamiento.

generación de la planificación del tratamiento. Con

La tecnología MVCT tiene como resultado una uni-

este sistema el papel de la TC se amplía aún más.

formidad igual a la de una tomografía convencional (kVCT) manteniendo una consistencia en los valores de las unidades Hounsfield obteniendo mapas de densidad precisos. Un haz de MV permite proporcionar imágenes de TC confiables independientemente del tamaño y forma del paciente, e incluso con la presencia de materiales de alto número atómico, los cuales producen artefactos que distorsionan las imágenes. Otra ventaja es que la dosis proporcionada para adquirir la imagen es baja. Cabe aclarar que las imágenes no son com-

Comparación de imágenes previo al tratamiento.

patibles en calidad con las de kVCT, pero pueden ser utilizadas para el cálculo de dosis teniendo en cuenta

Para el posicionamiento de los pacientes las imáge-

las heterogeneidades (Hu et al. 2017). Esto abre la

nes de CTrue™ desempeñan un papel fundamental.

puerta a la replanificación dosimétrica y por ende a la

Ellas son tomografías realizadas con el mismo acele-

planificación adaptativa.

El objetivo central es mostrar los efectos dosimétricos que se producen debido a los desajustes en el posicionamiento y los cambios de la anatomía. Existen diversos factores que deforman las estructuras anatómicas antes de llevar a cabo el tratamiento, como son, la pérdida de peso, la contención de líquidos, el movimiento de la respiración, entre otros. El software PreciseART™ permite hacer un seguimiento de este tipo de cambios. La Opción de Terapia Radiante PreciseART amplía las posibilidades de radioterapia adaptativa, brindando un nivel completamente nuevo de integración de sistemas y automatización del flujo de trabajo. PreciseART les permite a los médicos monitorear a cada paciente y adaptar de manera eficiente los planes, ayudando a ofrecer tratamientos más precisos a más pacientes.

El procesamiento automatizado de imágenes diarias agiliza el flujo de trabajo de los médicos, a la vez que aumenta la seguridad del paciente.

El sistema posee una única base de datos que alma-

• Deforma y acumula dosis diarias en la planificación

cena la información de la planificación y la entrega de

de tratamiento CT.

dosis, lo que hace sencillo identificar los puntos "ca-

• Genera informes definidos por el usuario.

lientes" y "fríos", haciendo más fácil la actualización

• Marca fracciones con estructura(s) que exceden la

de la planificación.

dosis definida por el usuario o la tolerancia al volumen

La automatización de procesos permite a los médicos supervisar a todos los pacientes e identificar de inmediato a los candidatos para volver a planificar.

de dosis. • Revisión de la dosis diaria y los registros, la dosis acumulada, las diferencias de dosis y los datos de tendencias. • Compara fracciones y ve contornos originales y de-

Características:

formados en una imagen fusionada diariamente.

• Deforma los VOI de planificación en la imagen diaria.

• Evalúa la deformación con herramientas de control

• Calcula la dosis en la imagen diaria.

de calidad incorporadas.

Imagen de planificación de tratamiento para TomoTherapy.

Comp one ntes del sistem a

Diagrama de TomoTherapy mostrando su isocentro

Acelerador lineal Opera con fotones de 6MV generados en el Linac integrado en el gantry. Opuestamente al Linac se encuentran los detectores de Xenón que facilitan la dosimetría y permiten la adquisición de imágenes TC. Inmediatamente después del sistema detector se encuentra el Beam Stop que detiene la radiación directa y dispersa en un 50% proveyendo un auto-blindaje que disminuye los requerimientos de construcción del bunker.

Integrated Shielding Linear Accelerator (Linac)

Target Primary Collimator

Jaw Collimator

Vista lateral de los componentes del sistema de colimación.

Gantry Posee la capacidad de generar un movimiento con-

Características:

tinuo, rotatorio, del acelerador lineal en 360° mien-

• La velocidad de rotación para el tratamiento va

tras la camilla de tratamiento avanza hacia dentro del

desde 1 a 5.08 RPM y para adquisición de imágenes

Gantry produciendo una entrega de dosis de manera

es de 6 RPM.

helicoidal. Reproduce los tratamientos con una pre-

• La rotación completa de gantry se divide en 51 pro-

cisión de décimas de milímetros optimizando la dosi-

yecciones, donde cada una cubre un segmento

metría y la planificación. Tanto para la TC como para

de ≈ 7º con apertura máxima del colimador.

el tratamiento existe una conjunción entre el movi-

• Si existiese un error en la rotación al realizar la fu-

miento de mesa y el gantry (PITCH), el cual puede ser

sión de la imagen de MVCT con la TAC de referencia,

modificado según la patología y la sección a irradiar

éste se corrige variando gradualmente el punto de

(van Gestel et al. 2015).

inicio de irradiación a través del gantry.

La radioterapia helicoidal permite acortar las terapias y entregar tratamiento en un promedio de doce minutos, incluso para los casos más complejos.

Sistema de colimación Multi-Leaf Es un sistema multi-lámina acoplado al sistema de colimación que se mueve junto con el acelerador lineal, generando un haz modulado rotatorio. Junto a este sistema se encuentra el sistema de colimación primario compuesto por mandíbulas dinámicas que permiten la obtención de campos rectangulares de tamaños 1x40. 2,5x40 y 5x50 cm a nivel del isocentro.

Está compuesto por 64 láminas que se interponen

A diferencia de los aceleradores lineales convencio-

en el haz de radiación mediante un sistema binario

nales, donde los movimientos de MLC son realizados

de apertura/cierre definiendo pequeños haces indi-

mediante motores, el TomoTherapy es el único equi-

viduales. Las dimensiones de los haces son mínimas,

po del mercado que ofrece un movimiento neumático

en el caso más pequeño de 6x10 mm2, correspon-

del MLC de elevada precisión, velocidad y exactitud.

diendo a la anchura de la lámina y a la apertura mínima del colimador. La velocidad de apertura/cierre de las láminas es de aproximadamente 250 cm/s.

Sistema de obtención de imágenes El TomoTherapy permite obtener imágenes de TC

El sistema de detección se encuentra en la salida del

para la verificación de la posición, forma del tumor y

haz de radiación que genera una imagen CT con foto-

tejido sano adyacente con respecto a la TC de planifi-

nes de 3,5 MV. El sistema de adquisición de imáge-

cación. Gracias a ello, es posible disminuir al máximo

nes tiene una geometría de haz de abanico helicoidal

errores en el posicionamiento del paciente en cada

como el de una tomografía de diagnóstico denomi-

una de las sesiones, aumentando el control tumoral y

nada MVCT.

por ende la vida del paciente.

Características de las imágenes MVCT: • La uniformidad es comparable con la CT de diagnóstico mientras que el ruido es mayor. • Las unidades Hounsfield MVCT son consistentes, adecuados para el cálculo dosimétrico. • La resolución espacial para una imagen de 512x512 es de aproximadamente 1.5 mm • La dosis es de aproximadamente 1.1 cGy para un ancho de slice de 5 mm y pitch de 1. La dosis decrece con la disminución del pitch. • La energía es de 3.5 MV, dado que se genera mediante un spot mucho más pequeño con un mejoramiento en la penumbra y la resolución de contraste. Cabe destacar que la calidad de la imagen es aceptable para la alineación del paciente y para la delineación y marcación de tejidos blandos.

Cone Beam CT vs MVCT El sistema de imágenes del TomoTherapy es superior en ciertos aspectos a los sistemas convencionales. A continuación, ofrecemos dos imágenes comparativas que ilustran la calidad de imagen del sistema MVCT de TomoTherapy. Tomografía (CBCT)

Tomografía (MVCT)

En las siguientes figuras podemos observar algunos cortes de la secuencia de tomografías para un estudio de próstata en la cual el paciente posee prótesis. También es posible observar su correspondiente reconstrucción en 3D.

El sistema permite comparar las tomografías de planificación, realizada en un tomógrafo convencional de kilovoltaje, y la tomografía de verificación MVCT realizada directamente en el sistema TomoTherapy de manera de asegurar que el tratamiento sea efectivo. La tomografía de megavoltaje permite obtener una imagen clara bien definida aún en los casos donde los artefactos por piezas metálicas complican la visualización de la imagen.

Tomografía (CT)

TomoTherapy (MVCT)

El planificador nos permite realizar una correlación manual o automática entre las imágenes de MVCT y de planificación para los planos transversales, sagitales y coronales. Una vez conseguida la óptima alineación de todas las proyecciones, el planificador obtiene las correcciones de los parámetros que se deben modificar en la camilla. Luego de eso, la misma se desplazará, de manera on-line, para ubicarse en las coordenadas precisas.

Dosimetría La innovación que propone TomoTherapy es realizar una dosimetría antes del tratamiento sobre las imágenes de MVCT o kVCT, obteniendo grandes beneficios para el aumento del control tumoral. En las siguientes

figuras se pueden visualizar diferentes tipos de patologías y sus correspondientes dosimetrías para determinar, de manera precisa, si las curvas de isodosis abarcan completamente las estructuras blanco y si se minimiza la dosis para los órganos de riesgo.

Dosimetría en Planificación

Dosimetría en Verificación

Capacite a su equipo con los flujos de trabajo y los programas de tratamientos con radioterapia más adaptables del mercado. Precision permite centralizar la actividad de todos los sistemas de terapias radiantes de Accuray.

AUMENTA LA EFICIENCIA DE LA PLANIFICACIÓN Genere y adapte planes de tratamiento personalizados y precisos en menos tiempo.

MEJORA LOS RESULTADOS DEL PACIENTE MEJORA LA SATISFACCIÓN DEL PERSONAL Automatice los flujos de trabajo y proporcione herramientas de planificación de tratamientos de última generación.

Ofrezca planes de tratamiento más personalizados y precisos para más pacientes.

Planifique para todos los tipos de casos Sistemas Radixact y TomoTherapy Entrega de tratamiento TomoHelical Entrega de tratamiento TomoDirect 3DCRT planificado hacia adelante

Sistema CyberKnife SRS intracraneal sin marco Seguimiento pulmonar sin fiduciarios con compensación dinámica de movimiento SBRT SRT IMRT

Sistema de planificación El sistema de planificación Precision diseñado por Accuray específicamente para su sistema de terapia radiante, es la herramienta que fortalece al equipo de trabajo con potencia de planificación y flujo de trabajo.

Es un sistema de planificación que incluye capacidades de registro y fusión de imágenes de diferentes tipos, herramientas de contorneo de estructuras avanzadas, opciones de comparación, suma y verificación de planes de tratamiento para asegurar la mejor optimización de la dosis en la enfermedad restringiendo al máximo la dosis recibida en los órganos a riesgo.

Modalidades de tratamiento a. TomoDirect

b. TomoHelical

El sistema ofrece una modalidad de tratamiento

El modo de administración TomoHelical proporciona

con gantry fijo.

la entrega de tratamiento IMRT en un patrón helicoi-

El modo de entrega TomoDirect proporciona tratamiento 3DCRT a través de un modo de entrega no giratorio de ángulo discreto. TomoDirect permite la creación de planes de tratamiento que incluyen entre 2 y 12 ángulos. Durante la administración del tratamiento, los haces se administran secuencialmente con la camilla pasando a través del gantry a una velocidad adecuada

dal continuo (360°). El modo TomoHelical es adecuado para la mayoría de situaciones clínicas, donde la entrega rotacional y la modulación del haz mejoran la conformación y uniformidad de la dosis. El usuario puede crear un plan de tratamiento donde puede definir los objetivos y las restricciones de dosis para las estructuras blanco y de riesgo, el nivel de modulación para el plan, así como el de fraccionamiento.

para cada haz. Los modos de mandíbula fija y opcionalmente el de mandíbula dinámica (TomoEDGE) están disponibles para TomoDirect. Con TomoEDGE, el ancho del campo varía durante la entrega para disminuir el ancho del gradiente de dosis fuera del objetivo.

TomoDirect Entrega el mejor tratamiento modulado para cáncer de mama desde ángulos fijos.

Durante la administración del tratamiento, el acelera-

tratamientos más cortos que la mayoría de los demás

dor lineal completa múltiples rotaciones de 360 gra-

sistemas de tratamiento de radiación, y proporciona

dos alrededor del paciente, mientras que la camilla

distribuciones de dosis uniformes y altamente con-

pasa a través del orificio central del gantry. La admi-

formadas, al tiempo que minimiza la dosis a las es-

nistración continua de dosis altas permite tiempos de

tructuras normales circundantes.

TomoHelical Se pueden tratar objetivos de hasta 135 cm de longitud, sin necesidad de reposicionar al paciente y sin unión de campo.

¿Q ué p a cie ntes se pueden tra ta r ?

La radioterapia helicoidal que ofrecen en igual calidad

Debido a la posibilidad de tratar blancos de hasta una

TomoTherapy y su nueva configuración, Tomotherapy,

longitud de 135 cm. con Tomotherapy, el problema

es la tecnología más avanzada y confiable para el tra-

de las uniones de campo se reduce y, por lo tanto, se

tamiento del cáncer haciendo uso de las radiaciones

evita la subdosificación por brechas en los campos o

ionizantes. La diversidad de casos que se pueden tra-

la sobredosis debido a la superposición de estos. Esta

tar con este sistema es tan amplia que prácticamente

capacidad permite desarrollar planificaciones ópti-

ninguna lesión oncológica está fuera del alcance de

mas para casos poco frecuentes como el Total Skin,

tratamiento usando el TomoTherapy. Esto involucra

Meduloblastomas o TBI.

desde los casos más simples hasta los más complicados, todos bajo la misma estructura de flujo de trabajo que hace que la experiencia del paciente sea más cómoda al tener unos tiempos de tratamiento sumamente bajos. En este capítulo se presentan consideraciones sobre las capacidades de ambos equipos para el tratamiento de todo tipo de tumores. Versatilidad y precisión en todo el cuerpo Tomotherapy ha demostrado ser el sistema más versátil entre los aceleradores modernos. Se puede emplear para tratar tumores benignos o malignos en todas las localizaciones, como lo demuestra la literatura existente. Y aún más. Este sistema de administración de trata-

Su capacidad de entrega personalizada en sincronía con el movimiento del objetivo para cada tratamiento logra adaptar la posición del haz a la ubicación del tumor de manera precisa y exacta en todo momento durante la administración del tratamiento. Esto permite entregar una dosis continua e ininterrumpida con márgenes estrechos y gradientes de dosis pronunciados, así los médicos tienen la libertad de elegir el esquema de fraccionamiento que mejor se adapte a las necesidades clínicas de sus pacientes, sabiendo que la eficacia y la eficiencia de su tratamiento se mantendrán sin obstáculos. Radioterapia helicoidal en la contención del COVID

mientos aumenta las indicaciones de radioterapia pre-

La radioterapia helicoidal se está utilizando en el

cisa para una amplia variedad de pacientes oncológicos

marco de las terapias para enfrentar el COVID-19

como ningún otro sistema disponible en el mercado.

con resultados promisorios y fundamentales en el

Gracias a su diseño y características únicas proporciona una flexibilidad sin precedentes, favorable para un gran número de aplicaciones. Radioterapia para lesiones extensas La tomoterapia es especialmente adecuada para la irradiación de volúmenes extensos en un solo procedimiento de irradiación, como, por ejemplo: • irradiación craneoespinal, • volúmenes linfáticos de cabeza y cuello, • cáncer de mama y sarcomas, • linfomas, • leucemias.

marco de la contención de la pandemia. Aunque la mayoría de los pacientes con COVID-19 son asintomáticos, pueden ocurrir complicaciones como neumonía grave, insuficiencia respiratoria o síndrome de dificultad respiratoria aguda, que a menudo conducen a resultados fatales para los pacientes. La mayoría de las veces, los pacientes con dichas complicaciones requieren el ingreso en la unidad de cuidados intensivos y el apoyo de un ventilador mecánico (VMI), servicios que por su especificidad y recursos son muy limitados. Como demuestra el estudio de Elena Moreno-Olmedo et al., publicado en 2020, la aplicación de muy bajas dosis (ultra-LDRT)

en pacientes con COVID-19 podría desempeñar un papel en la reducción de la respuesta inflamatoria pulmonar, reducir el riesgo de requerir VMI y aliviar los síntomas potencialmente mortales, lo que ayuda a reducir la mortalidad sin secuelas significativas a largo plazo.

Eficacia probada La investigación clínica respalda el uso de la tecnología TomoTherapy para el tratamiento de tumores cerebrales. A continuación, se enumeran los estudios clave que respaldan el uso de la tecnología. Para lesiones metastásicas

CÁNCER DE CEREBRO

Un análisis retrospectivo evaluó el uso de radiocirugía

Los tumores cerebrales pueden afectar diferentes

helicoidal como tratamiento exclusivo para pacientes

sentidos y / o memoria según su ubicación. Por eso,

con una y tres metástasis cerebrales. El estudio encon-

cuando es necesario tratar los tejidos y estructuras

tró que el tratamiento no invasivo fue muy bien to-

complejos, delicados y vitales del cerebro, la preci-

lerado y proporciona resultados clínicos alentadores.1

sión es importante.

estereotáctica (SRS) administrada con TomoTherapy

Un estudio retrospectivo de pacientes con metásta-

Los avances tecnológicos de la actualidad brindan

sis cerebrales grandes que no se pudieron extirpar

mejores opciones para las personas diagnosticadas

quirúrgicamente encontró que la radioterapia este-

con tumores cerebrales, lo que ayuda a garantizar

reotáctica hipofraccionada (SRT) administrada me-

que reciban el tratamiento más eficaz para su afec-

diante tomoterapia helicoidal “puede considerarse

ción médica particular. La radioterapia puede ser una

un tratamiento seguro para metástasis cerebrales

opción de tratamiento y puede usarse para tratar los

mayores de 2 cm dada la baja tasa de radionecrosis

dos tipos principales de tumores cerebrales:

asociada con esta método.”2

• Tumores cerebrales primarios: tumores que co-

Un estudio prospectivo evaluó el uso de SRT admi-

mienzan en el cerebro.

nistrado con tomoterapia helicoidal en cuatro se-

• Tumores cerebrales metastásicos o secundarios: tumores que comienzan en otra parte del cuerpo y luego se diseminan al cerebro.

siones para tratar metástasis únicas o múltiples. Los investigadores del estudio encontraron que el protocolo de tratamiento resultó en un excelente control del tumor con una toxicidad mínima.3

El sistema Tomotherapy es el único equipo en el mundo capaz de administrar radiación helicoidal, entregando el 100% de la dosis al tumor protegiendo al máximo las estructuras sanas. En caso de tratar múltiples lesiones cerebrales, el Tomotherapy® es capaz de restringir la dosis que recibe el cerebro sano disminuyendo la toxicidad por radiación. Además, la verificación diaria de la posición del paciente a través de la imagen TC permite garantizar la precisión del tratamiento.

Para tumores primarios: Múltiples estudios que evalúan la viabilidad del uso de la tomoterapia helicoidal para la irradiación del eje

cabeza y cuello proporcionando una alternativa eficaz cuando la cirugía no es posible o cuando el tumor no se puede extirpar por completo.

craneoespinal (meduloblastomas) han demostrado el interés de los médicos por esta técnica y sus beneficios en el tratamiento de este tipo de tumores.4, 5, 6 Un estudio comparó los planes de tratamiento desarrollados para la tomoterapia helicoidal y los sistemas de radioterapia convencional para tratar a pacientes con glioblastoma multiforme (GM) cuyos tumores se encontraban cerca de órganos críticos. Los autores concluyeron que “los planes de tomoterapia eran superiores a los planes de aceleradores lineales desde el punto de vista de la conservación de órganos en riesgo”.8 Por último, un estudio de planificación del tratamiento que evaluó la tomoterapia helicoidal, IMRT y 3D-CRT, mostró que, para los pacientes con glioblastoma multiforme, la tomoterapia helicoidal proporcionó una mejor cobertura del objetivo que la IMRT y mejoró la preservación de los órganos en riesgo en comparación con la IMRT y la 3D-CRT.⁹

CÁNCER DE CABEZA Y CUELLO Los cánceres de cabeza y cuello pueden afectar la

Un estudio de una sola institución de 72 pacientes con varias etapas de carcinoma nasofaríngeo (NPC) tratados con el método de administración TomoHelical encontró que la tasa de control local de cinco años fue del 97 por ciento, lo que demuestra un excelente control de la enfermedad a largo plazo. El estudio también mostró que los tratamientos con TomoHelical produjeron una toxicidad aguda y tardía generalmente leve.⁹

capacidad en los pacientes para comunicarse y co-

Otro estudio prospectivo multiinstitucional evaluó los

mer, causar dolor y afectar negativamente su bien-

beneficios clínicos de la IMRT administrada con el modo

estar emocional. Por eso, cuando es necesario tra-

TomoHelical en comparación con la terapia de arco vo-

tar tumores de la cabeza y el cuello, la precisión es

lumétrico modulado (VMAT) para 166 pacientes con

importante. El sistema Tomotherapy proporciona

cáncer de cabeza y cuello. La tasa de control local y la

una opción no quirúrgica diseñada para maximizar

tasa de supervivencia específica del cáncer fueron sig-

la radiación administrada al tumor mientras minimi-

nificativamente mejores en el grupo de pacientes con

za la dosis a los tejidos sanos, como los del cerebro,

tomoterapia que en el grupo de pacientes con VMAT.

la médula espinal, las glándulas salivales y paróti-

El tratamiento con TomoHelical también permitió la ad-

das, protegiendo las funciones relacionadas y pre-

ministración de dosis de radiación significativamente

servando su calidad de vida. Tomotherapy se puede

reducidas fuera del tumor, lo que condujo a una mejor

utilizar para tratar todo el espectro de tumores de

función salival que con VMAT.10

CÁNCER DE MAMA El sistema Tomotherapy está diseñado para ayudar a mejorar los resultados clínicos, mientras se minimiza el riesgo de efectos secundarios, para mejorar la calidad de vida de los pacientes, tanto durante el tratamiento como después de este. Sus dos modos de administración de tratamiento, TomoHelical y TomoDirect, ofrecen ventajas únicas en el tratamiento del cáncer de mama, incluida la capacidad de administrar una dosis de radiación precisa a cualquier tumor o lecho tumoral, durante cada sesión de tratamiento, mientras minimiza la dosis a los órganos y tejidos sanos cercanos. Esto es especialmente importante para las mujeres diagnosticadas con cáncer en la mama izquierda, donde el tumor puede estar cerca de órganos críticos como el corazón.

Un estudio realizado utilizando la modalidad TomoDirect demostró una administración uniforme de la dosis de radiación para toda la mama, con una dosis mínima a los órganos en riesgo cercanos. Los pacientes experimentaron una toxicidad leve y ninguna recidiva local en un seguimiento medio de 12 meses. La estética (preservación de la apariencia normal de la mama) fue buena / excelente en el 91 por ciento de los pacientes tratados.17 De forma similar, el análisis de 30 pacientes que usaron TomoHelical para la irradiación del cáncer de mama en estadio III encontró que los tratamientos se toleraron muy bien, con efectos secundarios agudos o moderadamente tardíos mínimos. Las pruebas cardíacas y respiratorias no mostraron evidencia de anomalías significativas relacionadas con el tratamiento. No se registró ninguna recidiva local del cáncer al finalizar el estudio.18 Otro estudio retrospectivo en un mismo centro con 136 pacientes con cáncer de mama invasivo encontró que la radioterapia hipofraccionada administrada con TomoTherapy fue muy bien tolerada con toxicidades agudas y tardías mínimas. Además, esta modalidad de tratamiento proporcionó una excelente supervivencia libre de falla locorregional a tres años, lo que significa que no hubo recurrencia local o regional o progresión del tumor, o muerte por cáncer de mama, tres años después del tratamiento.19

La opción más precisa para tratar el cáncer, protegiendo el tejido sano El sistema Tomotherapy se puede utilizar para tratar el espectro completo de cánceres de mama, desde tumores de rutina hasta tumores complejos, aquellos ubicados en áreas de difícil acceso y Tumores recurrentes. Varios estudios realizados utilizando radioterapia helicoidal han mostrado buenos resultados en el tratamiento de esta patología.

CÁNCER DE ESÓFAGO El sistema Tomotherapy permite la administración precisa de IG-IMRT, un tipo avanzado de IMRT, para el tratamiento del cáncer de esófago en varias etapas, incluida la enfermedad recurrente. El uso de IG-IMRT es una solución efectiva para esta enfermedad tan difícil de tratar con cualquier otra tera-

Otro estudio que evaluó la quimiorradioterapia concurrente basada en IMRT (CCRT) y la CCRT basada en radioterapia conformada 3D en pacientes diagnosticados con carcinoma de células escamosas de esófago torácico avanzado (estadio IIIA-IIIC) encontró que la CCRT basada en IMRT resultó en tasas de supervivencia más altas.22

pia, porque cuando se detecta se suele presentar en un estadio avanzado.

CÁNCER DE PULMÓN Uno de los mayores desafíos en el tratamiento del cáncer de pulmón sigue siendo tratar eficazmente la lesión, al tiempo que se minimiza la dosis a los numerosos tejidos sensibles y órganos vitales que rodean los pulmones.

Un tratamiento clínicamente probado para el cáncer de esófago Un estudio, desarollado en una sola institución, encontró que la supervivencia general mejoró significativamente con el tratamiento de IMRT. Ese estudio comparó 1) IMRT y quimioterapia con radioterapia conformada 3D y 2) quimioterapia en pacientes con cáncer de esófago localmente avanzado.20

La radioterapia helicoidal proporciona la flexibilidad para adaptar la radioterapia a la anatomía de cualquier paciente con cáncer de pulmón. TomoTherapy

Un estudio retrospectivo que evaluó una pequeña

es la opción no quirúrgica para el tratamiento del

cantidad de pacientes con cáncer de esófago local-

cáncer de pulmón diseñada para maximizar la radia-

mente avanzado encontró que la IMRT y la IG-IMRT

ción administrada al tumor y minimizar la dosis a los

pueden proporcionar dosis curativas de radiación

tejidos sanos. Esta precisión ayuda a mejorar la efica-

con niveles aceptables de toxicidad, incluso en per-

cia del tratamiento del cáncer, al tiempo que reduce

sonas con afecciones preexistentes.21

el riesgo de efectos secundarios.

Tomotherapy cuenta con la capacidad de rastrear la

Cáncer de pulmón de células no pequeñas en esta-

posición de los tumores en movimiento en tiempo

dio temprano (CPCNP): La SBRT de pulmón con la

real a través del sistema Synchrony.

tecnología TomoTherapy ofrece un buen control local

Cuando el paciente respira, el torso se mueve. Esto significa que un tumor de pulmón, o cualquier objetivo dentro o cerca de los pulmones, se moverá continuamente durante la administración del tratamiento. A diferencia de cualquier otro dispositivo de radiación convencional, el sistema Tomotherapy con Synchrony utiliza la única tecnología capaz de sincro-

y supervivencia con baja toxicidad en el tratamiento del cáncer de pulmón de células no pequeñas en estadio temprano.23 Cáncer de pulmón médicamente inoperable: la SBRT de pulmón con la tecnología TomoTherapy proporciona una alternativa segura y eficaz cuando la cirugía no es posible.24

nizar el haz de tratamiento con el movimiento del

Mesotelioma: IMRT con la tecnología TomoTherapy

tumor en tiempo real, de manera que la radiación se

ofrece un excelente control local- regional y super-

entregue continuamente sobre el tumor sin irradiar

vivencia en el tratamiento del mesotelioma pleural

tejido sano incesariamente. Esto ayuda a garantizar

maligno (MPM).25

que la dosis de radiación se administre al objetivo, lo que maximiza la efectividad del tratamiento y minimiza la dosis a los tejidos circundantes para reducir la incidencia de efectos secundarios.

Oligometástasis: la SBRT con la tecnología TomoTherapy ofrece un control local adecuado con baja morbilidad aguda en el tratamiento de oligometástasis, incluidas las metástasis múltiples.26

A diferencia de otras opciones de radioterapia convencional en 4D, el sistema Tomotherapy guiado con Syncrhony no requiere dispositivos para restringir la respiración de paciente. Al contrario, puede relajarse y respirar normalmente.

CÁNCER DE CUELLO DE ÚTERO Tomotherapy es uno de los sistemas avanzados más integrados para el tratamiento integral del cáncer

Un tratamiento clínicamente probado para el cán-

disponibles en la actualidad. Este sistema permite la

cer de pulmón

administración precisa de IG-IMRT, un tipo avanza-

Tomotherapy System es el equipo mejor preparado para el tratamiento del cáncer en la actualidad, lo que permite la administración precisa de tratamientos sim-

do de IMRT, para el tratamiento del cáncer de cuello uterino. El uso de esta tecnología, así como IMRT, está respaldado por estudios clínicos publicados.

ples a complejos para todo el espectro de pacientes

Un análisis de múltiples estudios independientes (me-

con cáncer de pulmón, desde los primeros estadios

tanálisis) encontró que los pacientes con cáncer de

del cáncer de pulmón de células no pequeñas (CPCNP)

cuello uterino tratados con radioterapia de intensidad

hasta el tratamiento posoperatorio del mesotelioma.

modulada (IMRT) experimentaron una reducción sig-

Los resultados positivos que se obtienen con el uso de la radioterapia helicoidal se encuentra respaldada por estudios clínicos publicados, algunos de los cuales se muestran a continuación:

nificativa de las toxicidades gastrointestinales agudas y genitourinarias y la toxicidad crónica , que los pacientes en el grupo de control tratado con radioterapia conformada tridimensional (3DCRT) o 2DCRT.12

Un estudio evaluó el uso de la tomoterapia para ad-

menor en la función intestinal y urinaria durante el

ministrar IMRT pélvica completa en pacientes con

tratamiento. Esto quiere decir que que la radiación

cáncer de cuello uterino localmente avanzado. Los

no afectó significativamente los órganos sanos ni

planes de tratamiento con tomoterapia se compara-

la vida normal del paciente.

ron con los creados para la radioterapia pélvica completa convencional (WPRT). El estudio encontró que el tratamiento con TomoTherapy es una opción viable. Además, los planes de tratamiento de TomoTherapy redujeron con éxito la dosis de radiación que se administraría al recto, la vejiga y los intestinos, en comparación con los planes WPRT convencionales.13

CÁNCER DE PRÓSTATA La evidencia clínica respalda el uso del sistema de tomoterapia para el tratamiento de pacientes con cáncer de próstata de todos los grupos de riesgo, y la evidencia preliminar sugiere excelentes resultados clínicos. Los regímenes de tratamiento descritos en los estudios refuerzan los beneficios de las capacidades únicas de las plataformas TomoTherapy y Radixact. Tratamiento del cáncer de próstata moderadamente hipofraccionado Varios estudios demuestran que la radioterapia helicoidal es excelente para el tratamiento con hipofraccionamiento moderado de grandes volúmenes blanco que incluyen la próstata y los ganglios linfáticos pélvicos. El consenso clínico indica que determinados niveles de hipofraccionamiento son apropiados para el tratamiento eficaz de los cánceres de próstata.27, 28, 29

La radioterapia helicoidal es la mejor opción para pacientes con cáncer de cuello uterino ya que logra los niveles más bajos de toxicidad en órganos sanos, lo que permite mejorar la calidad de vida después del tratamiento.14 Los resultados de un estudio aleatorizado diseñado para comparar la perspectiva de los pacientes con cáncer de cuello uterino y de endometrio sobre la toxicidad aguda y la calidad de vida durante el tratamiento con radiación pélvica estándar o IMRT, encontraron que la IMRT tuvo un impacto

Ultra-hipofraccionamiento para el cáncer de próstata En este caso, la evidencia clínica respalda el uso de la tecnología para el hipofraccionamiento extremo. En un estudio clínico, los pacientes que recibieron tratamiento “ultrahipofraccionado” con TomoTherapy vieron tasas de recaída a 5 años comparables a una combinación de radioterapia tradicional y braquiterapia; sin embargo, con una toxicidad significativamente menor y un curso general de tratamiento más corto.

común de tratar los cánceres anales en estadio I (con invasión de la membrana basal) a estadio III. Según la Sociedad Estadounidense del Cáncer y varias organizaciones profesionales de la salud, la radioterapia de intensidad modulada (IMRT) es el tipo preferido de tratamiento con EBRT. Un tratamiento clínicamente probado para el cáncer anal El sistema Tomotherapy es uno de los sistemas avanzados más integrados para el tratamiento integral del cáncer disponibles en la actualidad. El sistema Tomo-

CÁNCER DE ANO

therapy permite la administración precisa de IG-IMRT,

Los pacientes con cánceres de ano están logrando

cáncer anal. El uso de la tecnología de radioterapia

resultados exitosos a través de tratamientos avan-

helicoidal, así como la IMRT, está respaldado por estu-

zados que combinan quimioterapia y radioterapia.

dios clínicos publicados.31, 32

Debido a que los cánceres anales se encuentran muy cerca del resto del tracto digestivo, la vejiga y los órganos reproductivos, la precisión es fundamental para reducir el riesgo de efectos secundarios a corto y largo plazo. La precisión en la administración de la dosis de radiación también es necesaria para ayudar a controlar la enfermedad. La radioterapia de haz externo (EBRT) es la forma más

un tipo avanzado de IMRT, para el tratamiento del

Los estudios encontraron que los pacientes con cáncer anal que recibieron IG-IMRT con un refuerzo de radiación simultáneo, utilizando Tomoterapia helicoidal, experimentaron bajas toxicidades agudas o tardías relacionadas con el tratamiento y un buen control local del cáncer, al tiempo que brindan una opción de tratamiento más eficiente y conveniente para los pacientes. Este enfoque de tratamiento con radiación, con o sin quimioterapia, permitió a los médicos reducir los márgenes alrededor del tumor que recibe radiación, lo que resultó en una reducción significativa en ciertas tasas de toxicidad sin afectar los resultados del tratamiento. Un análisis que involucró a pacientes con cáncer anal encontró que el tratamiento con IMRT y la radiación de refuerzo integrada simultánea mostró excelentes resultados a largo plazo y con efectos secundarios bien tolerados por los pacientes.33 La comparación que generaron Fredman E.T., Abdel-Wahab M., Kumar AMS entre pacientes que recibieron IMRT o radioterapia conformada 3D,

en combinación con quimioterapia, mostró que la

El sistema Radixact/TomoTherapy es el único equi-

IMRT, como parte del protocolo de tratamiento, re-

po el mundo que es capaz de administrar radiación

sultó en una cantidad significativamente menor de

helicoidal, y a su vez tiene integrado un sistema de

incontinencia, dolor y fatiga, así como significativa-

imagenes que permite realizar una radioterapia pre-

mente menos toxicidades crónicas posteriores al

cisa guiada por imágenes y de intensidad modulada

tratamiento, en comparación con la terapia confor-

(IG -IMRT) de múltiples rotaciones de 360 grados

mada 3D.

alrededor de su cuerpo, lo que brinda una opción al-

tamente precisa, personalizada y no invasiva para el

CÁNCER DE RECTO El primer paso para tratar el cáncer de recto localmente avanzado suele ser la radioterapia y la quimioterapia, cuando el paciente está lo suficientemente sano para ambos. Las innovaciones en radioterapia ayudan a garantizar que los pacientes reciban el tratamiento más eficaz para su afección médica particular.

tratamiento del cáncer de recto avanzado. Una opción más precisa: tratar el cáncer. Minimizar el daño al tejido sano La radioterapia es un tratamiento comprobado para el cáncer de recto localmente avanzado y generalmente se usa antes de la cirugía, con o sin quimioterapia, para reducir el tamaño del tumor, con el objetivo final de curar la enfermedad. Sin embargo, la radiación administrada a los órganos circundantes, como el intestino y la vejiga, puede provocar efectos secundarios que cambian la vida lo que hace que sea de vital importancia que la radiación se administre con extrema precisión y precisión. El sistema Tomotherapy porciona un mayor control de la radiación para que se adapte con precisión al tumor y ayude a minimizar el daño a los tejidos sanos. El resultado es un tratamiento de radioterapia que maximiza la efectividad al tiempo que ayuda a preservar la función gastrointestinal y genitourinaria, lo que puede conducir a una mejor calidad de vida para los pacientes tanto durante como después del tratamiento.

Los tratamientos con TomoTherapy son más confortables y rápidos, además de ofrecer los mejores resultados en precisión y eficacia clínica.

OTRAS INDICACIONES Micosis Fungoides La micosis fungoides es una enfermedad que afecta la piel y es familia de los linfomas no hodgkinianos. La micosis fungoides es la expresión más frecuente del linfoma cutáneo de células T y se presenta como una afectación de la piel en la que aparecen brotes de lesiones planas, en forma de placas delgadas o pe-

Pre Tratamiento

Post Tratamiento

queños tumores en todo el cuerpo. Esta enfermedad tiende a diseminarse a los ganglios linfáticos y otros órganos. Entre los tratamientos comunes para esta

en piel de aspecto normal o en piel dañada (aunque

enfermedad está la irradiación con electrones a cuer-

haya sido muchos años antes) por la exposición al

po entero. Sin embargo, con el sistema Tomotherapy

sol (queratosis actínica). Con Tomotherapy es posible

existe una manera de tratar esta enfermedad con fo-

tratar estas afecciones de manera muy efectiva.

tones dirigidos a la piel. Existe evidencia científica de los protocolos utilizados con este sistema para tratar dicha enfermedad (Sarfehnia et al 2013).

Leucemia Linfoblástica

Meduloblastoma Este Este tipo de tumor es intracraneal maligno y se origina en el cerebelo. Usualmente crece desde la parte más central del cerebelo produciendo a menu-

Una de las técnicas utilizadas para tratar la leucemia

do hidrocefalia secundaria. Este tipo de tumor tiene

linfoblástica aguda es la Irradiación Corporal Total o

tendencia a extenderse a través del sistema nervioso

TBI por sus siglas en inglés. La finalidad de este trata-

central e invadir meninges. El tratamiento radiante

miento es inmuno- suprimir al paciente para hacerle

para estos casos generalmente se realiza mediante

implante de médula ósea. Con el sistema Tomotherapy

una irradiación craneo-espinal por lo que dicho plan

es posible realizar este tipo de tratamiento de manera

de tratamiento es complicado de hacer y entregar

muy efectiva. La definición de los volúmenes de irra-

con un acelerador lineal convencional. El sistema To-

diación y restricción es un proceso muy importante

motherapy ofrece una solución muy eficiente para

con el cual se garantiza la dosis en el sistema de plani-

tratar estos casos debido a su modalidad de trata-

ficación. Existen trabajos que evidencian esta técnica.

miento helicoidal.

Carcinoma de células escamosas

La ventaja en estos casos es evitar la superposición

El carcinoma de células escamosas suele desarrollar-

de campos que se genera con aceleradores lineales

se en zonas de piel expuestas al sol, pero también

convencionales. A continuación, se presenta una

puede hacerlo en cualquier otra parte del cuerpo,

figura comparando la planificación con TomoThera-

como la lengua o la mucosa bucal. Puede formarse

py (A) y con un acelerador lineal convencional (B).

Al abarcar campos de 135 cm es el equipo ideal para tratamientos de columna.

Planificación con Tomotherapy

tecnología, desde el más simple hasta el más complicado, con una efectividad extraordinaria. La modalidad helicoidal trae múltiples ventajas en cuanto Otra ventaja que ofrece el Tomotherapy en este caso

a distribución de dosis, longitud de tratamiento y

que es la ubicación del paciente en máquina. El pa-

tiempo de tratamiento, lo que hace que esta tecno-

ciente se ubica sólo una vez, se verifica diariamente

logía sea realmente innovadora.

con la tomografía de posicionamiento y se trata todo el volumen de irradiación con un solo plan. Mientras que con un acelerador lineal convencional este tipo de tratamiento involucra 3 isocentros diferentes y además está el riesgo de superponer los campos produciendo una superposición de dosis en las uniones.

El confort del paciente es algo que se viene buscando con el desarrollo de nuevas técnicas de radioterapia ya que está directamente relacionado con la precisión del tratamiento. Un paciente que se sienta cómodo le resultará más fácil recibir el tratamiento que si se sintiese incómodo, y esto se relaciona con

En conclusión, existe evidencia científica que cual-

el posicionamiento diario y el tiempo que transcurre

quier tipo de cáncer puede ser tratado con esta

durante el tratamiento.

Tomoterapia de alta precisión en todo el cuerpo

LOCALIZACIÓN

PAT O LO G Í A S

INTRACRANEAL

MALFORMACIONES ARTEREOVENOSAS MÚLTIPLES METÁSTASIS TUMORES PRIMARIOS DE CUALQUIER TAMAÑO

CABEZA Y CUELLO

TUM O RE S P RI M ARI O S P EQ UE ÑO S TUM O RE S P RI M ARI O S G RAND E S RE I RRAD I ACI O NE S & BO O S T

PULMÓN

TUM O RE S P RI M ARI O S P EQ UE ÑO S TUM O RE S P RI M ARI O S G RAND E S M E TÁS TAS I S

MAMA

M AM A CO M P LE TA PARED COSTAL MAMA BILATERAL

COLUMNA

TUM O RE S BE NI G NO S MALFORMACIONES ARTEREOVENOSAS METÁSTASIS

HÍGADO

P RI M ARI O S I NO P E RABLE S M E TÁS TAS I S

PÁ N C R E A S

TUM O RE S I NO P E RABLE S BO O S T P RE / P O S T O P E RATO RI O

RIÑONES

TUM O RE S I NO P E RABLE S M E TÁS TAS I S

GINECOLÓGICO

CUE LLO UTE RI NO E ND O M E TRI O M E TÁS TAS I S

P E LV I S

VE JI GA CANAL ANAL

P R Ó S TATA

PRIMARIOS RIESGO BAJO / INTERMEDIO RECURRE NCI AS

SUPERFICIAL

LE S I O NE S E N P I E L CARCI NO M A BASAL Q UE LO I D E S

OTRAS

TBI TM I SARCO M AS

RECTO M E TÁS TAS I S

CRANEOESPINAL OLIGOMETÁSTASIS

Carac terístic as del t rat a mie nto

Mundialmente reconocido como el mejor en tratamientos pediátricos. Ultra preciso y versátil, para todo tipo de tumores. Reducción de efectos secundarios. Preservación de tejidos sanos.

SEGURIDAD

EFICACIA Y EFECTIVIDAD

La toxicidad asociada a TomoTherapy y los efec-

TomoTherapy es una tecnología efectiva

tos adversos sufridos por el paciente son me-

para el tratamiento del cáncer. Según los

nores que con radioterapia convencional. Esto

estudios realizados, en comparación con la

se debe a que la tomoterapia administra la do-

radioterapia convencional, se obtiene una

sis con gran precisión sobre el tumor, evitando

irradiación de alta precisión y mejores indi-

los tejidos sanos circundantes y los órganos de

cadores dosimétricos, mayor conformidad y

riesgo, reduciendo el riesgo de infra y sobre do-

homogeneidad en la distribución con mayo-

sificaciones. El tratamiento es indoloro y no re-

res gradientes de dosis. Al poder administrar

sulta incómodo para el paciente.

dosis superiores sobre el tumor, existe ma-

UTILIDAD CLÍNICA TomoTherapy contribuye a mejorar la calidad de vida de los pacientes, con un incremento de los controles de calidad realizados previo a la administración del tratamiento en comparación a otras formas de radioterapia. Es posible ver una reducción de la morbilidad y un aumento del control de la enfermedad y de la esperanza de vida. Otra ventaja es la reducción del tiempo global de tratamiento.

yor eficacia terapéutica en cuanto a destrucción de tejido tumoral, mayor control local de la enfermedad y menor riesgo de recidiva tumoral, sin incrementar la toxicidad.

Diseño del búnke r

DeLeC y Accuray prestarán asesoría a los profesionales de la institución en la evaluación de las instalaciones y en la interpretación de las especificaciones técnicas para la construcción del búnker, con el fin de que la institución proceda a una adecuada instalación y operación del equipo. En términos generales el servicio de asesoría consistirá en: Prestar asesoría, por parte de ingenieros de DeLeC y Accuray Inc. a los profesionales que designe la institución, en: la evaluación de las actuales instalaciones; en el visto bueno formal a los planos presentados para la obra de construcción del búnker, en forma previa su inicio; en la definición de las especificaciones técnicas para el diseño del búnker; y, en la realización de visitas inspectivas de carácter formal a la obra de construcción del búnker. A continuación, se relaciona un documento orientativo de las disposiciones genéricas que debe tener un búnker para el sistema Tomotherapy. Cada caso concreto se tratará de forma puntual y detallada teniendo en cuenta las características particulares de cada proyecto.

Compacto, autoblindado y potente. Optimiza los espacios del búnker.

Dimensiones del BÚNKER

A: 275 cm. B: 602 cm. C: 463 cm

Gracias a su exclusivo blindaje primario, podría permitir la reducción de los espesores de las paredes hasta 105 cm.

Ca sos de éxito

Centro Oncológico Sunchales

A principios del 2019 concluyó la instalación del

aplican en todo el mundo, actualizaciones periódicas

equipo para radioterapia y radiocirugía ThomoThera-

y controles de calidad estrictos que garantizan el ni-

py, de Accuray. Lo adquirió la Fundación ATILRA para

vel de prestación.

el Centro Oncológico Sunchales, ubicado en la ciudad de Sunchales, provincia de Santa Fe. El equipo de bioingenieros y físicos de DeLeC Científica participó del asesoramiento y la provisión del sistema TomoTherapy. El proyecto de Atilra consistió en el desarrollo de un centro de terapia radiante de excelencia en una región con alta incidencia de cáncer, y sin servicios de radioterapia de alta tecnología. Con la compra del equipo, ATILRA obtuvo un entrenamiento dirigido a los Físicos Nucleares y Técnicos

Foto: equipo de Servicio Técnico de DeLeC

en Radioterapia, siguiendo una planificación que consiste en tres etapas:

COS Atilra superó los 500 pacientes tratados con To-

i) fábrica de Accuray en Estados Unidos; ii) Centro

moTherapy, demostrando que es posible ofrecer te-

Médico instalado en Sudamérica y

rapias radiantes de máxima calidad en las provincias.

iii) por último el entrenamiento final in situ en el Centro Oncológico Sunchales. Los entrenamientos son impartidos por expertos y bajo estándares internacionales, con evaluaciones y calificaciones que se

Las clínicas más prestigiosas de Argentina hacen derivaciones a la ciudad de Sunchales para garantizar tratamientos seguros con TomoTherapy

Tecnología de punta en las provincias Se trata de un hito significativo para la región de Santa Fe y alrededores ya que el ThomoTerapy es un equipo fundamental en el tratamiento de todas las patologías de cáncer a través de la radiocirugía y la radioterapia. La ciudad de Sunchales es de fácil acceso para los ciudadanos de Santa Fe, Córdoba, Rosario, Buenos Aires y se proyecta como un enclave de vanguardia en el ámbito de la salud en el país. Con la inauguración del Centro Oncológico Sunchales, ATILRA busca ampliar las alternativas de tratamiento contra el cáncer y además impulsar proyectos de formación e investigación, junto con Universidades nacionales y de otros países. La tecnología de Accuray es una pieza importante para mejorar la calidad de vida de la población e impulsar el desarrollo local.

Hospital de Clínicas, SEDES, La Paz (Bolivia)

Otro caso notable de incorporación de nueva tecno-

Esta ventaja acortó los tiempos del proceso de ins-

logía para radioterapia y radiocirugía es el de SEDES.

talación y puesta en marcha. Se ganó la licitación

El Hospital de Clínicas de La Paz, Bolivia, adquirió un

y en diciembre de 2018 llegó el Radixact a La Paz.

equipo Radixact X7 para su área de terapia radiante.

La instalación del mismo la llevó adelante un grupo

Para incorporar el equipo, SEDES llamó a licitación pública. Entre los requisitos técnicos estaban la reutilización del búnker existente en el edificio y la presentación de estudios o certificaciones, por parte del proveedor, asegurando el funcionamiento a 3600 mts sobre el nivel del mar, altura en la que se encuentra la ciudad.

de ingenieros y técnicos liderados por DeLeC Científica S.A. Se trabajó respetando los protocolos previstos para la contención del COVID19, se superaron las adversidades que implicó la crisis social y política en Bolivia en 2019, y a comienzos del 2020 se inauguró el nuevo servicio de Radioterapia y Radiocirugía del Hospital de Clínicas SEDES, de La Paz.

En la actualidad, el staff de físicos y médicos continúan con entrenamientos en Bolivia y en otros centros de referencia de Accuray.

DeLeC Científica S.A., a través del Grupo Cosin, su representante oficial en Bolivia, se presentó a la convocatoria con una propuesta superadora. Gracias a que el equipo viene blindado desde fábrica, se ajustó al búnker existente.

Este proceso significa un paso notable para la calidad de los tratamientos que brinda el sistema público de salud boliviano, y responde a una demanda de años de la comunidad de pacientes oncológicos de este país con la tecnología del mundo en radioterapia y radiocirugía.

E nt re na mie nto

El usuario final de TomoTherapy/Radixact podrá acceder a un plan de capacitación integral compuesto por: i.

Cursos en fábrica.

ii.

Curso en una institución a definir con experiencia en el sistema y equipo en funcionamiento.

iii.

Curso en la institución de destino una vez instalado el equipo.

iv.

Capacitación brindada por personal de Aplicaciones Clínicas de DeLeC.

Cursos ofrecidos para el Sistema TomoTherapy

i. Cursos en fábrica

A. Curso para Físicos

El usuario deberá determinar el número de asistentes

Audiencia: Físicos Médicos responsables de ejecutar

que enviará a cada curso. El personal de DeLeC los

el comisionamiento y las tareas de control de calidad

asistirá para la inscripción. Se debe considerar que

del Sistema de tratamiento TomoTherapy.

previo a la instalación, al menos un físico debe tener el curso en fábrica finalizado y es recomendable que también tenga completo el curso on-site en un sitio donde ya se encuentra un equipo en funcionamiento. Los cursos en fábrica son tres. En la tabla anterior se enuncian y se indica además quién debería realizarlos. Al menos 1 Físico y 1 Técnico deben realizar estos cursos.

Objetivo: Este curso provee una visión general de la operación clínica con instrucciones en profundidad de los procedimientos para los test de aceptación (ATP), procedimientos de comisionamiento y herramientas prácticas de rutina para QA. Detalles: El programa del curso combina formación teórica y conceptual con ejercicios prácticos para

Se encuentran incluidos en la oferta los entrena-

preparar al Físico en el desarrollo del ATP, así como

mientos en fábrica para un (1) Médico, un (1) Fisico

también en las actividades de QA de rutina. Incluye

Médico y un (1) Tecnólogo.

una introducción a la Planificación del Tratamiento con prácticas aplicadas sobre el Sistema de Tratamiento TomoTherapy. La finalización de este curso prepara al Físico para ejecutar las actividades de comisionamiento y pruebas necesarias para asegurar que el sistema está listo para uso clínico. Nota: Para los Físicos que diseñan planes clínicos de tratamiento se les recomienda alistarse en el curso separado de Planificación de Tratamiento.

B. Curso para Operaciones de Entrega de Tratamiento

y aplicación de actividades prácticas. La formación va desde los fundamentos básicos a las técnicas de planificación más avanzadas. Se abordan aspectos y

Audiencia: Todos los operadores del Sistema

consideraciones únicos para planificar los tratamien-

TomoTherapy.

tos del sistema TomoTherapy. Se presta atención a

Objetivo: Este curso enseña las habilidades requeridas para la entrega de tratamientos y el desarrollo de tareas básicas de mantenimiento de datos. Detalles: El curso de tres días combina formación conceptual y teórica sobre entrega de tratamientos con ejercicios prácticos en laboratorio para permitir que los asistentes puedan realizar todos los pasos específicos en el proceso de tratamiento con TomoTherapy. Los asistentes tendrán la posibilidad de aplicar las habilidades adquiridas en un contexto práctico basado en la resolución de problemas, que los preparará para la operación del sistema en el escenario clínico.

las diferentes aplicaciones clínicas, incluidos los tratamientos intracraneales y extracraneales, para proporcionar un contexto clínico para las habilidades que se enseñan. Las fechas se definirán entre el usuario final y Accuray y/o DeLeC. La capacitación se dicta únicamente en idioma inglés. En caso de que el personal del cliente no tenga un buen dominio del idioma inglés, Accuray hará los arreglos necesarios para que haya un intérprete disponible para la capacitación correspondiente; dichos intérpretes deberán estar capacitados para realizar interpretación simultánea y estar familiarizados con la terminología involucrada. El cliente notificará con anticipación a Accuray si son necesarios los

C. Planificación de Tratamiento Audiencia: Dosimetristas, Físicos Médicos y personal clínico responsable del desarrollo y optimización de los planes de tratamiento clínico utilizando la estación de planificación de Tomo. Objetivo: Este curso incluye una descripción completa de las herramientas y capacidades de la planificación TomoHelical ™ y TomoDirect ™ usando IMRT y 3DCRT. Detalles: El programa del curso combina formación conceptual y teórica con ejercicios prácticos en laboratorio que permitirá a los asistentes el desarrollo

servicios de traducción. El cliente será responsable de todos los gastos de interpretación y traducción.

ii. Curso en institución con experiencia en el sistema y equipo en funcionamiento

iii. Curso en la institución una vez instalado el sistema

Además de los cursos en fábrica para físicos y téc-

La última etapa de entrenamiento se coordinará

nicos, se realizará en fecha e institución a coordi-

para ser realizada al finalizar la instalación del equi-

nar con el personal del usuario final y Accuray, el

po en el Hospital.

entrenamiento en un sitio donde ya se encuentra instalado un equipo.

iv. Capacitación permanente brindada por personal de Aplicaciones Clínicas de DeLeC

Allí se sugiere la participación del personal médico

Una vez finalizados los tres cursos anteriores manda-

radioterapeuta, físico y/o dosimetrista y técnico del

torios de Accuray, el personal de Aplicaciones Clíni-

servicio. Se encuentran incluidos en la oferta los en-

cas y Docencia de DeLeC Científica proveerá capaci-

trenamientos en fábrica para un (1) Médico, un (1)

taciones de forma permanente a la totalidad de los

Fisico Médico y un (1) Tecnólogo.

profesionales del servicio.

Primer paciente tratado en el Hospital de Clínicas de La Paz, al término del entrenamiento Go Live.

Comp a ra tiva

TomoTherapy vs Synergy Comparativa técnica

TOMO HDA VS SYNERGY

CARACTERÍSTICAS TÉCNICAS

TOMO HDA

SYNERGY

Caracterís cas de los haces de tratamiento ENERGÍAS DE FOTONES

6 MV

4, 6, 8, 10, 15 y 18 MV 6[1]

TA S A D E D Ó S I S APERTURA MÁX. DE CAMPO

5 x 40 cm[2]

40 x 40 cm

ENERGÍAS DE ELECTRONES

no posee electrones

4, 6, 8, 9, 10, 12, 15, 18 y 20 MeV

TA S A

DE DOSIS

Caracterís cas mecánicas del gantry PRECISIÓN GANTRY

R OTA C I Ó N

±0.1o 1 - 5 RPM para tratamiento

V E LO C I D A D R O TA C I Ó N GANTRY D I S TA N C I A F U E N T E ISOCENTRO

85 cm

DESPLAZAMIENTO DEL ISOCENTRO MECÁNICO

<0.4 mm

R A N G O D E R O TA C I O N GANTRY

±0.5o

DEL

0 - 1 RPM

100 cm

)

CUÑA FÍSICA

CÁMARA MONITORA

Cámara ionización sellada

Cámara ionización abierta

REFRIGERACION GANTRY

Sistema de refrigeración por

Sistema externo de refrigeración

DEL

)

CARACTERÍSTICAS TÉCNICAS

TOMO HDA

Caracterís cas

mecánicas

SYNERGY

y dosimétricas

del

MLC

CANTIDAD DE LÁMINAS ANCHO LÁMINA ISOCENTRO

0.625 cm

0.5 cm

APERTURA MÁXIMA CAMPO

40 x 40 cm

TRANSMISIÓN ENTRE LÁMINAS

<0.5 %

MÁXIMA VELOCIDAD LÁMINA

20 mseg

MECANISMO DE DESPLAZAMIENTO

Electrónico

GEOMETRÍA DEL HAZ UNIFORMIDAD DE LA IMAGEN

Dentro de las 25 HU

CONFIGURACIÓN DEL DETECTOR

Arreglo camaras ionizacion de xenon

RESOLUCIÓN DEL CONTRASTE

2% objetos de 2 cm

M AT R I Z D E I M A G E N

512 x 512

Dentro de las 2 HU

1024 x 1024

GUÍA POR IMÁGENES Camilla P E S O M Á X I M O S O P O R TA D O

200 kg

[1] Se pueden lograr 600 MU/min bajo demanda. [3] Opcionalmente, puede ser habilitado el modo de alta tasa de dosis de electrones (HDRE, por sus siglas en inglés),

Comparativa clínica

DESCRIPCIÓN

MODALIDADES T R ATA M I E N T O

TOMO HDA

SYNERGY

SISTEMA DE PLANIFICACIÓN MOSAIQ

OIS SISTEMA DE MANEJO MOVIMIENTO

DEL

T R ATA M I E N T O S E N LOCALIZACIONES

Synchrony

Response

MÁXIMA LONGITUD DEL C A M P O T R ATA M I E N T O

40 cm Procedimientos especiales

Técnica a distancia extendida, I R R A D I A C I Ó N TO TA L

DE tratamiento aproximado 1 hora

Técnica de irradiación con electrones a distancia extendida, planicación de posiciones correctas del tratamiento, se necesita comisionar la energía de los

MICOSIS FUNGOIDES

campo y a distancia extendida, se deben colocar protecciones de plomo

Un solo plan para tratar

plan para el craneo y cervical, plan

con técnica helicoidal combinación de éstas técnicas

TomoTherapy vs TrueBeam Comparativa técnica

TOMO HDA VS TRUEBEAM CARACTERÍSTICAS TÉCNICAS

ENERGÍAS DE FOTONES

TOMO HDA

6 MV

4, 6, 8, 10, 15 y 20 MV [1]

TA S A D E D Ó S I S

6 - 10 MV [2] 15 y 20 MV [3]

APERTURA MÁX. DE CAMPO

5 x 40 cm[4]

40 x 40 cm

ENERGÍAS DE ELECTRONES

PRECISIÓN GANTRY

R OTA C I Ó N

4, 6, 8, 9, 10, 12, 15, 18 y 20 MeV

± 0.1o

D I S TA N C I A F U E N T E ISOCENTRO

85 cm

DESPLAZAMIENTO DEL ISOCENTRO MECÁNICO

< 0.4 mm

R A N G O D E R OTA C I O N GANTRY

± 0.3o

1 - 5 RPM para tratamiento

V E LO C I D A D R O TA C I Ó N GANTRY

REFRIGERACION GANTRY

TRUEBEAM

DEL

0 - 1 RPM

100 cm

)

Rango de 370o

)

DEL

CARACTERÍSTICAS TÉCNICAS

TOMO HDA

TRUEBEAM

CANTIDAD DE LÁMINAS

120

APERTURA MÁXIMA CAMPO

34 x 40 cm

FUGA MÁXIMA ENTRE LÁMINAS

< 0.3 %

MÁXIMA VELOCIDAD LÁMINA MECANISMO DE DESPLAZAMIENTO

GEOMETRÍA DEL HAZ UNIFORMIDAD DE LA IMAGEN CONFIGURACIÓN DEL DETECTOR

de xenon

RESOLUCIÓN DE CONTRASTE M AT R I Z D E I M A G E N GUÍA POR IMÁGENES

[1] Es posible congurar energas FFF

512 x 512

Comparativa clínica

DESCRIPCIÓN

MODALIDADES T R ATA M I E N T O

TOMO HDA

SBRT

TRUEBEAM

3DCRT, IMRT, VMAT, SRS, SBRT

SISTEMA DE PLANIFICACIÓN ARIA

OIS SISTEMA DE MANEJO MOVIMIENTO

DEL

RPM

T R ATA M I E N T O S E N LOCALIZACIONES HABITUALES

MÁXIMA LONGITUD DEL C A M P O T R ATA M I E N T O

135 cm

40 cm

I R R A D I A C I Ó N TO TA L

MICOSIS FUNGOIDES

MEDULOBLASTOMAS

Referencias

Bruni A, Gaito S, Ciarmatori A, et al. Radiosurgery Using Tomotherapy for Patients with Brain Oligo-me-

tastasis: A Retrospective Analysis on Feasibility and Tolerance. Anticancer Res. 2015 Dec;35(12):6805-12. PMID: 26637900. 2.

Koide Y, Tomita N, Adachi S, et al. Retrospective analysis of hypofractionated stereotactic radiotherapy

for tumors larger than 2 cm. Nagoya J Med Sci. 2019 Aug;81(3):397-406. 3.

Nagai A, Shibamoto Y, Yoshida M, et al. Treatment of single or multiple brain metastases by hypofractio-

nated stereotactic radiotherapy using helical tomotherapy. Int J Mol Sci. 2014 Apr 22;15(4):6910-24. 4.

Boulle G, Bracci S, Hitchcock K, et al. Treatment of grade II-III intracranial meningioma with helical tomo-

therapy. J Clin Neurosci. 2019 Jan; 59:190-196. 5.

Donato V, Caruso C, Bressi C, et al. Evaluation of helical tomotherapy in the treatment of high-grade

gliomas near critical structures. Tumori. 2012 Sep-Oct;98(5):636-42. 6.

Sun Y, Liu G, Chen W, et al. Dosimetric comparisons of craniospinal axis irradiation using helical tomo-

therapy, volume-modulated arc therapy and intensity-modulated radiotherapy for medulloblastoma. Transl. Cancer Res. 2019;8. 7.

Koca T, Basaran H, Sezen D, Karaca S, Ors Y, Arslan D, Aydin A. Comparison of linear accelerator and

helical tomotherapy plans for glioblastoma multiforme patients. Asian Pac J Cancer Prev. 2014;15(18):7811 8.

Chan M, Schupak K, Burman C, Chui C, Clifton Ling C. Comparison of intensity-modulated radiotherapy

with three-dimensional conformal radiation therapy planning for glioblastoma multiforme. Medical Dosimetry. 28(4);261-5 9.

Leung et al. “Treatment of nasopharyngeal carcinoma by TomoTherapy: five-year experience.” Radiation

Oncology. 2013; 8:107. 10. Bibault JE et al. “Clinical Outcomes of Several IMRT Techniques for Patients With Head and Neck Cancer: A Propensity Score-Weighted Analysis. Int J Radiat Oncol Biol Phys.” 2017 Nov 15;99(4):929-937. 11. Bibault JE et al. “Clinical Outcomes of Several IMRT Techniques for Patients With Head and Neck Cancer: A Propensity Score-Weighted Analysis. Int J Radiat Oncol Biol Phys.” 2017 Nov 15;99(4):929-937. 12. Lin Y., Chen K., Lu Z. et al. Intensity-modulated radiation therapy for definitive treatment of cervical cancer: a meta-analysis. Radiat Oncol. 2018 Sep 14;13(1):177. 13. Hsieh C.H., Wei M.C., Lee H.Y. et al. Whole pelvic helical tomotherapy for locally advanced cervical cancer: technical implementation of IMRT with helical tomotherapy. Radiat Oncol. 2009 Dec 10; 4:62.

14. Naik A, Gurjar OP, Gupta KL, Singh K, Nag P, Bhandari V. Comparison of dosimetric parameters and acute toxicity of intensity-modulated and three-dimensional radiotherapy in patients with cervix carcinoma: A randomized prospective study. Cancer Radiother. 2016 Jul;20(5):370-6. 15. Marjanovic D., Plesinac Karapandzic V., Stojanovic Rundic S. et al. Implementation of intensity-modulated radiotherapy and comparison with three-dimensional conformal radiotherapy in the postoperative treatment of cervical cancer. J BUON. 2019 Sep-Oct;24(5):2028-2034. 16. Klopp A.H., Yeung A.R., Deshmukh S. et al. Patient-Reported Toxicity During Pelvic Intensity-Modulated Radiation Therapy: NRG Oncology-RTOG 1203. J Clin Oncol. 2018 Aug 20;36(24):2538-2544. 17. Franco et al. “Intensity-modulated and hypofractionated simultaneous integrated boost adjuvant breast radiation employing statics ports of TomoTherapy (TomoDirect): a prospective phase II trial.” J Cancer Res Clin Oncol. 2014 Jan;140(1):167-77. doi: 10.1007/s00432-013-1560-8. 18. Caudrelier et al. “IMRT sparing of normal tissues in locoregional treatment of breast cancer.” Radiat Oncol. 2014 Jul 22;9:161. doi: 10.1186/1748-717X-9-161. 19. Chitapanarux I, Nobnop W, Tippanya D et al. “Clinical outcomes and dosimetric study of hypofractionated Helical tomotherapy in breast cancer patients.” PLoS One. 2019 Jan 31;14(1): e0211578. 20. Bai XH, Dang J, Chen ZQ, He Z, Li G. Comparison between Intensity-Modulated Radiotherapy and Three-Dimensional Conformal Radiotherapy for Their Effectiveness in Esophageal Cancer Treatment: A Retrospective Single Institution Study. J Oncol. 2020 Mar 20;2020: 6582341. 21. Nguyen NP, Jang S, Vock J, Vinh-Hung V, Chi A, Vos P, Pugh J, Vo RA, Ceizyk M, Desai A, Smith-Raymond L; International Geriatric Radiotherapy Group. Feasibility of intensity-modulated and image-guided radiotherapy for locally advanced esophageal cancer. BMC Cancer. 2014 Apr 17;14: 265. 22. Lin WC, Chang CL, Hsu HL, Yuan KS, Wu ATH, Wu SY. Three-Dimensional Conformal Radiotherapy-Based or Intensity-Modulated Radiotherapy-Based Concurrent Chemoradiotherapy in Patients with Thoracic Esophageal Squamous Cell Carcinoma. Cancers (Basel). 2019 Oct 10;11(10):1529. 23. Rosen LR, Fischer-Valuck BW, Katz SR et. “Helical image-guided stereotactic body radiotherapy (SBRT) for the treatment of early-stage lung cancer: a single-institution experience at the Willis-Knighton Cancer Center.” Tumori. 2014 Jan-Feb;100(1):42-8. doi: 10.1700/1430.15814. 24. Arcangeli S, Falcinelli L, Bracci S et al. “Treatment outcomes and patterns of radiologic appearance after hypofractionated image-guided radiotherapy delivered with helical tomotherapy (HHT) for lung tumours.” Br J Radiol. 2017 Mar;90(1071):20160853. doi: 10.1259/bjr.20160853. 25. Minatel E, Trovo M, Polesel J et al. “Radical pleurectomy/decortication followed by high dose of radiation therapy for malignant pleural mesothelioma. Final results with long-term follow-up.” Lung Cancer. 2014 Jan;83(1):78-82. doi: 10.1016/j.lungcan.2013.10.013.

26. Sole CV, Lopez Guerra JL, Matute R et al. “Stereotactic ablative radiotherapy delivered by image-guided helical tomotherapy for extracranial oligometastases.” Clin Transl Oncol. 2013 Jun;15(6):484-91. doi: 10.1007/ s12094-012-0956-2 27. Di Muzio NG, Fodor A, Noris Chiorda B, et al. “Moderate Hypofractionation with Simultaneous Integrated Boost in Prostate Cancer: Long-term Results of a Phase I-II Study.” Clin Oncol (R Coll Radiol). 2016 Aug;28(8):490-500. doi: 10.1016/j.clon.2016.02.005. 28. Tomita N, Soga N, Ogura Y, et al. “High-dose radiotherapy with helical tomotherapy and long-term androgen deprivation therapy for prostate cancer: 5-year outcomes.” J Cancer Res Clin Oncol. 2016 Jul;142(7):160919. doi: 10.1007/s00432-016-2173-9. 29. Yamazaki H, Masui K, Suzuki G, et al. “High-Dose-Rate Brachytherapy Monotherapy versus Image-Guided Intensity-Modulated Radiotherapy with Helical Tomotherapy for Patients with Localized Prostate Cancer.” Cancers (Basel). 2018 Sep 10;10(9). pii: E322. doi: 1. 30. Macias VA, Barrera-Mellado I. “Ultra-hypofractionated radiation therapy for unfavourable intermediate-risk and high-risk prostate cancer is safe and effective: 5-year outcomes of a phase II trial.” BJU Int. 2019 Oct 15. doi: 10.1111/bju.14925. 31. Joseph K., Nijjar Y., Warkentin H. et al. Prospective phase II study of tomotherapy based chemoradiation treatment for locally advanced anal cancer. Radiother Oncol. 2015 Nov;117(2):234-9 32. De Bari B., Jumeau R., Bouchaab H. et al. Efficacy and safety of helical tomotherapy 33. Mitra D., Hong T.S., Horick N. et al. Long-term outcomes and toxicities of a large cohort of anal cancer patients treated with dose-painted IMRT per RTOG 0529. Advances in radiation oncology. 2017;2(2):110– 117. 34. Fredman E.T., Abdel-Wahab M., Kumar AMS. Influence of radiation treatment technique on outcome and toxicity in anal cancer. J Radiat Oncol. 2017;6(4):413-421.

Bibliografía DING (2018) Image guidance doses delivered during radiotherapy: Quantification, managment and reduction: Report of the AAPM Therapy Physics Committee Task Group 180. 2018 ZALESKA (2017) Influence of optimizing protocol choice on the integral dose value in prostate radiotherapy planning by dynamic techniques - Pilot study. HSU (2017) Dosimetric comparison of different treatment modalities for stereotactic radiotherapy. SHELLEY (2017) Delivered dose can be a better predictor of rectal toxicity than planned dose in prostate radiotherapy. NAGAI (2017) Intensity-modulated radiotherapy using two statics ports of TomoTherapy for breast cancer after conservative surgery : dosimetric comparison with other treatment methods and 3-year clinical results. WADASADAWALA (2015) Use of TomoTherapy in treatment of synchronous bilateral breast cancer: dosimetric comparison study. VAN GESTEL (2015) Fast Helical TomoTherapy in a head and neck cancer planning study: is time priceless? SAW (2018) 3D treatment planning on helical tomotherapy delivery system HU (2017) A feasibility study on the use of tomotherapy megavoltage computed tomography images for palliative patient treatment planning. RAMSEY (2006) A technique for adaptive image-guided helical tomotherapy for lung cancer. KIM (2018) Assesment of inter- and intra-fractional volume of bladder and body contor by mega-voltage computed tomography in helical tomotherapy for pelvic malignancy. PEÑAGARÍCANO (2011) Clinical feasibility of TBI with helical TomoTherapy. ZHANG (2014) Dosimetric comparison of craniospinal irradiation using different TomoTherapy techniques. RONG (2011) Dosimetric and clinical review of helical tomotherapy SARFEHNIA (2013) A novel approach to total skin irradiation using helical tomotherapy

Índice 1. Image guidance doses delivered during radiotherapy.

2. Dosimetric comparison of different treatment modalities for stereotactic radiotherapy.

108

3. A feasibility study on the use of TomoTherapy megavoltage computed Tomograpy images for palliative Patient tratment planning.

119

4. Assessment of inter and intra-fractional volume of bladder and body contour by mega-voltage computed tomography in helical tomotherapy for pelvic malignancy.

137

5. Intensity-modulated radiotherapy using two static port of TomoTherapy for breast cancer after conservative surgery: dosimetric comparison with other treatment methods and 3-years clinical results.

143

6. Patient dose from kilovoltage radiographs durin motion-synchronized treatments on Radixact.

5151

7. Clinical Imprementation and Initial Experience of Real-Time Motion Tracking With Jaws and Multileaf Collimator During Helical Tomotherapy Delivery.

159

8. Organ sparing total marrow irradiation compared to total body irradiation prior to allogeneic stem cell transplantation. 9. 3D treatment planning on helical TomoTherapy.

169 184

10. Delivered dose can be a better predictor of rectal toxicity than planned dose in prostate radiotherapy.

193

11. Helical tomotherapy for prostate cancer radiation therapy: An audit of early toxicity and quality of life.

199

12. Influence of optimizing protocol choice on the integral dose value in prostate radiotherapy planning by dynamic techniques. 13. A novel approach to total skin irradiation using helical TomoTherapy.

205 210

14. COVID-19 pneumonia treated with ultra-low doses of radiotherapy (Ultra-COVID study): a single institution report of two cases. 90

217

A continuación se pone a disposición una selección de publicaciones científicas que avalan las características y beneficios del sistema Radixact, de Accuray. En la selección de estos papers se dio prioridad a los contenidos más recientes y pertinentes, teniendo en cuenta la presentación que se ofrece en la carpeta Radixact confeccionada por DeLeC Científica. Si el lector desea ampliar la información científica sobre los usos del TomoTherapy puede consultar a los sitios www.delec.com.ar, o bien al correo: comunicaciones@ delec.com.ar.

MÁS PUBLICACIONES

WWW.DELEC.COM.AR

Image guidance doses delivered during radiotherapy

Image guidance doses delivered during radiotherapy: Quantiﬁcation, management, and reduction: Report of the AAPM Therapy Physics Committee Task Group 180 George X. Dinga)

Department of Radiation Oncology, Vanderbilt University School of Medicine, Nashville, TN 37232, USA

Parham Alaei University of Minnesota, Minneapolis, MN 55455, USA

Bruce Curran Virginia Commonwealth University, Richmond, VA 23284, USA

Ryan Flynn University of Iowa, Iowa City, IA 52242, USA

Michael Gossman Tri-State Regional Cancer Center, Ashland, KY 41101, USA

T. Rock Mackie University of Wisconsin, Madison, WI 53715, USA

Moyed Miften University of Colorado, Aurora, CO 80045, USA

Richard Morin Mayo Clinic, Jacksonville, FL 32224, USA

X. George Xu Rensselaer Polytechnic Institute, Troy, NY 12180, USA

Timothy C. Zhu University of Pennsylvania, Philadelphia, PA 19104, USA

(Received 18 July 2017; revised 10 January 2018; accepted for publication 10 January 2018; published xx xxxx xxxx) Background: With radiotherapy having entered the era of image guidance, or image-guided radiation therapy (IGRT), imaging procedures are routinely performed for patient positioning and target localization. The imaging dose delivered may result in excessive dose to sensitive organs and potentially increase the chance of secondary cancers and, therefore, needs to be managed. Aims: This task group was charged with: a) providing an overview on imaging dose, including megavoltage electronic portal imaging (MV EPI), kilovoltage digital radiography (kV DR), Tomotherapy MV-CT, megavoltage cone-beam CT (MV-CBCT) and kilovoltage cone-beam CT (kVCBCT), and b) providing general guidelines for commissioning dose calculation methods and managing imaging dose to patients. Materials & Methods: We briefly review the dose to radiotherapy (RT) patients resulting from different image guidance procedures and list typical organ doses resulting from MV and kV image acquisition procedures. Results: We provide recommendations for managing the imaging dose, including different methods for its calculation, and techniques for reducing it. The recommended threshold beyond which imaging dose should be considered in the treatment planning process is 5% of the therapeutic target dose. Discussion: Although the imaging dose resulting from current kV acquisition procedures is generally below this threshold, the ALARA principle should always be applied in practice. Medical physicists should make radiation oncologists aware of the imaging doses delivered to patients under their care. Conclusion: Balancing ALARA with the requirement for effective target localization requires that imaging dose be managed based on the consideration of weighing risks and benefits to the patient. © 2018 American Association of Physicists in Medicine [https://doi.org/10.1002/mp.12824] Key words: IGRT, image dose management, image dose reduction techniques, image guidance doses, recommended dose threshold

Med. Phys. 0 (0), xxxx

0094-2405/xxxx/0(0)/1/xx

Ding et al.: Image Guidance Doses to Radiotherapy Patients

TABLE OF CONTENTS 1. INTRODUCTION 2. OVERVIEW OF DOSE RESULTING FROM IMAGE GUIDANCE PROCEDURES 2.A. Megavoltage beam imaging 2.B. Kilovoltage beam imaging 3. DOSE CALCULATION ALGORITHMS FOR KV AND MV IMAGING DOSE 3.A. Monte Carlo-based methods 3.B. Model-based methods 4. KILOVOLTAGE IMAGING BEAM DOSIMETRY 4.A. Input data for kV x-ray beam characterization 4.B. Output of a kV imager 4.C. In vivo dosimetry 5. METHODS OF ACCOUNTING FOR IMAGING DOSE 5.A. Patient-specific imaging dose calculations 5.B. Nonpatient-specific imaging dose estimations 6. RECOMMENDATIONS 6.A. General recommendations 6.B. Imaging dose output and consistency checks 6.C. Accounting for imaging dose to RT patients 6.D. Available techniques to reduce imaging dose to patients 7. ACKNOWLEDGMENTS

1. INTRODUCTION Image-guided radiation therapy (IGRT) has rapidly been adopted as the standard of care to improve the geometric accuracy of patient positioning during radiotherapy.1–6 IGRT can significantly reduce target positioning errors, therefore, enabling highly conformal treatments. The acquired images during treatment delivery can be used for monitoring patient and target geometry changes, potential adaptive planning,7–9 or margin reduction.10 During the course of IGRT, the image guidance procedure is typically performed for each treatment fraction. The patient may occasionally be imaged more than once during any fraction in order to ensure that the patient’s position is correct, and to reposition if necessary. Since these imaging procedures deliver additional radiation dose to patients, understanding the magnitude of this dose has become increasingly important in order to minimize its risk. While the commonly adopted radiation protection safety philosophy of As Low As Reasonably Achievable (ALARA) is also applicable for imaging dose, minimizing imaging doses by employing reasonable methods should not compromise target localization. Currently, imaging dose is not accounted for in RT treatment planning,11 and the purpose of this report is to provide imaging dose data and develop guidelines for clinicians to make informed decisions regarding the risk and benefits of x-ray image guidance. The report of AAPM TG-751 provided dose estimates for a variety of image guidance techniques and recommended strategies for minimizing imaging dose while improving treatment delivery. TG-75 also identified the need to manage imaging dose for the large number of current and emerging

imaging techniques in RT. These techniques include CT; 4DCT; diagnostic x-ray imaging; in-room CT; dual radiographic x-ray imaging; fluoroscopy; and portal imaging, either using film or an electronic portal imaging device (EPID), in various modes. This report is intended to complement the AAPM TG-75 report.1 It contains updated dose data resulting from current image acquisition procedures and modalities and addresses current issues in estimating and accounting for imaging dose during treatment planning when required. It also addresses how to minimize dose due to imaging procedures, and provides recommendations for incorporating suggestions made in AAPM TG-751 and ICRP-102.12 This report also offers guidelines for commissioning imaging beams in order to provide patient-specific imaging dose calculations when needed. The imaging dose referred to in this report is absorbed dose to medium (e.g., dose to bone or dose to soft tissue), which differs from the effective dose metric used in TG-75. Effective dose, as defined by the ICRP,13 is based on an estimate of biological effect integrated over the entire patient body, requiring a detailed knowledge of the radiation energy spectrum and irradiation geometry. Most treatment planning systems (TPSs) are not capable of calculating and displaying kV energy range dose distributions without special research tools, nor are they capable of converting calculated absorbed dose to effective dose and displaying the results. Thus, in order to avoid this additional level of complexity, absorbed dose is used in this report rather than effective dose. The magnitude of imaging dose is dependent on many factors, including the frequency of imaging and the technique used. For a single treatment fraction, two or more planar images or one or more volumetric acquisitions may be acquired. In the case of the Brainlab AG (Feldkirchen, GERMANY) ExacTrac14,15 or Accuray, Inc. (Sunnyvale, CA) CyberKnife systems,16,17 the number of planar image acquisitions per session can potentially be well over 80, even for none of the SRS/SBRT treatments, as frequent imaging is typical for monitoring patient position. Each of these imaging procedures deliver additional radiation dose to normal tissue.1,18–25 Depending on the imaging protocols and techniques used there are large variations in the imaging dose delivered to the patient. In general, MV imaging delivers higher doses than kV imaging.26 With the exception of MV volumetric imaging, a single image acquisition can deliver a dose of 0.1–5.0 cGy to the patient depending on the imaging modality. However, even with demonstrated progress in dose reduction,21,25,27–41 the kV-CBCT procedure employed for pelvic imaging can add a cumulative dose of 1–3% of the prescription dose during the course of treatment. Since the photoelectric effect is the dominant photon interaction process for kV imaging, the imaging dose to bony structures is a factor of 2–4 greater than that to soft tissue.20,21,29 For an MV-CBCT image acquisition, the imaging dose can be greater than 10 cGy, depending on the imaging site and clinical protocol.23,42–45 With all imaging procedures, the imaged volume is generally larger than the treatment volume, and tissues and organs outside the

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Ding et al.: Image Guidance Doses to Radiotherapy Patients

therapeutic beams are exposed to imaging radiation. These imaging doses to organs outside the treatment volume also need to be managed, as they may present an increased risk, especially in the case of pediatric patients. In this report, we review a variety of methods for determining x-ray imaging dose. For kV-CBCT imaging dose, these include experimental phantom measurements,19,38,46,47 in vivo measurements on patients,48 and Monte Carlo (MC) calculations.21,22,25–27,29,30,40,49–52 Commercially available treatment planning systems with user modifications, as well as mathematical models,39 have been used to calculate the MV-CBCT42,45 and kV-CBCT53,54 dose. Measurements have been used to estimate doses from 2D kV radiographs,32,38 kV-CBCT,21,27–41 MV portal images,26,32,38 MV23,42,44 55,56 and MVCT. CBCT, In radiation therapy the prescribed therapeutic dose represents the minimum dose to part or all of the planning target volume. In developing strategies for managing the imaging dose, this task group considers 5% of the therapeutic target dose to be the threshold beyond which imaging dose should be accounted for in the treatment planning process. Dische et al.57 stated that there was evidence from published clinical data and a suggestion from an analysis of the Continuous Hyperfractionated, Accelerated Radiotherapy (CHART) pilot study data58 that dose variations as small as 5% may lead to real variations in both tumor response and the risk of morbidity.59 Many studies on accuracy requirements in radiotherapy have recommended an accuracy level of 5% in the delivery and determination of dose to tumors and normal tissue.60–65 Hence, the choice of a 5% threshold is based on considerations of clinical relevance, accuracy of dose calculation and delivery, dose tolerances for critical organs, and feasibility in clinical practice. Data currently available in the literature, and quoted throughout this report, for patient populations undergoing IGRT indicate that imaging dose is generally less than 5% of the therapeutic target dose,26,32,66,67 except for some imaging procedures that use MV beams, particularly MV-CBCT.42 Balancing ALARA principles with the requirement for effective target localization, however, requires the imaging dose to be managed on the consideration of weighing risks and benefits to the patient. 2. OVERVIEW OF DOSE RESULTING FROM IMAGE GUIDANCE PROCEDURES 2.A. Megavoltage beam imaging Megavoltage imaging modalities capture projection images using either electronic portal imaging devices (EPIDs) [Fig. 1(a)] or, in the case of MVCT in the Tomotherapy HiArt Radixact system (Accuray Inc., Sunnyvale, CA),55,68,69 a single-row CT detector. A typical pair of orthogonal 6 MV portal images acquired using an EPID results in a dose distribution like the one shown in Fig. 1(b), and organ doses of 1– 5 cGy (Tables Ia–Ic) while the imaging dose from a 2.5-MV image beam70 is about 50% of that from a 6-MV beam. Medical Physics, 0 (0), xxxx

Volumetric MV-CBCT images are reconstructed using projections acquired with the EPID and result in a greater dose than a pair of orthogonal MV portal images. Reported doses per monitor unit for MV-CBCT delivered to regions and organs typically considered are listed in Table Id.45 Monitor unit values ranging from 2 to 15 have been reported in the literature.42–45,71 Typically the head and neck region is imaged with lower monitor unit protocols (2–5 MU) than the thoracic or pelvic regions, which may be imaged at up to 15 MU. Figure 2 shows an MV-CBCT dose distribution for a pelvic patient imaged at 15 MU for reference. The Siemens kView system provides the option to improve MV-CBCT image quality per unit dose by generating the imaging beam with a low Z (carbon) electron target and a 4.2-MeV electron beam, increasing the percentage of kilovoltage photons in the imaging beam considerably relative to MV-CBCT acquired with a conventional 6-MV beam generated with a tungsten target.72 With the kView system it is possible to obtain the same contrast-to-noise ratio as conventional MV-CBCT at about one-third the imaging dose.73 Organ-specific kView CBCT doses reported by Beltran74 and Dzierma et al.75 ranged from 0.6 cGy to 1.2 cGy/ MU. Image doses from kView based MV-CBCT per monitor unit are generally less than those of conventional 6-MV beams.44,73–80 Table Ie shows measured Tomo MVCT doses at the center of a 30-cm water phantom. Doses range from 0.8 to 2.5 cGy and depend on the acquisition mode. 2.B. Kilovoltage beam imaging Current kV imaging devices are generally integrated into linear accelerators and are capable of acquiring both 2D radiographs and 3D volumetric kV-CBCT images.8,81–83 Examples of kV-CBCT scanners integrated into a Varian Medical Systems, Inc. (Palo Alto, CA) On Board Imaging (OBI) system and an Elekta (Stockholm, Sweden) X-Ray Volume Imaging (XVI) system are shown in Fig. 3. Using MC methods to simulate an earlier version of the kV-CBCT scanner on the Varian OBI system (Varian OBI 1.3), Ding et al. reported21 the imaging doses received by patients from kV-CBCT scans of different treatment sites, including head and neck, chest, and abdomen. The imaging doses resulting from a single kV-CBCT procedure were 1–9 cGy to soft tissues and 6–29 cGy to bones and depended on the patient size and the site of the scan.21 Since the introduction of kV imaging systems, progress has been made by the vendors to reduce the imaging dose29 while maintaining or improving image quality. Examples of these efforts include better reconstruction techniques, improved software implementation, and the use of lower beam energies (100 and 110 kVp, in addition to the standard 125 kVp x rays), where beam energy is optimized for the size of the patient and the atomic number of the structures being imaged.85 Newer kV-CBCT acquisition techniques, which utilize 200 degree scans (instead of 370 degree ones), were introduced to reduce the imaging dose to patients for head and pelvis scans.29

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(a)

(b)

FIG. 1. (a) Conventional electronic portal imaging device (EPID) and (b) typical dose distributions and organ dose-volume histograms (DVHs) resulting from an orthogonal pair of 6 MV portal images (2 MU per image). Reproduced from Ding and Munro.26 TABLE IA. Typical organ doses for the head and neck treatment site with MV EPID portal imaging. D50 is minimum dose delivered to 50% of the organ volume (from Reference [26] for 6 MV beam and Reference [70] for 2.5 MV beam). These are for a typical pair of orthogonal setup fields (2 MU/field for 6 MV and 1 MU for 2.5 MV).

TABLE IB. Typical organ doses for the chest treatment site with MV EPID portal imaging (from References [26] and [70]) for a typical pair of orthogonal setup fields (2 MU/field for 6 MV and 1 MU for 2.5 MV). Chest D50 range (cGy)

Brain D50 range (cGy) Organ

6 MV

2.5 MV

Brain

2.0–5.0

1.0–2.0

Brainstem

3.0–4.0

1.0–2.0

Chiasm

3.0–5.0

1.2–2.0

Eyes

3.0–5.0

1.3–2.0

Optic Nerves

3.0–5.0

1.0–2.0

Pituitary

2.0–5.0

1.0–2.0

This not only reduces CBCT acquisition times, but results in a nonuniform exposure of the patient with the potential to avoid irradiating superficial critical structures.29 These

Organ

6 MV

Aorta

2.0–4.0

1.0–2.0

Lungs

1.0–4.5

0.5–2.0

Esophagus

2.5–3.5

–

Kidney Heart

2.0–3.0 3.0–4.5

– 1.0–1.5

Liver

1.0–4.5

Spinal Cord

2.0–3.0

2.5 MV

0.5–1.0

improvements have reduced imaging dose by more than an order of magnitude in some cases. Figures 4–6 compare dose distributions between kV-CBCT scanners on newer

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TABLE IC. Typical organ doses for the pelvis treatment site with MV EPID portal imaging (from Reference [26] and [70]) for a typical pair of orthogonal setup fields (2 MU/field for 6 MV and 1 MU for 2.5 MV).

5 TABLE IE. Tomo MVCT dose at the center of a 30-cm water phantom and its dependency on acquisition protocols. MVCT in Tomo

Pelvis

Acquisition mode D50 range (cGy)

Dose (cGy)

Fine pitch (4 mm couch travel/rotation)

2.5 cGy

Organ

6 MV

2.5 MV

Normal pitch (8 mm couch travel/rotation)

1.2 cGy

Bladder

2.0–3.5

1.0–1.5

Coarse pitch (12 mm couch travel/rotation)

0.8 cGy

Bowel

2.0–4.0

1.0–1.5

Femoral heads

2.5–3.5

0.8–1.5

Prostate

3.5–3.5

0.9–1.1

Rectum

2.0–4.0

0.8–1.0

TABLE ID. MV-CBCT doses per monitor unit using a 6 MV treatment beam with an acquisition arc of 200 degrees, starting at 270 degrees and stopping at 110 degrees (from Reference [45]).

Location Cranium Total-brain

Isocenter dose (cGy/MU) 0.88 0.01

Left lens Left eye 0.81 0.06

Total lung Heart

1.13 0.03

1.18 0.01

1.13 0.01 0.85 0.06 0.80 0.06

Soft Tissue 0.75 0.04

1.18 0.01

1.25 0.03

1.15 0.06 1.11 0.04 1.15 0.05

0.80 0.08

0.61 0.08

0.86 0.15

0.80 0.14

0.95 0.09

0.61 0.09

Varian OBI systems (OBI 1.4/1.5) and on a previous version of the Varian OBI system (OBI 1.3).26,29 When two orthogonal planar kV images are sufficient for an image guidance task, 2D radiographs are often used. The doses resulting from 2D kV imaging, investigated using multiple methods,26,32,38 have been shown to be much lower compared to those from volumetric kV-CBCT26 procedures. Figure 7 shows typical dose distributions resulting from a pair of orthogonal planar images in head, thorax, and pelvis scans.26 Similar lower doses, on the order of 0.1 cGy, were reported for fixed double x-ray tube systems that use projected images for patient localization, such as the Brainlab ExacTrac 14,15 and the Accuray CyberKnife.16,17

1.19 0.01

1.16 0.01

0.59 0.10

0.86 0.15

Vertebral bodies

Femoral heads

1.16 0.01

0.83 0.06

Spinal canal

Pelvis

0.90 0.01

1.16 0.01

Right eye Left lung Right lung

Maximum organ dose (cGy/MU)

1.15 0.03

Right lens

Thorax

Average organ dose (cGy/MU)

From Edward Chao, Accuray Incorporated and T. Rock Mackie, UW, Madison, WI.

1.10 0.06

1.25 0.03 1.25 0.01

3. DOSE CALCULATION ALGORITHMS FOR KV AND MV IMAGING DOSE 3.A. Monte Carlo-based methods Monte Carlo (MC) techniques for simulating dosimetry problems have evolved considerably over the last three decades86 and are regarded as the gold standard in dose calculations. The development of a special purpose MC code, BEAM,87,88 made it practical to simulate megavoltage and kilovoltage beams. With many improvements in both accuracy and computational efficiency,87,89 MC techniques have been used to characterize therapeutic megavoltage beams from linear accelerators and kilovoltage photon beams from x-ray units.21,25,51,84,86,88,90–92 Given these capabilities, MC simulations have been used to calculate realistic imaging dose distributions in patients resulting from different x-ray imaging systems.21,22,25,27,29,30,40,49–51 These studies provide detailed information about patient organ dose resulting from different image guidance procedures. Although a number of commercial treatment planning systems incorporate MC calculations for MV beams, none currently allow MC calculations for kV beams. 3.B. Model-based methods

FIG. 2. Dose distribution resulting from an MV-CBCT localization procedure of a prostate cancer patient using a 15 MU imaging protocol with a 6 MV beam. Reproduced from Miften et al.42 It is worth noting that the asymmetric dose distribution is because the scan is acquired with a gantry rotation of 200 degrees. Medical Physics, 0 (0), xxxx

Model-based dose calculation algorithms were developed for accurate MV beam dose calculations and are commonly implemented in commercial treatment planning systems.93 When an imaging procedure uses MV beams, these algorithms are capable of accurately calculating the imaging dose.

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(a)

(b)

“wedge” to mimic the isodose tilt of a half fan/half-bow tie imaging beam in the treatment planning system. Further work in this area has demonstrated that this could also be achieved by inserting a compensator in the beam.99 The same commercial TPS has also been used to model kV beams from Elekta XVI and Siemens kVision imaging systems.100,101 In general, use of these algorithms produces dose distributions of sufficient accuracy, except in and around bony structures. A proposed correction method, the Medium-Dependent Correction (MDC) approach,102 accounts for atomic number dependency when computing kV dose distributions and can potentially increase the accuracy of kV imaging dose calculations to an acceptable 10–20%.94,95 With additional improvements in commercial TPSs, therefore, it may become feasible to use the same model-based algorithms to calculate doses from both an MV therapeutic beam and a kV imaging beam. 4. KILOVOLTAGE IMAGING BEAM DOSIMETRY Unlike MV imaging beams that can be easily added to treatment plans for dose calculation purposes, kV imaging beams generally require commissioning in treatment planning systems. As indicated above, current commercial treatment planning systems do not accommodate the addition of kV imaging beams in routine clinical practice. Considering that kV imaging dose calculation in treatment planning systems may become possible in the future, however, guidance is provided in Sections 4.A and 4.B to address kV imaging beam data acquisition. 4.A. Input data for kV x-ray beam characterization

FIG. 3. kV image devices integrated into linear accelerators: (a) Varian OBI system on a Varian Trilogy treatment unit, Reproduced from Ding at el.84; (b) Elekta XVI on an Elekta Synergy treatment unit.

Morin et al.43 and Miften et al.42 calculated the imaging dose from MV-CBCT using two different treatment planning systems and reported dose calculation accuracy of better than 3%. The dose from the Siemens’ kView system has been computed using a commercial treatment planning system44,76 by implementing the kView beam spectrum given by Faddegon et al.72 in the TPS. It is feasible to use model-based dose calculation algorithms to perform dose calculations for kV-range beams, but there are inherent inaccuracies in the approach. Commercially available model-based algorithms underestimate dose to bone by up to 300%94,95 when used for kV beams due to the fact that they do not account for photoelectric effect.21,93,96,97 Alaei et al. demonstrated the feasibility of modifying an existing MV model-based dose calculation algorithm in a commercial TPS to calculate kV-CBCT dose.53 This required the addition of low-energy deposition kernels98 which accounted for the density effect of bone but not the photoelectric effect. In addition, unlike MV beams, modeling kV beams in a planning system requires beam data for the respective kV system, a topic which is further discussed in Section 5. In reference 51, Alaei et al. used a

Characterizing kV imaging beams in a planning system requires collecting beam data, including depth-dose curves, cross-profiles, and the absolute dose resulting from an image acquisition procedure. There are inherent challenges in collecting data for kV imaging beams due to the low radiation dose rate and the strong dependence on the medium in which the measurements are made. To overcome these challenges, experimentally validated MC-simulated beam data can be used.53,84,103 Caution should be taken when using the beam data generated from MC simulations, as they will depend on the simulation parameters. 4.B. Output of a kV imager The beam output should be collected by the clinical physicist using a proper detector calibration and data collection protocol. Although a method for determining kV absorbed dose with a calibrated ionization chamber based on x-ray beam specifiers, such as half-value layer (HVL) and kVp, is available from dosimetry protocols,104–106 the calibration conditions recommended in these dosimetry protocols are often not applicable to imaging acquisition procedures, especially when the x-ray source is moving during the scan. It is known that water is the most suitable medium for kV x-ray beam measurements. However, plastic phantom materials are more convenient. A method to determine the output

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(a)

(b)

(d) 100 90

70 60

Left eye

Bone

Right eye

Brain

Body

30 20

Spinal cord

70 60

Brain

50 40

Bone

Right eye

Body

10 0

Standard Dose Head: OBI 1.4

Spinal cord

% volume

(e) 100

Head Scan: OBI 1.3

10 0

10 dose /cGy

(c)

% volume

Left eye 0.0

0.5

1.0 dose /cGy

1.5

2.0

(f) 100 90 80 70 60 50 40 30 20 10 0

Head OBI 1.4

Left eye Right eye Spinal cord

0.0

0.1

0.2

0.3

0.4

0.5

0.6

0.7

0.8

dose /cGy

FIG. 4. Typical doses for a head scan shown in color wash along with dose-volume histograms (DVHs) for radiosensitive organs for the Varian OBI 1.3 (a,d); for the OBI 1.4 during a Standard-Dose Head scan (b,e), where the x-ray source is positioned below the patient; and for the OBI 1.4 during a head scan with the xray source positioned above the patient (c,f—dashed lines). The solid lines in (f) are reproduced from (e) and show the quantitative effect of rotating the x-ray source from the back to the front of the patient. Note that the abscissa in (d) is 10 times larger than in (e). Reproduced from Ding et al.29 (Scanning parameters are listed Table IId).

resulting from a specific image acquisition procedure has been described103 where the effect of using different plastic phantom materials in the kV energy range is investigated. This study includes two water equivalents, Plastic Water – Low Energy Range (PW-LR–CIRS, Inc., Norfolk, VA) and Solid Water (Gammex, Inc., Middleton, WI), along with the less water-equivalent polymethyl methacrylate (PMMA). Caution should be used when interpreting the measured data from solid water-equivalent and PMMA phantoms to determine the output of a kV beam, as the uncertainties can be significant (8–20%).103 The considerations for a suitable phantom include phantom size relative to x-ray field size, beam attenuation by the phantom, and availability. For cases where fluoroscopy mode is used instead of radiography mode for acquiring 2D kV planar images, the imaging dose is proportional to the x-ray exposure times for the selected imaging protocol parameters (kVp and mA), and doses can be estimated based on the product of dose rate and scan time for the kV beam. The output of a kV beam can be obtained in air or in a phantom as recommended in the AAPM dosimetry protocol for kV beams.106 When measured in air, the beam output is insensitive to the field size used. When measured in a phantom, the beam output is affected by the phantom scatter, which depends on the field size. If the beam cannot be delivered in static mode, rotational absorbed dose can be measured utilizing a cylindrical chamber placed at the isocenter. Medical Physics, 0 (0), xxxx

4.C. In vivo dosimetry If patient-specific imaging dose verification is desired, in vivo patient dose measurements can be performed using available detectors such as diodes, thermoluminescent dosimeters (TLDs), or optically stimulated luminescent dosimeters (OSLDs).48,107,108 Dosimeters, such as diodes, that are intended for use in MV beam in vivo measurements are not suitable for kV beams as they include inherent buildup. In addition, their response to kV radiation is significantly different from MV beams. Dosimeters that are used for kV beams should be calibrated for the beam energy used.48 In vivo measurements using detectors placed on the patient’s skin may be used to estimate organ dose once detector response has been scaled by the known dose distribution inside the patient.48 There have been many publications discussing the use of TLDs, OSLDs, MOSFETs, and other detectors in kV beams.48,109–112 5. METHODS OF ACCOUNTING FOR IMAGING DOSE Many different methods have been used to calculate the imaging dose delivered to RT patients.1,11,18,19,21–23,25,51 When there is reasonable expectation that the imaging dose will exceed 5% of the total prescribed dose, two methods can

Ding et al.: Image Guidance Doses to Radiotherapy Patients

(a)

(b)

(d)

100 90

Pelvis: Full scan length

100

Left femur head

60 50

Body

40 30

Rectum

20 0

dose /cGy

3 Left femur head

Body

Righ femur head

50 40 20

Prostate

Bladder

Dose profiles in axial direction

Pelvis: 5 cm scan length

Righ femur head

% volume

(e)

Bladder

Rectum

10 Prostate 0 0 1

dose /cGy

(c)

Standard scan length (17 cm) Scan length set to 10 cm Scan length set to 5 cm

-10

-5

z-axis /cm

FIG. 5. The effect of reducing the scanned length: (a) Dose distributions shown in colorwash for default Pelvis scan length (16 cm); (b) reduced Pelvis scan length (5 cm); (c, d) Corresponding dose-volume histograms for the specific organs resulting from respective scans; (e) Dose profiles in the inferior–superior direction along the line AB shown in Figure (a,b) across the irradiated volume for 16 cm (standard scan length), 10 cm, and 5 cm, respectively. The direction of z-axis is from inferior to superior in (e). The peak at the right in (e) represents the dose as the line AB crosses into the sacral vertebral body (bone). Note that reducing the scan length of the CBCT scan reduces both the maximum dose and the volume that is exposed to radiation. Reproduced from Ding et al.29 (Scanning parameters are listed Table IId).

be used to manage it: patient-specific dose calculations and nonpatient-specific dose estimations. 5.A. Patient-speciﬁc imaging dose calculations Patient-specific imaging dose calculations are based on patient CT images67,113 and provide individualized organ doses, since the dose resulting from image guidance procedures will vary depending on the patient size as well as image location.21,54,67 In order to perform patient-specific imaging dose calculations in a treatment planning system, the beams used for imaging procedures must be characterized as part of the commissioning process. The process of characterizing MV imaging beams in a treatment planning system is straightforward in cases where

the imaging beam is the same as the therapeutic beam, allowing imaging dose to be calculated according to the monitor units and field sizes used in image acquisition. Imaging dose can then be added to therapeutic dose directly during treatment planning. Moreover, if the total number of imaging procedures is known at the planning stage, the imaging dose can be accounted for when optimizing patient treatment plans for total dose to the target and OARs. Miften et al. demonstrated this approach42 by showing optimized IMRT plans with and without MV-CBCT included in the process. This, along with the lack of MC simulations or model-based algorithms capable of handling kV beams in commercial TPSs,53 currently precludes patient-specific imaging dose calculations for any other than therapeutic MV beams.

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(a)

(b)

(d)

100

Low Dose Thorax: OBI 1.4

% volume

100

Bone

60 50

Heart Left lung Right lung Spinal cord

40 30

Body

Bone

Heart Left lung Right lung Spinal cord

50 40 30

Body

20 10

10 0

Chest: OBI 1.3

% volume

(c)

dose /cGy

FIG. 6. Axial, frontal, and sagittal views showing dose distributions resulting from (a) OBI 1.4 low-dose thorax scan and (b) OBI 1.3 scan. The corresponding dose-volume histograms for different organs are shown for the low-dose scan (c) and the OBI 1.3 scan (d). Note that the horizontal scales in (c) and (d) differ by a factor of 5. Reproduced from Ding et al.29 (Scanning parameters are listed Table IId).

5.B. Nonpatient-speciﬁc imaging dose estimations Given the small magnitude of imaging dose relative to therapeutic dose,26,113 it may be adequate to use simpler approaches that provide reasonable estimates of the imaging dose. It has been shown Ref. [54,67] that interpatient variation and geometry dependence are small in most cases and that dose estimates could be provided in the form of simple look-up tables, which may be accurate enough to estimate the dose from repeat imaging procedures. Such tabulated values67,113 can provide clinicians with adequate estimates of Medical Physics, 0 (0), xxxx

100

imaging dose to organs. Tables IIa, IIb, IIc, IId, IIe, and IIIa, IIIb, IIIc list representative organ doses resulting from kVCBCT scans in the Varian OBI and Elekta XVI systems for different treatment sites and scan protocols. Note that bow tie filters used in the kV-CBCT acquisition not only improve image quality but also significantly reduce imaging dose.26 These tabulated values, when scaled by the mAs used for image acquisition, are sufficient to estimate imaging dose to within 20%67 and can assist the clinician in: (a) determining if the imaging doses are expected to be close to the 5% threshold, (b) choosing a suitable IGRT protocol, and (c)

Ding et al.: Image Guidance Doses to Radiotherapy Patients

(a)

(b)

(c)

FIG. 7. Imaging dose from a pair of orthogonal planar kV images for (a) head, (b) chest, and (c) pelvis images using the Varian OBI system.26 (Parameters for kV radiographs for specified acquisition techniques are listed in Table IId). Medical Physics, 0 (0), xxxx

101

Ding et al.: Image Guidance Doses to Radiotherapy Patients

TABLE IIA. Organ doses for the head and neck and brain treatment sites from Varian OBI v1.4 using Standard Head kV-CBCT scan. D50 and D10 are minimum dose delivered to 50% and 10% of the organ volume, respectively. (From Reference [67] and kV-CBCT scan parameters for Varian OBI 1.4 shown in Table IId).

11 TABLE IID. Parameters for kV-CBCT-specified acquisition techniques in Varian OBI 1.4 (from Reference [26]).

kV-CBCT Standard head, brain

Standard head, head and neck

Organ

D50 range (cGy)

Brain

0.21–0.33

0.27–0.40

Brain

0.15–0.22

0.16–0.23

Brainstem

0.19–0.30

0.22–0.32

Larynx

0.21–00.29

0.25–0.33

Chiasm Eyes

0.08–0.26 0.03–0.31

0.09–0.26 0.04–0.35

Oral cavity Parotids

0.13–0.26 0.26–0.42

0.20–0.31 0.31–0.48

Optic Nerves

0.05–0.27

Spinal cord

0.16–0.25

0.19–0.32

Pituitary

0.07–0.24

0.08–0.25

Thyroid

0.07–0.23

0.11–0.32

Spinal Cord Skin

0.26–0.33

0.29–0.34

Esophagus

0.07–0.16

0.14–0.26

0.19–0.41

0.39–0.63

Skin

0.18–0.27

0.34–0.44

Bones

0.45–1.11

1.13–1.67

Bones

0.25–0.65

0.64–1.07

D10 range (cGy)

Organ

D10 range (cGy)

TABLE IIB. Organ doses for the chest treatment site from Varian OBI v1.4 using the low-dose thorax kV-CBCT scan (from Reference [114] and kVCBCT scan parameters for Varian OBI 1.4 shown in Table IId). Low-dose thorax

Name

Bow tie filter

(kV)

(mAs)

Gantry rotation (degrees)

OBI

Standard-dose head

Full fan

100

145

200

OBI

Low-dose head

Full fan

100

200

OBI

High-quality head

Full fan

100

720

200

OBI OBI

Pelvis Pelvis spot light

Half fan Full fan

125 125

700 720

360 200

OBI

Low-dose thorax

Half fan

110

262

360

TrueBeam TrueBeam

Head Pelvis

Full fan Half fan

100 125

147 1056

200 360

TrueBeam

Spotlight

Full fan

125

733

200

TrueBeam

Thorax

Half fan

125

264

360

TABLE IIE. Parameters for kV radiographs for specified acquisition techniques in Varian OBI 1.4. Name

(kV)

(mAs)

Head-AP Head-Lat

100 70

8 5

Organ

D50 range (cGy)

D10 range (cGy)

Aorta

0.42–0.58

0.44–0.63

Lungs Small bowel

0.30–0.61 0.33–0.54

0.43–0.72 0.39–0.61

Thorax-AP

Thorax-Lat

Esophagus

0.29–0.60

0.35–0.74

Pelvis-AP-Med

0.49–0.59

Pelvis-Lat-Med

105

Kidney

0.43–0.54

Heart

0.31–0.55

0.41–0.63

Liver

0.31–0.51

0.38–0.61

Spinal cord

0.32–0.57

0.35–0.78

Spleen

0.32–0.52

0.36–0.60

Stomach Trachea

0.28–0.57 0.36–0.71

0.31–0.62 0.47–1.04

Skin

0.46–0.57

0.64–0.89

Bones

1.06–1.74

1.47–2.25

The clinical default OBI blades are set to X1 = X2 = 13.3 cm and Y1 = Y2 = 10.3 cm in all acquisition techniques. All six techniques were modeled with and without a full fan bow tie filter.

TABLE IIIA. Organ doses for the head and neck treatment site from Elekta XVI kV-CBCT scan using S cassettes, 100 kVp, 0.1 mAs/acquisition, 360 acquisitions, 345–190 degree (IEC) rotation (from Reference [54]). Head and neck Organ

TABLE IIC. Organ doses for the pelvis treatment site from Varian OBI v1.4 using Pelvis kV-CBCT scan. (From Reference [114] and kV-CBCT scan parameters for Varian OBI 1.4 shown in Table IId). Pelvis scan, prostate isocenter Organ

D50 range (cGy)

D10 range (cGy)

D50 range (cGy)

Brainstem

0.06–0.08

Rt eye Lt eye

0.08–0.09 0.13–0.13

Rt parotid

0.05–0.06

Lt parotid

0.16–0.17

Rt cochlea

0.04–0.05

Bladder

1.36–2.20

1.72–2.69

Lt cochlea

0.09–0.12

Bowel

1.54–1.91

2.04–2.65

Oral cavity

0.09–0.11

Femoral heads

2.40–3.60

3.22–4.88

Prostate

1.19–1.79

1.33–1.89

Rectum

1.51–1.99

1.70–2.22

Skin Bone

1.80–1.96 2.93–3.96

2.26–2.92 4.61–5.72

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accounting for the organ dose resulting from a specific image acquisition procedure over the course of treatment. Until kV dose calculations become available in commercial treatment planning systems, using estimated organ dose

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TABLE IIIB. Organ doses for the pelvis treatment site from Elekta XVI kVCBCT scan using an M cassette without a bow tie filter, 120 kVp, 1.0 mAs/ acquisition, 650 acquisitions, full 360 degree rotation (from Reference [54]). Pelvis Organ

D50 range (cGy)

Bladder

0.9–2.0

Rectum Small bowel

1.1–1.9 1.0–1.8

TABLE IIIC. Organ doses for the pelvis treatment site from Elekta XVI kVCBCT scan using an M cassette with bow tie filter, 120 kVp, 1.6 mAs/acquisition, 650 acquisitions, full 360 degree rotation (from Reference [54]). Pelvis Organ

D50 range (cGy)

Bladder

1.1–2.5

Rectum Small Bowel

1.3–2.4 1.1–2.3

tables from various imaging procedures may be an acceptable option given the expected low-dose level. 6. RECOMMENDATIONS Unlike diagnostic imaging procedures, IGRT image acqusitions are more frequent, repeated on a daily basis, and include a volume that is larger than the treated one. Proper management of imaging dose in IGRT includes adherence to ALARA principles by minimizing the dose as much as possible and accounting for it when necessary. 6.A. General recommendations (a) Create local imaging protocols, including imaging modality, technique, and frequency, that are suitable for the imaging requirements of the clinic.26 Consulting with a diagnostic imaging physicist may be helpful in this process. (b) Develop protocols that are specific for pediatric patients.29,40 (c) Communicate the imaging dose associated with IGRT protocols by site (head, thorax, abdomen, pelvis) to radiation oncologists. This enables informed decision-making for selecting imaging protocols and ensures the clinicians are aware of the imaging doses being delivered to their patients.

6.B. Imaging dose output and consistency checks (a) The anticipated imaging dose for each image acquisition procedure, with specified protocol parameters, should be measured in air or in-phantom, according to the AAPM dosimetry protocols for kV and MV beams, to confirm

that measured dose is within the manufacturer-stated specifications at the time of acceptance of the image device. Image acquisition procedures should include both those at MV and kV energies. The phantom and detectors used should be appropriate for the beam energy. Phantom sizes should be large enough to provide full x-ray scattering. (b) Consistency checks should be performed annually and after each system upgrade, and the recommendations from AAPM quality assurance reports, such as those from AAPM Task Group 142,115 should be used. Checks for imaging dose consistency in air can also be performed using commercially available tools for measuring beam parameters (i.e., kVp, mAs, etc.) that uniquely define the specific procedure. (c) If patient-specific imaging dose verification is desired for a particular patient, in vivo patient dose measurements should be performed with suitable detectors. The limited accuracy of patient-specific measurements should be taken into account in the review of the measured data.

6.C. Accounting for imaging dose to RT patients It is recommended that imaging dose be considered part of the total dose at the treatment planning stage if the dose from repeated imaging procedures is expected to exceed 5% of the prescribed target dose. Patient organ doses can be calculated or estimated by using either patient-specific or nonpatient-specific methods. Facilitation of patient-specific imaging dose calculations may require implementation of new algorithms for MV and kV beams in commercial treatment planning systems. It is acceptable for the uncertainties of calculated imaging doses to reach 20%, because imaging dose is generally only a few percent of the prescribed target dose. As a result, the uncertainty of the summed dose (therapeutic + imaging) will still be at a level of 2–3%. 6.D. Available techniques to reduce imaging dose to patients Depending on the imaging modality, a variety of techniques are available to reduce the imaging dose to organs at risk, as recommended by AAPM TG-751 and AAPM TG179.116 ALARA should always be the guiding principle applied in practice. At the time of this report, the following techniques are recommended: (a) Reduce the imaging field size as much as possible. This will reduce the volume of irradiated tissue surrounding the target. Reducing the cranial-caudal extent of kVCBCT scans can also significantly reduce the integral as well as scattered dose in the volume.29 (b) During patient setup for MV portal images, minimize the imaging field size without removing reference

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structures needed for patient alignment. For images acquired for documenting delivery, select “image during treatment” to avoid adding additional dose to the patient. (c) For Tomotherapy units, select MVCT scan pitch parameters that balance imaging dose with clinical need (i.e. patient positioning or adaptive planning). The imaging dose differs significantly when different pitch parameters are selected (Table Ie).56 (d) For MV-CBCT, select a patient-specific MV imaging protocol and restrict the imaging field of view (FOV). The imaging dose can be reduced if bony anatomy rather than soft tissue is used for treatment localization.78 Note that the degree of dose reduction possible will depend upon the image quality requirements of the clinicians. (e) When deciding between 2D radiographs or 3D volumetric images, consider the image requirements. As ALARA is the guiding principle, consider 2D if two planar orthogonal kV images are sufficient for the task. The organ doses from image guidance can be reduced by a factor of 10 using 2D kV imaging compared to 3D kV-CBCT.26 (f) Optimize imaging parameters (e.g., kVp, mAs) and select appropriate manufacturer-provided default clinical protocols (pelvis, abdomen, thorax, head and neck) for different normal adult body sites. In the case of pediatric patients with a small body size, default low-dose protocols for a head and neck kV-CBCT scan can be used to image a pelvic site. This reduces imaging dose by a factor of 2–3 without compromising the image quality.29 (g) The kV-CBCT scan protocols that use partial rotation provide the opportunity to selectively avoid irradiating superficial organs. Partial rotation during a head scan can be used to dramatically reduce the dose to the eyes.29 The technique can also be applied to reduce dose to the bladder or rectum for kV-CBCT scans. (h) Since the beam exit dose is only a few percent of the entry dose for kV x rays, the beam directions used for orthogonal planar images can be selected to minimize dose to critical organs.26 For a fixed orthogonal pair, consider not only 0 and 90 but also 180 and 90, 0 and 270, and 180 and 270 beam angles to minimize dose to organs at risk. (i) Consider the use of full bow tie filters when acquiring planar kV images. Bow tie filters can significantly reduce skin dose and dose to organs at risk. Always use the appropriate bow tie filter for kV-CBCT acquisition when manual placement of the filter is required, since failure to employ the filter increases the imaging dose by factors of 2–4.26 ACKNOWLEDGMENTS The members of this task group thank Greg Sharp (TISC Lead Reviewer), Ping Xia (TPC Lead Reviewer), Jeffrey Medical Physics, 0 (0), xxxx

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Siebers (External Lead Reviewer), Jeff Colvin, and Sonja Dieterich for their very helpful comments and suggestions. We thank Gig Mageras and Debra Brinkmann for their helpful guidance over the years in which this report was developed. We also thank the referees for their very helpful and constructive comments. We wish to acknowledge the support from AAPM TPC leadership and extend our thanks to the science editor for the professional proof reading of this report. Finally, we want to thank our consultants: Walter Bosch, Jun Deng, Choonsik Lee, Peter Munro and Ying Xiao for their invaluable contributions to this report. a)

Author to whom correspondence should be addressed. Electronic mail: george.ding@vanderbilt.edu.

REFERENCES 1. Murphy M, Balter JM, BenComo J, et al. The management of imaging dose during image-guided radiotherapy: Report of the AAPM Task Group 75. Med Phys. 2007;34:4041–4063. 2. Duggan DM, Ding GX, Coffey 2nd CW, et al. Deep-inspiration breath-hold kilovoltage cone-beam CT for setup of stereotactic body radiation therapy for lung tumors: initial experience. Lung Cancer. 2007;56:77–88. 3. Jaffray DA, Siewerdsen JH. Cone-beam computed tomography with a flat-panel imager: initial performance characterization. Med Phys. 2000;27:1311–1323. 4. Letourneau D, Wong JW, Oldham M, et al. Cone-beam-CT guided radiation therapy: technical implementation. Radiother Oncol. 2005;75:279–286. 5. Oldham M, Letourneau D, Watt L, et al. Cone-beam-CT guided radiation therapy: a model for on-line application. Radiother Oncol. 2005;75:271 E1–271 E278. 6. Thilmann C, Nill S, Tucking T, et al. Correction of patient positioning errors based on in-line cone beam CTs: clinical implementation and first experiences. Radiat Oncol. 2006;1:16. 7. Ding GX, Duggan DM, Coffey CW, et al. A study on adaptive IMRT treatment planning using kV cone-beam CT. Radiother Oncol. 2007;85:116–125. 8. Jaffray DA, Drake DG, Moreau M, Martinez AA, Wong JW. A radiographic and tomographic imaging system integrated into a medical linear accelerator for localization of bone and soft-tissue targets. Int J Radiat Oncol Biol Phys. 1999;45:773–789. 9. Nijkamp J, Pos FJ, Nuver TT, et al. Adaptive radiotherapy for prostate cancer using kilovoltage cone-beam computed tomography: first clinical results. Int J Radiat Oncol Biol Phys. 2008;70:75–82. 10. Pawlowski JM, Yang ES, Malcolm AW, Coffey CW, Ding GX. Reduction of dose delivered to organs at risk in prostate cancer patients via image-guided radiation therapy. Int J Radiat Oncol Biol Phys. 2010;76:924–934. 11. Ding GX, Coffey CW. Is it time to include imaging guidance doses in the reportable total radiation doses of radiotherapy patients? Int J Radiat Oncol Biol Phys. 2008;72:S145–S146. 12. ICRP-102. Managing patient dose in multi-detector computed tomography (MDCT). Ann ICRP. 2007;37:1–79. 13. ICRP-103. The 2007 Recommendations of the International Commission on Radiological Protection. ICRP Publication 103, vol. Ann. ICRP 37; 2007. 14. Lee SW, Jin JY, Guan H, Martin F, Kim JH, Yin FF. Clinical assessment and characterization of a dual tube kilovoltage X-ray localization system in the radiotherapy treatment room. J Appl Clin Med Phys. 2008;9:2318. 15. Ding G. Characteristics of x-rays from ExacTrac and patient dose from imaging procedures. Med Phys. 2015;42:3268. 16. Dieterich S, Cavedon C, Chuang CF, et al. Report of AAPM TG 135: quality assurance for robotic radiosurgery. Med Phys. 2011;38:2914–2936.

Ding et al.: Image Guidance Doses to Radiotherapy Patients

17. Sullivan A, Ding G. Additional imaging guidance dose to patient organs resulting from x-ray tubes used in CyberKnife image guidance system. Med Phys. 2015;42:3264. 18. Islam MK, Purdie TG, Norrlinger BD, et al. Patient dose from kilovoltage cone beam computed tomography imaging in radiation therapy. Med Phys. 2006;33:1573–1582. 19. Wen N, Guan H, Hammoud R, et al. Dose delivered from Varian’s CBCT to patients receiving IMRT for prostate cancer. Phys Med Biol. 2007;52:2267–2276. 20. Walters BR, Ding GX, Kramer R, Kawrakow I. Skeletal dosimetry in cone beam computed tomography. Med Phys. 2009;36:2915– 2922. 21. Ding GX, Coffey CW. Radiation dose from kilovoltage cone beam computed tomography in an image-guided radiotherapy procedure. Int J Radiat Oncol Biol Phys. 2009;73:610–617. 22. Downes P, Jarvis R, Radu E, Kawrakow I, Spezi E. Monte Carlo simulation and patient dosimetry for a kilovoltage cone-beam CT unit. Med Phys. 2009;36:4156–4167. 23. Gayou O, Parda DS, Johnson M, Miften M. Patient dose and image quality from mega-voltage cone beam computed tomography imaging. Med Phys. 2007;34:499–506. 24. Ding GX, Duggan DM, Coffey C. Additional doses to critical organs from CBCT scan in image guided radiation therapy. Int J Radiat Oncol Biol Phys. 2007;69:S45. 25. Ding GX, Duggan DM, Coffey CW. Accurate patient dosimetry of kilovoltage cone-beam CT in radiation therapy. Med Phys. 2008;35:1135–1144. 26. Ding GX, Munro P. Radiation exposure to patients from image guidance procedures and techniques to reduce the imaging dose. Radiother Oncol. Jul 2013;108:91–98. 27. Chow JC, Leung MK, Islam MK, Norrlinger BD, Jaffray DA. Evaluation of the effect of patient dose from cone beam computed tomography on prostate IMRT using Monte Carlo simulation. Med Phys. 2008;35:52–60. 28. Ding GX, Coffey CW. Dosimetric evaluation of the OneDoseTM MOSFET for measuring kilovoltage imaging dose from image-guided radiotherapy procedures. Med Phys. 2010;37:4880–4885. 29. Ding GX, Munro P, Pawlowski J, Malcolm A, Coffey CW. Reducing radiation exposure to patients from kV-CBCT imaging. Radiother Oncol. 2010;97:585–592. 30. Deng J, Chen Z, Roberts KB, Nath R. Kilovoltage imaging doses in the radiotherapy of pediatric cancer patients. Int J Radiat Oncol Biol Phys. 2012;82:1680–1688. 31. Ding G, Munro P. Reduced CBCT imaging dose due to the new x-ray source in TrueBeam . Med Phys. 2011;38:3372–3373. 32. Stock M, Palm A, Altendorfer A, Steiner E, Georg D. IGRT induced dose burden for a variety of imaging protocols at two different anatomical sites. Radiother Oncol. 2011;102:355–363. 33. Hyer DE, Hintenlang DE. Estimation of organ doses from kilovoltage cone-beam CT imaging used during radiotherapy patient position verification. Med Phys. 2010;37:4620–4626. 34. Palm A, Nilsson E, Herrnsdorf L. Absorbed dose and dose rate using the Varian OBI 1.3 and 1.4 CBCT system. J Appl Clin Med Phys. 2010;11:3085. 35. Kim S, Yoo S, Yin FF, Samei E, Yoshizumi T. Kilovoltage cone-beam CT: comparative dose and image quality evaluations in partial and fullangle scan protocols. Med Phys. 2010;37:3648–3659. 36. Kan MW, Leung LH, Wong W, Lam N. Radiation dose from cone beam computed tomography for image-guided radiation therapy. Int J Radiat Oncol Biol Phys. 2008;70:272–279. 37. Shah A, Aird E, Shekhdar J. Contribution to normal tissue dose from concomitant radiation for two common kV-CBCT systems and one MVCT system used in radiotherapy. Radiother Oncol. 2012;105:139– 144. 38. Walter C, Boda-Heggemann J, Wertz H, et al. Phantom and in-vivo measurements of dose exposure by image-guided radiotherapy (IGRT): MV portal images vs. kV portal images vs. cone-beam CT. Radiother Oncol. 2007;85:418–423. 39. Jeng SC, Tsai CL, Chan WT, Tung CJ, Wu JK, Cheng JC. Mathematical estimation and in vivo dose measurement for cone-beam computed tomography on prostate cancer patients. Radiother Oncol. 2009;92:57–61. TM

14 40. Zhang Y, Yan Y, Nath R, Bao S, Deng J. Personalized assessment of kV cone beam computed tomography doses in image-guided radiotherapy of pediatric cancer patients. Int J Radiat Oncol Biol Phys. 2012;83:1649–1654. 41. Perks JR, Lehmann J, Chen AM, Yang CC, Stern RL, Purdy JA. Comparison of peripheral dose from image-guided radiation therapy (IGRT) using kV cone beam CT to intensity-modulated radiation therapy (IMRT). Radiother Oncol. 2008;89:304–310. 42. Miften M, Gayou O, Reitz B, Fuhrer R, Leicher B, Parda DS. IMRT planning and delivery incorporating daily dose from mega-voltage cone-beam computed tomography imaging. Med Phys. 2007;34:3760– 3767. 43. Morin O, Gillis A, Descovich M, et al. Patient dose considerations for routine megavoltage cone-beam CT imaging. Med Phys. 2007;34:1819–1827. 44. Flynn RT, Hartmann J, Bani-Hashemi A, et al. Dosimetric characterization and application of an imaging beam line with a carbon electron target for megavoltage cone beam computed tomography. Med Phys. 2009;36:2181–2192. 45. VanAntwerp AE, Raymond SM, Addington MC, Gajdos S, Vassil A, Xia P. Dosimetric evaluation between megavoltage cone-beam computed tomography and body mass index for intracranial, thoracic, and pelvic localization. Med Dosim. 2011;36:284–291. 46. Tomic N, Devic S, DeBlois F, Seuntjens J. Comment on “reference radiochromic film dosimetry in kilovoltage photon beams during CBCT image acquisition” [Med. Phys. 37, 1083-1092 (2010)]. Med Phys. 2010;37:3008. 47. Hyer DE, Serago CF, Kim S, Li JG, Hintenlang DE. An organ and effective dose study of XVI and OBI cone-beam CT systems. J Appl Clin Med Phys. 2010;11:3183. 48. Ding GX, Malcolm AW. An optically stimulated luminescence dosimeter for measuring patient exposure from imaging guidance procedures. Phys Med Biol. 2013;58:5885–5897. 49. Zhang Y, Yan Y, Nath R, Bao S, Deng J. Personalized estimation of dose to red bone marrow and the associated leukaemia risk attributable to pelvic kilo-voltage cone beam computed tomography scans in image-guided radiotherapy. Phys Med Biol. 2012;57:4599–4612. 50. Deng J, Chen Z, Yu JB, Roberts KB, Peschel RE, Nath R. Testicular doses in image-guided radiotherapy of prostate cancer. Int J Radiat Oncol Biol Phys. 2011;82:e39–e47. 51. Spezi E, Downes P, Radu E, Jarvis R. Monte Carlo simulation of an xray volume imaging cone beam CT unit. Med Phys. 2009;36:127–136. 52. Ding A, Gu J, Trofimov AV, Xu XG. Monte Carlo calculation of imaging doses from diagnostic multidetector CT and kilovoltage cone-beam CT as part of prostate cancer treatment plans. Med Phys. 2010;37:6199–6204. 53. Alaei P, Ding GX, Gua H. Inclusion of the dose from kilovoltage cone beam CT in the radiation therapy treatment plans. Med Phys. 2010;37:244–248. 54. Alaei P, Spezi E, Reynolds M. Dose calculation and treatment plan optimization including imaging dose from kilovoltage cone beam computed tomography. Acta Oncol. 2014;53:839–844. 55. Mackie TR, Kapatoes J, Ruchala K, et al. Image guidance for precise conformal radiotherapy. Int J Radiat Oncol Biol Phys. 2003;56:89–105. 56. Meeks SL, Harmon Jr JF, Langen KM, Willoughby TR, Wagner TH, Kupelian PA. Performance characterization of megavoltage computed tomography imaging on a helical tomotherapy unit. Med Phys. 2005;32:2673–2681. 57. Dische S, Saunders MI, Williams C, Hopkins A, Aird E. Precision in reporting the dose given in a course of radiotherapy. Radiother Oncol. 1993;29:287–293. 58. Saunders MI, Dische S, Grosch EJ, et al. Experience with CHART. Int J Radiat Oncol Biol Phys. 1991;21:871–878. 59. ICRU-62. “Prescribing, recording and reporting photon beam therapy (supplement to ICRU report 50),” Bethesda. USA; 1999. 60. Brahme A. Dosimetric precision requirements in radiation therapy. Acta Radiol Oncol. 1984;23:379–391. 61. Dutreix A. When and how can we improve precision in radiotherapy? Radiother Oncol. 1984;2:275–292. 62. Mijnheer BJ, Battermann JJ, Wambersie A. What degree of accuracy is required and can be achieved in photon and neutron therapy? Radiother Oncol. 1987;8:237–252.

Medical Physics, 0 (0), xxxx

105

Ding et al.: Image Guidance Doses to Radiotherapy Patients

63. Svensson H. Quality assurance in radiation therapy: physical aspects. Int J Radiat Oncol Biol Phys. 1984;10:59–65. 64. Wambersie A. What accuracy is required and can be achieved in radiation therapy (review of radiobiological and clinical data). Radiochim Acta. 2001;89:255–264. 65. Brahme A, Chavaudra J, Landberg T, et al. Accuracy requirements and quality assurance of external beam therapy with photons and electrons. Acta Oncol Suppl. 1988;1:5–76. 66. Kudchadker RJ, Chang EL, Bryan F, Maor MH, Famiglietti R. An evaluation of radiation exposure from portal films taken during definitive course of pediatric radiotherapy. Int J Radiat Oncol Biol Phys. 2004;59:1229–1235. 67. Nelson AP, Ding GX. An alternative approach to account for patient organ doses from imaging guidance procedures. Radiother Oncol. 2014;112:112–118. 68. Mackie TR, Balog J, Ruchala K, et al. Tomotherapy. Semin Radiat Oncol. 1999;9:108–117. 69. Mackie TR, Holmes T, Swerdloff S, et al. Tomotherapy: a new concept for the delivery of dynamic conformal radiotherapy. Med Phys. 1993;20:1709–1719. 70. Ding GX, Munro P. Characteristics of 2.5MV beam and imaging dose to patients. Radiother Oncol. 2017;125:541–547. 71. Morin O, Aubry JF, Aubin M, et al. Physical performance and image optimization of megavoltage cone beam CT. Med Phys. 2009;36:1421–1432. 72. Faddegon BA, Wu V, Pouliot J, Gangadharan B, Bani-Hashemi A. Low dose megavoltage cone beam computed tomography with an unflattened 4 MV beam from a carbon target. Med Phys. 2008;35:5777–5786. 73. Breitbach EK, Maltz JS, Gangadharan B, et al. Image quality improvement in megavoltage cone beam CTusing an imaging beam line and a sintered pixelated array system. Med Phys. 2011;38:5969–5979. 74. Beltran C. Image quality of an investigational imaging panel for use with the imaging beam line cone-beam CT. J Appl Clin Med Phys. 2012;13:3607. 75. Dzierma Y, Ames E, Nuesken F, Palm J, Licht N, Rube C. Image quality and dose distributions of three linac-based imaging modalities. Strahlenther Onkol. 2015;191:365–374. 76. Dzierma Y, Nuesken FG, Licht NP, Ruebe C. Dosimetric properties and commissioning of cone-beam CT image beam line with a carbon target. Strahlenther Onkol. Jul 2013;189:566–572. 77. Beltran C, Lukose R, Gangadharan B, Bani-Hashemi A, Faddegon BA. Image quality & dosimetric property of an investigational imaging beam line MV-CBCT. J Appl Clin Med Phys. 2009;10:3023. 78. Faddegon BA, Aubin M, Bani-Hashemi A, et al. Comparison of patient megavoltage cone beam CT images acquired with an unflattened beam from a carbon target and a flattened treatment beam. Med Phys. 2010;37:1737–1741. 79. Sawkey D, Lu M, Morin O, et al. A diamond target for megavoltage cone-beam CT. Med Phys. 2010;37:1246–1253. 80. Fast MF, Koenig T, Oelfke U, Nill S. Performance characteristics of a novel megavoltage cone-beam-computed tomography device. Phys Med Biol. 2012;57:N15–N24. 81. Shiu AS, Chang EL, Ye JS, et al. Near simultaneous computed tomography image-guided stereotactic spinal radiotherapy: an emerging paradigm for achieving true stereotaxy. Int J Radiat Oncol Biol Phys. 2003;57:605–613. 82. Uematsu M, Fukui T, Shioda A, et al. A dual computed tomography linear accelerator unit for stereotactic radiation therapy: a new approach without cranially fixated stereotactic frames. Int J Radiat Oncol Biol Phys. 1996;35:587–592. 83. Yenice KM, Lovelock DM, Hunt MA, et al. CT image-guided intensity-modulated therapy for paraspinal tumors using stereotactic immobilization. Int J Radiat Oncol Biol Phys. 2003;55:583–593. 84. Ding GX, Duggan DM, Coffey CW. Characteristics of kilovoltage xray beams used for cone-beam computed tomography in radiation therapy. Phys Med Biol. 2007;52:1595–1615. 85. Kalender WA, Deak P, Kellermeier M, van Straten M, Vollmar SV. Application- and patient size-dependent optimization of x-ray spectra for CT. Med Phys. 2009;36:993–1007. 86. Verhaegen F, Seuntjens J. Monte Carlo modelling of external radiotherapy photon beams. Phys Med Biol. 2003;48:R107–R164.

Medical Physics, 0 (0), xxxx

106

15 87. Kawrakow I, Rogers DWO. The EGSnrc Code System: Monte Carlo Simulation of Electron and Photon Transport. Ionizing Radiation Standards, National Research Council of Canada, NRCC Report PIRS-701, Ottawa NRCC Report PIRS-701; 2002. 88. Rogers DWO, Faddegon BA, Ding GX, Ma CM, We J, Mackie TR. BEAM: a Monte Carlo code to simulate radiotherapy treatment units. Med Phys. 1995;22:503–524. 89. Kawrakow I. Accurate condensed history Monte Carlo simulation of electron transport. I. EGSnrc, the new EGS4 version. Med Phys. 2000;27:485–498. 90. Verhaegen F, Nahum AE, Van de Putte S, Namito Y. Monte Carlo modelling of radiotherapy kV x-ray units. Phys Med Biol. 1999;44:1767–1789. 91. Sheikh-Bagheri D, Rogers DW. Monte Carlo calculation of nine megavoltage photon beam spectra using the BEAM code. Med Phys. 2002;29:391–402. 92. Jarry G, Graham SA, Moseley DJ, Jaffray DJ, Siewerdsen JH, Verhaegen F. Characterization of scattered radiation in kV CBCT images using Monte Carlo simulations. Med Phys. 2006;33:4320–4329. 93. Ahnesjo A, Aspradakis MM. Dose calculations for external photon beams in radiotherapy. Phys Med Biol. 1999;44:R99–R155. 94. Pawlowski JM, Ding GX. A new approach to account for the mediumdependent effect in model-based dose calculations for kilovoltage xrays. Phys Med Biol. 2011;56:3919–3934. 95. Pawlowski JM, Ding GX. An algorithm for kilovoltage x-ray dose calculations with applications in kV-CBCT scans and 2D planar projected radiographs. Phys Med Biol. 2014;59:2041–2058. 96. Alaei P, Gerbi BJ, Geise RA. Evaluation of a model-based treatment planning system for dose computations in the kilovoltage energy range. Med Phys. 2000;27:2821–2826. 97. Alaei P, Gerbi BJ, Geise RA. Lung dose calculations at kilovoltage xray energies using a model-based treatment planning system. Med Phys. 2001;28:194–198. 98. Alaei P, Gerbi BJ, Geise RA. Generation and use of photon energy deposition kernels for diagnostic quality x rays. Med Phys. 1999;26:1687–1697. 99. Kim S, Alaei P. Implementation of full/half bowtie filter models in a commercial treatment planning system for kilovoltage cone-beam CT dose estimations. J Appl Clin Med Phys. 2016;17:5988. 100. Alaei P, Spezi E. Commissioning kilovoltage cone-beam CT beams in a radiation therapy treatment planning system. J Appl Clin Med Phys. 2012;13:3971. 101. Dzierma Y, Nuesken F, Otto W, Alaei P, Licht N, Rube C. Dosimetry of an in-line kilovoltage imaging system and implementation in treatment planning. Int J Radiat Oncol Biol Phys. 2014;88:913–919. 102. Ding GX, Pawlowski JM, Coffey CW. A correction-based dose calculation algorithm for kilovoltage x rays. Med Phys. 2008;35:5312– 5316. 103. Ding GX, Coffey CW. Beam characteristics and radiation output of a kilovoltage cone-beam CT. Phys Med Biol. 2010;55:5231– 5248. 104. Almond PR, Biggs PJ, Coursey BM, et al. AAPM’s TG-51 protocol for clinical reference dosimetry of high-energy photon and electron beams. Med Phys. 1999;26:1847–1870. 105. Andreo P, Burns DT, Hohlfeld K, et al. Absorbed Dose Determination in External Beam Radiotherapy: An International Code of Practice for Dosimetry Based on Standards for Absorbed Dose to Water. Volume 398 of Technical Report Series. Vienna: International Atomic Energy Agency (IAEA); 2000. 106. Ma CM, Coffey CW, DeWerd LA, et al. AAPM protocol for 40-300 kV x-ray beam dosimetry in radiotherapy and radiobiology. Med Phys. 2001;28:868–893. 107. Al-Senan RM, Hatab MR. Characteristics of an OSLD in the diagnostic energy range. Med Phys. 2011;38:4396–4405. 108. Schembri V, Heijmen BJ. Optically stimulated luminescence (OSL) of carbon-doped aluminum oxide (Al2O3:C) for film dosimetry in radiotherapy. Med Phys. 2007;34:2113–2118. 109. Kron T, Duggan L, Smith T, et al. Dose response of various radiation detectors to synchrotron radiation. Phys Med Biol. 1998;43:3235–3259. 110. Nunn AA, Davis SD, Micka JA, DeWerd LA. LiF:Mg, Ti TLD response as a function of photon energy for moderately filtered x-ray

Ding et al.: Image Guidance Doses to Radiotherapy Patients

spectra in the range of 20–250 kVp relative to 60Co. Med Phys. 2008;35:1859–1869. 111. Giaddui T, Cui Y, Galvin J, Yu Y, Xiao Y. Comparative dose evaluations between XVI and OBI cone beam CT systems using Gafchromic XRQA2 film and nanoDot optical stimulated luminescence dosimeters. Med Phys. 2013;40:062102. 112. Nobah A, Aldelaijan S, Devic S, et al. Radiochromic film based dosimetry of image-guidance procedures on different radiotherapy modalities. J Appl Clin Med Phys. 2014;15:5006. 113. Spezi E, Downes P, Jarvis R, Radu E, Staffurth J. Patient-specific three-dimensional concomitant dose from cone beam computed

16 tomography exposure in image-guided radiotherapy. Int J Radiat Oncol Biol Phys. 2011;83:419–426. 114. Nelson AP, Ding GX. An alternative approach to account for patient organ doses from imaging guidance procedures. Radiother Oncol. 2014;112:112–118. 115. Klein EE, Hanley J, Bayouth J, et al. Task Group 142 report: quality assurance of medical accelerators. Med Phys. 2009;36: 4197–4212. 116. Bissonnette JP, Balter PA, Dong L, et al. Quality assurance for imageguided radiation therapy utilizing CT-based technologies: a report of the AAPM TG-179. Med Phys. 2012;39:1946–1963.

Medical Physics, 0 (0), xxxx

107

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Dosimetric comparison of different treatment modalities for stereotactic radiotherapy

RESEARCH

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Dosimetric comparison of different treatment modalities for stereotactic radiotherapy Shih-Ming Hsu1,2,3*, Yuan-Chun Lai1,4,5, Chien-Chung Jeng4 and Chia-Ying Tseng1,2 Abstract Background: The modalities for performing stereotactic radiotherapy (SRT) on the brain include the cone-based linear accelerator (linac), the flattening filter-free (FFF) volumetric modulated arc therapy (VMAT) linac, and tomotherapy. In this study, the cone-based linac, FFF-VMAT linac, and tomotherapy modalities were evaluated by measuring the differences in doses delivered during brain SRT and experimentally assessing the accuracy of the output radiation doses through clinical measurements. Methods: We employed a homemade acrylic dosimetry phantom representing the head, within which a thermoluminescent dosimeter (TLD) and radiochromic EBT3 film were installed. Using the conformity/gradient index (CGI) and Paddick methods, the quality of the doses delivered by the various SRT modalities was evaluated. The quality indicators included the uniformity, conformity, and gradient indices. TLDs and EBT3 films were used to experimentally assess the accuracy of the SRT dose output. Results: The dose homogeneity indices of all the treatment modalities were lower than 1.25. The cone-based linac had the best conformity for all tumors, regardless of the tumor location and size, followed by the FFF-VMAT linac; tomography was the worst-performing treatment modality in this regard. The cone-based linac had the best gradient, regardless of the tumor location and size, whereas the FFF-VMAT linac had a better gradient than tomotherapy for a large tumor diameter (28 mm). The TLD and EBT3 measurements of the dose at the center of tumors indicated that the average difference between the measurements and the calculated dose was generally less than 4%. When the 3% 3-mm gamma passing rate metric was used, the average passing rates of all three treatment modalities exceeded 98%. Conclusions: Regarding the dose, the cone-based linac had the best conformity and steepest dose gradient for tumors of different sizes and distances from the brainstem. The results of this study suggest that SRT should be performed using the cone-based linac on tumors that require treatment plans with a steep dose gradient, even as the tumor is slightly irregular, we should also consider using a high dose gradient of the cone base to treat and protect the normal tissue. If normal tissues require special protection exist at positions that are superior or inferior to the tumor, we can consider using tomotherapy or Cone base with couch at 0° for treatment. Keywords: Linac, Stereotactic radiotherapy, Tomotherapy, Treatment planning systems, VMAT

* Correspondence: smhsu@ym.edu.tw 1 Medical Physics and Radiation Measurements Laboratory, National Yang-Ming University, Taipei, Taiwan, ROC 2 Department of Biomedical Imaging and Radiological Sciences, National Yang-Ming University, No. 155, Sec. 2, Li-Nong St., Beitou District, Taipei 112, Taiwan, ROC Full list of author information is available at the end of the article © The Author(s). 2017 Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 International License (http://creativecommons.org/licenses/by/4.0/), which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made. The Creative Commons Public Domain Dedication waiver (http://creativecommons.org/publicdomain/zero/1.0/) applies to the data made available in this article, unless otherwise stated.

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Background Stereotactic radiosurgery (SRS) can be used to treat arteriovenous malformation, glioblastoma multiforme, and various metastasized tumors in the brain. Because lesions that are treated using SRS tend to be very small, and the method in which the doses are delivered differs from the traditional multi-fractionated dose-delivery mode, the required radiation in SRS is usually delivered in a single dose. In stereotactic radiotherapy (SRT), the required dose is fractionated into multiple doses. Because each of the doses in a single SRT or SRS treatment is extremely large, a high accuracy is necessary for the treatments, as well as a very steep dose gradient, to ensure the tumor is given a sufficiently high dose while the surrounding normal tissues are protected and left unharmed [1]. In recent years, advancements in linear accelerator (linac) based technologies, including developments in image-guidance systems, multileaf collimators (MLCs), and volumetric-modulated arc therapy (VMAT), have led to linac-based treatments that can achieve a high accuracy, steep gradients, and a high level of conformity [2–9]. Traditionally, the Gamma Knife has been the primary tool for performing brain SRS or SRT. However, the sites without this facility instead utilize tomotherapy and MLC or cone-based linac devices to perform SRT therapy. Tomotherapy has a linac mounted on a ring gantry, and a binary MLC is used to adjust the dose of the photon-beam irradiation in sync with the forward motion of the treatment couch, resulting in a helical and tomographic form of intensity modulated radiotherapy (TomoHelical IMRT). Linear accelerators may use either an MLC or a cone to shape and limit the field of radiation. Recent developments in flattening filter-free (FFF) high-dose models have led to a further reduction in the probability of patient movement, thus reducing the effects caused by patient movement. This has enabled the FFF-VMAT linac treatment modality to become a viable tool for performing SRT. Different treatment modalities have different output dose characteristics, which may affect the radiation doses received by normal tissues surrounding the tumor [10–12]. Therefore, the main goal of this study is to compare the SRT treatment doses of the cone-based linac, FFF-VMAT linac, and tomotherapy treatment modalities and evaluate the differences between doses calculated according to treatment planning systems and measured radiation doses. Methods Design of dosimetry phantom

A homemade acrylic phantom of the head was created according to computed-tomography (CT) images of patients. EBT3 radiochromic films (Ashland, USA) and the cubic thermoluminescent dosimeters (Thermo,

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USA) were installed within the coronal slices to measure the distribution of the radiation doses. In the region where the tumor was located the slices were 2 mm thick; the thickness of the remaining slices was 5 mm, as shown in Fig. 1. Treatment planning

CT (LightSpeed GE, USA) was applied to obtain images of the phantom, and the thickness of each CT slice was 1.25 mm. The images were sent to a tomotherapy treatment planning system (TomoTherapy Planning Station Hi-ART® version 4.3.2 Accuray, USA) and a Pinnacle treatment planning system (Pinnacle3® Version 9.8 Philips, USA). The TomoTherapy system designed all the planning related to tomotherapy, and the Pinnacle system designed all the planning for the cone-based and FFF-VMAT linacs. All necessary beam data were entered into the Pinnacle system, and commission tests were completed for this system. A structure with a diameter of 3 cm was placed on the CT images to simulate the location of the brainstem. To match the size of the collimating cone, spherical tumors 8, 18, and 28 mm in diameter were placed at distances of 1 and 6 mm from the borders of the brainstem, as shown in Fig. 2. The use of spherical tumors is expected to exclude the effects of tumor shapes in order to purely assess the differences in different modalities. Different treatment plans were designed by the treatment planning systems according to the size of the tumors. To exclude the effects of the beam angle, all the cone-based linac and FFF-VMAT linac plans used the arc-therapy method and the same beam angles, as shown in Fig. 3. The beam angles were as follows: counterclockwise from 179° to 345° with a collimator angle of 0° and a couch angle of 0°, counter-clockwise from 210° to 180° with a collimator angle of 10° and a couch angle of 0°, counter-clockwise from 179° to 0° with a collimator angle of 330° and a couch angle of 330°, counterclockwise from 179° to 0° with a collimator angle of 310° and a couch angle of 300°, counter-clockwise from 179° to 0° with a collimator angle of 260° and a couch angle of 270°, and clockwise from 180° to 0° with a collimator angle of 250° and a couch angle of 60°. The accelerator used for the cone-based linac was a 6MV Elekta Synergy (Sweden) photon. Cone diameters of 10, 20, and 30 mm were used. The accelerator used for the FFF-VMAT linac was a 6-MV FFF Elekta Axesse (Sweden) photon beam and was used in conjunction with a 5 mm wide Elekta Agility high-speed MLC. The following parameters were used for the TomoTherapy system (Accuray, USA): modulation factor of 3.0, field width of 1 cm, pitch of 0.086. All treatment planning were planned by the same planner. In all treatment plans, a dose of 600 cGy was

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Fig. 1 Homemade acrylic dosimetry phantom of the head: (a) coronal slices and fixing rods, (b) head phantom formed from all of the coronal slices, and (c) head phantom fixed by a mask

delivered to the tumors, and the conditions were optimized to maintain 98% dose coverage on the tumor, with the maximum tumor dose not exceeding 125% to minimize the doses incident on the brainstem and normal brain tissue. Maximum dose constrain of brainstem for tumor away from brainstem 1 mm and 6 mm were limited to 500 cGy and 200 cGy, respectively and D1% of these were limited to 150 cGy and 100 cGy, respectively. Auxiliary ROIs such as “Ring” structure were also used to decrease the dose of normal tissue during planning. The three-dimensional (3D) dose grid of the three axes of the Pinnacle system was set to 1 mm and that of the tomotherapy system was set to “fine”. Analytic indicators of dose quality

The homogeneity index (HI) [13], conformity/gradient index (CGI), and Paddick indices were used to compare the quality of the treatment plans. The HI was used to describe the homogeneity of the dose within the tumor. The HI is defined as HI ¼ MD=PD;

ð1Þ

where MD is the maximum dose within the tumor, and PD is the 100% prescription dose. The HI of a perfect

treatment plan is 1; if the 80% isodose curve is selected as the prescription dose, then the HI becomes 1.25 instead. The CGI is a holistic index that consists of the conformity index (CGIc) and the gradient index (CGIg) [14]. The CGI is defined as CGI ¼ CGI C þ CGI g =2

ð2Þ

The CGIc is used to describe the relationship between the volume of the tumor and the volume covered by the dose. The CGIc is defined as CGI C ¼

TV PIV

� 100

ð3Þ

PIV is the volume covered by the 100% prescription dose curve, and TV is the volume of the tumor. CGIc = 100 corresponds to perfect conformity of the treatment planning. . The CGIg is the effective difference in radius between the volumes covered by the 50% and 100% doses; it is used to evaluate the decrement of the dose in the highdose region (50% and above) and is defined as follows:

Fig. 2 CT images of the homemade acrylic dosimetry phantom of the head: (a) transverse view, (b) sagittal view, (c) coronal view (Red, the simulated brainstem; Green, tumor of 8 mm diameter and 1 mm away from brainstem; Blue, tumor of 8 mm diameter and 6 mm away from brainstem; Pink, tumor of 18 mm diameter and 1 mm away from brainstem; Dark-green, tumor of 18 mm diameter and 6 mm away from brainstem; Yellow-green, tumor of 28 mm diameter and 1 mm away from brainstem; Orange, tumor of 28 mm diameter and 6 mm away from brainstem.)

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represents the degree to which a tumor is covered by a specified isodose curve. For a perfect treatment plan, CIPaddick = 1. The GIPaddick describes the decrement of the dose in the high-dose region (50% and above) and is defined as

GI Paddick ¼ V 50% V 100

where V50% is the volume covered by 50% of the prescription dose, and V100% is the volume covered by 100% of the prescription dose. The GIPaddick can represent the degree to which normal tissues outside the tumor are protected. A perfect treatment plan must have a value of the GIPaddick that approaches 1.

Fig. 3 All the beam angles used by the Pinnacle treatment planning system

� �� CGI g ¼ 100− 100 � Reff ;50%Rx −Reff ;Rx −0:3cm

Radiation dose measurements

ð4Þ

Reff , Rx refers to the effective radius of the volume covered by the 100% prescription dose curve, and Reff , 50 % Rx is the effective radius of the volume covered by the 50% prescription dose curve, with Reff defined as rffiffiffiffiffiffiffi 3 3V ð5Þ Reff ¼ 4π V is the volume covered by the required dose. This 3 mm in distance between Reff , 50 % Rx and Reff , Rx gradient was obtained empirically from clinical radiosurgery planning cases, and corresponds to the possible gradient with linac radiosurgery when using multiple noncoplanar arcs. As CGIg more than 100, it corresponds to less gradient than an optimum 3 mm empirically.. The Paddick indices are clinically used to describe the conformity [15] and gradient [16] of the treatment plan. The Paddick indices include the conformity index (CIPaddick) and the gradient index (GIPaddick). As the CGIc is unable to present the degree of tumor-volume coverage for a specified prescription dose curve, the CIPaddick complements the CGIc by describing the volume covered by the prescription dose as well as the relationship between the tumor volume covered by the prescription dose and the overall volume of the tumor. The CIPaddick is defined as CIPaddick ¼

ðTV PIV Þ2 TV � PIV

ð7Þ

ð6Þ

where PIV refers to the volume covered by the 100% prescription dose curve, TV is the tumor volume, and TVPIV is the tumor volume covered by PIV. This index

In this work, cubic TLD-100 dosimeters and EBT3 films were used to measure the radiation dose [17–22], with the dose at each tumor location measured three times. Each cone-based linac and FFF-VMAT linac measurement was accompanied by alignment using the six degree-of-freedom image-guided cone-beam CT of the accelerator. MVCT was used to align the tomotherapy measurements to correct for 3D position shifts and rollangle deviations in the rotating gantry. FILM QATM Version 2.2 was used to evaluate the profile changes in the right–left (R–L) and superior–inferior (S–I) directions, and gamma evaluation was used to determine the differences between the calculated dose of the treatment plan and the two-dimensional planar dose measured by the EBT3 films. Because SRT treatments characteristically require a high level of positional accuracy and a steep gradient, the 3% 3-mm and 5% 1-mm criteria were chosen as the gamma passing rate metrics for assessing the differences in the planar doses. Statistical analysis

The Mann–Whitney test (Statistical Package for the Social Sciences, IBM Corporation, New York, USA) was used to assess the statistical significance of the gamma analysis results for the different techniques.

Results Dose-quality analysis

The results of the cone-based linac, FFF-VMAT linac, and tomotherapy dose-quality analyses are shown in Table 1. The average HI values of the cone-based linac, the FFF-VMAT linac, and tomotherapy were 1.20 ± 0.03, 1.21 ± 0.03, and 1.23 ± 0.02, respectively. As it was strictly specified that the maximum dose on the tumors did not exceed the 125% of the prescription dose during the creation of the treatment plans, none of the average HIs of the treatment plans exceeded 1.25. The lowest HI

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Table 1 HI, CGI, and Paddick indices calculated by the treatment planning system using the cone-based linac, FFF-VMAT linac, and tomotherapy treatment modalities Tumor Diameter

8 mm

18 mm

Distance 1 mm from brainstem Modality

6 mm

28 mm

1 mm

6 mm

1 mm

6 mm

Cone- FFF- Tomo Cone- FFF- Tomo Cone- FFF- Tomo Cone- FFF- Tomo Cone- FFF- Tomo Cone- FFF- Tomo based VMAT based VMAT based VMAT based VMAT based VMAT based VMAT

1.24

1.25

1.20

CGIc

84.59

48.89

47.96 86.25

1.23

1.25

1.23

67.93

46.79 92.02

1.20

1.19

1.25

75.66

69.75 95.35

1.20

1.17

1.24

73.99

67.76 98.99

1.17

1.23

1.21

95.44

86.04 99.84

1.16

1.19

1.23

92.27

86.68

CGIg

103.25 66.45

74.39 103.15 74.30

75.96 88.43

60.53

60.61 89.33

59.71

62.68 74.02

52.79

48.02 75.26

61.62

50.49

CGI

93.92

57.67

61.18 94.71

71.11

61.38 90.23

68.10

65.18 92.34

66.85

62.22 86.50

74.11

67.03 87.55

76.95

68.58

CIPaddick

0.82

0.48

0.47

0.84

0.66

0.45

0.90

0.73

0.68

0.92

0.72

0.66

0.94

0.92

0.84

0.95

0.88

0.81

GI Paddick

4.23

10.97

9.07

4.28

10.58

8.57

3.02

4.90

4.83

3.00

4.93

4.62

2.73

3.67

4.14

2.69

3.21

3.90

(1.16) was observed when the cone-based linac was used to treat 28 mm diameter tumors that were located 6 mm from the brainstem. The average CGI values for the cone-based linac, the FFF-VMAT linac, and tomotherapy were 90.88 ± 3.37, 69.13 ± 6.74, and 64.26 ± 3.13, respectively. In general, the FFF-VMAT linac had higher CGI values than tomotherapy except for tumors with small distance from the brainstem. The average CGIc values for the conebased linac, the FFF-VMAT linac, and tomotherapy were 92.84 ± 6.41, 75.70 ± 17.01, and 67.50 ± 17.48, respectively. For all distances from the brainstem and tumor diameters, the cone-based linac exhibited the highest CGIc values, followed by the FFF-VMAT linac, and finally tomotherapy. The average CGIg values for the cone-based linac, the FFF-VMAT linac, and tomotherapy were 88.91 ± 12.78, 62.57 ± 7.23, and 62.03 ± 11.65, respectively. The FFF-VMAT linac had higher CGIg values than tomotherapy for large-diameter tumors (28 mm), with ratios of 52.79: 48.02 and 61.62: 50.49 for distances of 1 and 6 mm from the brainstem, respectively. The average CIPaddick for the cone-based linac, the FFF-VMAT linac, and tomotherapy were 0.90 ± 0.05, 0.73 ± 0.16, and 0.65 ± 0.16, respectively. Regardless of the tumor diameter and distance from the brainstem, the cone-based linac exhibited the best CIPaddick values, followed by the FFF-VMAT linac, and finally tomotherapy. The GIPaddick value of the FFF-VMAT linac for large-diameter tumors (28 mm) was better than that of tomotherapy, with ratios of 3.67: 4.14 and 3.21: 3.90 for distances of 1 and 6 mm from the brainstem. However, tomotherapy had better GIPaddick values than the FFF-VMAT linac for smaller-diameter tumors (8 mm), with ratios of 9.07: 10.97 and 8.57: 10.58 for distances of 1 and 6 mm from the brainstem, respectively.

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Dose measurements

The dose-linearity curves of TLD and EBT3 (0–800 cGy) are shown in Fig. 4. The radiation doses at the center of the tumors within the phantom were clinically measured and compared with the dose calculated in the treatment plan; the differences are shown in Table 2. The TLD and EBT3 dose measurements indicated that the average differences between the output doses of the cone-based linac, the FFF-VMAT linac, and tomotherapy and the calculated doses of the treatment plans were generally lower than 4%. The largest observed difference was −3.68% (−4.52% to −3.27%) for the cone-based linac and was measured using the EBT3 film. Figure 5 shows the dose profile measured using EBT3 films for tumors locaed 1 mm from the brainstem in the R–L and S–I directions. The results of the measurement using the EBT3 film are generally consistent with calculations of the treatment plan. The average dose profile widths of the 50% and 30% doses relative to the dose at the center of the tumor for tumors of various sizes are shown in Fig. 6. The 30% profile widths of the FFFVMAT linac were smaller than those of tomotherapy for all tumor volumes because the gantry rotated in a coplanar fashion, synchronized with the movement of the treatment couch, during the tomotherapy treatments to enable irradiation of the tumor. Because the R–L direction lies within the beam pathway, the distribution of low-intensity doses in the R–L direction was broadened. The gamma passing rates of the three treatment modalities under two different gamma passing criteria are shown in Fig. 7. When the 3% 3-mm criteria was used as the passing metric, the passing rates for the conebased linac, the FFF-VMAT linac, and tomotherapy were 99.28 ± 1.36%, 98.71 ± 1.39%, and 99.98 ± 0.18%, respectively. Among these, tomotherapy had the highest passing rate (p < 0.05), and there was no statistically significant difference between the passing rates for the

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Fig. 4 Dose-linearity curves for 6 MV: (a) TLD and (b) EBT3

cone-based and FFF-VMAT linacs (p = 0.235). Considering that SRT treatments characteristically require a high level of positional accuracy and steep dose gradients, the treatment modalities were also evaluated using the 5% 1-mm criteria as the passing metric. In this case, the passing rates for the cone-based linac, the FFF-VMAT linac, and tomotherapy were 97.73 ± 2.42%, 93.53 ± 3.82%, and 98.19 ± 2.09%, respectively. Among these, the FFF-VMAT linac had the lowest passing rate (p < 0.01), and there was no significant difference between the passing rates for the cone-based linac and tomotherapy (p = 0.46). The gamma evaluation maps of 28 mm diameter tumors located 1 mm from the brainstem using the 3% 3mm and 5% 1-mm criteria were analyzed, as shown in Fig. 8. Here, changing the passing metric caused an increase in the failed areas in regions with steep doses at the borders of the tumor for the cone-based and FFFVMAT linac modalities. The cone-based linac and tomotherapy retained a gamma passing rate of 95% and above, whereas the passing rate of the FFF-VMAT linac decreased below 95%.

Discussion The result of this study show that the average HI for the cone-based linac was lower than those for the FFFVMAT linac and tomotherapy because of the radiation of the cone-based linac was homogeneous. As a result of no dose-intensity control within the radiation field of

cone-based linac, there were no significant changes for a cone treatment at a distance difference of only 5 mm distance to brainstem. Because the radiation field of the cone-based linac was similar to the size of the tumors, this modality yielded the highest CGIc and CIPaddick. Unlike the cone-based linac, tomotherapy uses a constant jaw size, leading to a “ramp-up” effect, which causes normal tissues surrounding the tumor in the S–I direction to receive a higher dose [23]. The use of a cone in the cone-based linac minimized the dose divergence, resulting in the cone-based linac having the best CGIg and GIPaddick among the three treatment modalities. When the tumor volume was very small, the jaw used in tomotherapy limited the dispersion range of the low-dose region, causing the CGIg to be higher than that for the FFF-VMAT linac. As the tumor volume increased, the dose on the brainstem increased. The research of Yip et al. [12] indicated that, regardless of the conformity and gradient, the cone-based linac performed better than tomotherapy for tumors with a regular shape; this finding is consistent with our results. However, Soisson et al. [24] reported that excellent levels of tumor conformity were achieved using tomotherapy. Nevertheless, we obtained a similar result with respect to the overall evaluation of the CGI. Soisson et al. did not provide a detailed comparison between the doses of the FFF-VMAT linac and tomotherapy for SRT, whereas

Table 2 Average difference in the dose at the center of tumors between the calculated doses from the treatment planning system and the doses measured using TLD and EBT3 for the cone-based linac, the FFF-VMAT linac, and tomotherapy Dosimeter

Cone-based linac

FFF-VMAT linac

Tomotherapy

TLD (%)

−1.38 (−4.08 to 0.81)

−1.34 (−4.96 to 4.04)

1.05 (−2.10 to 3.65)

EBT3 (%)

−3.68 (−4.52 to −3.27)

−1.75 (−4.70 to 2.52)

−1.02 (−3.72 to 0.58)

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Fig. 5 Differences of EBT3-measured and treatment plan-calculated profiles (normalized to the dose of tumor center) in the R–L and S–I directions for tumors located 1 mm from the brainstem with diameters of (a) 8 mm, (b) 18 mm, and (c) 28 mm

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Fig. 6 Average dose profile widths of doses that are 50% and 30% of the dose at the center of the tumor, measured using EBT3 films, in the (a) R–L direction and (b) S–I direction

we showed that, regardless of the tumor size and distance from the brainstem, the conformity of the FFFVMAT linac was always better than that of tomotherapy. The FFF-VMAT linac also had a steeper gradient than tomotherapy for larger tumors, whereas tomotherapy exhibited a steeper gradient for smaller tumors. It will result in the dose accumulation to the borders of 18 mm and 28 mm diameter PTV located 1 mm from brainstem if we try to lower the dose of brainstem for FFF-VMAT linac and tomotherapy with intensity modulated field. In this situation, if we take into account the tumor coverage, it may increase the dose closed to the borders of PTV. For cone-based linac without intensity modulated field, the dose in the PTV will be more uniform and the dose of brainstem will be reduced because of high dose gradient. According to the AAPM TG-142

report, a deviation of 1 mm is allowed in the rotational center of the couch and gantry of the linear accelerator used for SRS or SRT, and the repeatability of the MLC is required [25]. These deviations could have affected the gamma analysis results for regions with a steep dose gradient. O’Connor et al. [26] reported that errors in the position of the MLC significantly affected the results of gamma analysis; for example, with the 3% 1-mm criteria as the gamma analysis passing metric, a 0.8 mm deviation in the position of the MLC reduced the gamma passing rates of square-field rotating beams with field sizes of 16 and 40 mm by 5.7% and 4.5%, respectively. In the continuous delivery of VMAT, the position of MLC at each control point must match the gantry’s speed and dose rate, and the MLC position in this continuous process will also be affected by gravity and the speed of

Fig. 7 Gamma passing rates of the three treatment modalities under two different gamma passing criteria: Criteria 1: 3% 3-mm and Criteria 2: 5% 1-mm

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Fig. 8 Gamma-evaluation maps of the three different treatment modalities evaluated using two different gamma passing criteria (the red circle indicates the area of the 28 mm tumor that is located 1 mm from the brainstem): (a) 3% 3-mm and (b) 5% 1-mm

MLC. Since the setting of MLC’s tolerance table in machine’s setting is 1 mm, it means that the machine will keep delivery as the MLC position error is less than 1 mm at each control point in the process of delivery, and that the 1 mm tolerance may affect the measurement results, especially in the small field and high-dose gradient regions [27, 28]. Therefore the more mechanical error variable, the more likely to affect the Gamma pass rate. The treatment time of each technique is also the focus of our concern. In our study, the longest treatment time required for the cone-based linac, FFF-VMAT linac and Tomotherapy were 830, 679 and 728 s, respectively. The above time did not include the time of image registration and confirmation. For cone-based linac and FFF-VMAT linac techniques using the non-coplanar angles, the number of beams that need to rotate the angle of the couch which can affects the time required for treatment.

Conclusion As a result of the use of spherical tumors, we could not be affected by the shape of the tumor and clearly understand the differences of the dose characteristics between three modalities. Among the three treatment modalities studied, the cone-based linac had the best conformity

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and dose gradient for tumors of all sizes and locations. According to our results, if a critical organ, such as the brainstem, is located near the tumor and the situation requires a steep dose gradient, the cone-based linac should be used for SRT therapy. Since the steep dose gradient of the cone-based linac is obvious, we should also consider using a high dose gradient of the cone base to treat slightly irregular tumor and protect the critical organs or normal brain. The dose conformity of the FFF-VMAT linac for tumors of all sizes and positions was better than that of tomotherapy. The dose gradient of the FFF-VMAT linac for large tumors (28 mm in diameter) was better than that of tomotherapy, whereas tomotherapy had a better dose gradient than the FFFVMAT linac for small tumors (8 mm in diameter). The cone-based linac had the smallest 50% and 30% dose profile widths in the R–L and S–I directions among the three modalities, with the exception of the 30% dose profile width for 28 mm tumors in the S–I direction, where tomotherapy and the cone-based linac produced similar results. On one hand, the 30% dose profile widths of the FFF-VMAT linac in the R–L direction for all tumor volumes were smaller than those of tomotherapy. Therefore, for protecting normal tissues located superior and inferior to the tumor, we can consider using

Hsu et al. Radiation Oncology (2017) 12:155

tomotherapy or Cone base with couch at 0 ° for treatment. The TLD and EBT3 measurement results indicate that all three SRT treatment modalities achieved accurate doses. However, the FFF-VMAT and cone-based linacs may have produced dose deviations in regions with steep gradients on the borders of the tumor because of the effects of mechanical factors. Abbreviations 3D: Three-dimensional; CGI: Conformity/gradient index; CGIc: Conformity index; CGIg: Gradient index; CIPaddick: Paddick conformity index; CT: Computed-tomography; FFF: Flattening filter-free; GIPaddick: Paddick gradient index; HI: Homogeneity index; Linac: Linear accelerator; MLCs: Multileaf collimators; R–L: Right–left; S–I: Superior–inferior; SRS: Stereotactic radiosurgery; SRT: Stereotactic radiotherapy; TLD: Thermoluminescent dosimeter; VMAT: Volumetric modulated arc therapy

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7. 8.

Acknowledgements Not applicable.

10.

Funding This study was supported in part by the Ministry of Science and Technology of Taiwan (MOST 104-2314-B-010-040-MY3 and MOST 106-NU-E-010-001-NU).

11.

Availability of data and materials All data generated or analysed during this study are included in this published article. Authors’ contributions SMH and YCL designed the project. SMH,YCL, CCJ and CYT contributed to acquisition of data and data analysis. SMH,YCL and CCJ contributed to methodology of the process. SMH was the Senior Author who oversaw the project. All authors read and approved the final manuscript. Ethics approval and consent to participate Not applicable. Consent for publication Not applicable. Competing interests The authors declare that they have no competing interests.

Publisher’s Note

Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations. Author details 1 Medical Physics and Radiation Measurements Laboratory, National Yang-Ming University, Taipei, Taiwan, ROC. 2Department of Biomedical Imaging and Radiological Sciences, National Yang-Ming University, No. 155, Sec. 2, Li-Nong St., Beitou District, Taipei 112, Taiwan, ROC. 3Biophotonics and Molecular Imaging Research Center, National Yang-Ming University, Taipei, Taiwan, ROC. 4Department of Physics, National Chung Hsing University, Taichung, Taiwan, ROC. 5Department of Radiation Oncology, Changhua Christian Hospital, Changhua, Taiwan, ROC.

12.

13.

14.

15. 16. 17.

18.

19.

20.

21.

22.

Received: 20 April 2017 Accepted: 7 September 2017 23. References 1. Lee N, Isaacson SR, Schiff PB, Sisti MB, Germano IM. Historical perspective and basic principles of radiation physics and biology. In: Germano IM, editor. LINAC and gamma knife radiosurgery. Park Ridge: AANS; 2000. p. 3–10. 2. Meeks SL, Buatti JM, Bova FJ, Friedman WA, Mendenhall WM. Treatment planning optimization for linear accelerator radiosurgery. Int J Radiat Oncol Biol Phys. 1998;41:183–97.

24.

25.

Hazard LJ, Wang B, Skidmore TB, Chern SS, Salter BJ, Jensen RL, et al. Conformity of linac-based stereosurgery radiosurgery using dynamic conformal arcs and micro-multileaf collimator. Int J Radiat Oncol Biol Phys. 2009;73:562–70. Dhabaan A, Elder E, Schreibmann E, Crocker I, Curran WJ, Oyesiku NM, et al. Dosimetric performance of the new high-definition multileaf collimator for intracranial stereotactic radiosurgery. J Appl Clin Med Phys. 2010;11:197–211. Mayo CS, Ding L, Addesa A, Kadish S, Fitzgerald TJ, Moser R. Initial experience with volumetric IMRT (rapidarc) for intracranial stereotactic radiosurgery. Int J Radiat Oncol Biol Phys. 2010;78:1457–66. Ohtakara K, Hayashi S, Hoshi H. Dose gradient analyses in Linac-base intracranial stereotactic radiosurgery using Paddicks gradient index: consideration of the optimal method for plan evaluation. J Radiat Res. 2011;52:592–9. Galal MM, Keogh S, Khalil S. Dosimetric and mechanical characteristics of a commercial dynamic μMLC used in SRS. Med Phys. 2011;38:4225–31. Audet C, Poffenbarger BA, Chang P, Jackson PS, Lundahl RE, Ryu SI, et al. Evaluation of volumetric modulated arc therapy for cranial radiosurgery using multiple noncoplanar arcs. Med Phys. 2011;38:5863–75. Hong LX, Gard M, Lasala P, Kim M, Mah D, Chen CC, et al. Experience of micromultileaf collimator linear accelerator based single fraction stereotactic radiosurgery: Tumors dose inhomogeneity, conformity, and dose fall off. Med Phys. 2011;38:1239–47. Gevaert T, Levivier M, Lacornerie T, Verellen D, Engels B, Reynaert N, et al. Dosimetric comparison of different treatment modalities for stereotactic radiosurgery of arteriovenous malformations and acoustic neuromas. Radiother Oncol. 2013;106:192–7. Kaul D, Badakhshi H, Gevaret T, Pasemann D, Budach V, Tuleasca C, et al. Dosimetric comparison of different treatment modalities for stereotactic radiosurgery of meningioma. Acta Neurochir. 2015;157:559–63. Yip HY, Mui WL, Lee JW, Fung WW, Chan JM, Chiu G, et al. Evaluation of radiosurgery techniques–Cone-based linac radiosurgery vs tomotherapybased radiosurgery. Med Dosim. 2013;38:184–9. Shaw E, Scott C, Souhami L, Dinapoli R, Bahary JP, Kline R, et al. Radiosurgery for the treatment of previously irradiated recurrent primary brain tumors and brain metastases: Initial report of Radiation Therapy Oncology Group Protocol 90-05. Int J Radiat Oncol Biol Phys. 1996;34:647–54. Wagner TH, Bova FJ, Friedman WA, Buatti JM, Bouchet LG, Meeks SL. A simple and reliable index for scoring rival stereotactic radiosurgery plans. Int J Radiat Oncol Biol Phys. 2003;57:1141–9. Paddick I. A simple scoring ratio to index the conformity of radiosurgical treatment plans. J Neurosurg. 2000;93(Suppl 3):219–22. Paddick I, Lippitz B. A simple dose gradient measurement tool to complement the conformity index. J Neurosurg. 2006;105(Suppl):194–201. Ertl A, Zehetmayer M, Schöggl A, Kindl P, Hartl R. Dosimetry studies with TLDs for stereotactic radiation techniques for intraocular tumors. Phys Med Biol. 1997;42:2137–45. Ho AK, Gibbs IC, Chang ST, Main B, Adler JR. The use of TLD and Gafchromic film to assure submillimeter accuracy for image-guided radiosurgery. Med Dosim. 2008;33:36–41. Faught AM, Kry SF, Luo D, Molineu A, Bellezza D, Gerber RL, et al. Development of a modified head and neck quality assurance phantom for use in stereotactic radiosurgery trials. J Appl Clin Med Phys. 2013;14:206–15. Fiandra C, Fusella M, Giglioli FR, Filippi AR, Mantovani C, Ricardi U, et al. Comparison of Gafchromic EBT2 and EBT3 for patient-specific quality assurance: Cranial stereotactic radiosurgery using volumetric modulated arc therapy with multiple noncoplanar arcs. Med Phys. 2013; doi: 10. 1118/1.4816300. Barbosa NA, da Rosa LA, Batista DV, Carvalho AR. Development of a phantom for dose distribution verification in stereotactic radiosurgery. Phys Med. 2013;29:461–9. Cusmano D, Fumagalli ML, Marchetti M, Fariselli L, De Martin E. Dosimetric verification of stereotactic radiotherapy dose distributions using Gafchromic EBT3. Med Dosim. 2015;40:226–31. Oliver M, Ansbacher W, Beckham WA. Comparing planning time, delivery time and plan quality for IMRT, Rapid Arc and tomotherapy. J Appl Clin Med Phys. 2009;10:117–31. Soisson ET, Mehta MP, Tome WA. A comparison of helical tomotherapy to circular collimator-based linear-accelerator radiosurgery for the treatment of brain metastases. Am J Clin Oncol. 2011;34:388–94. Klein EE, Hanley J, Bayouth J, Yin FF, Simon W, Dresser S, et al. Task Group 142 report: Quality assurance of medical accelerators. Med Phys. 2009;36: 4197–212.

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26. O’Connor P, Seshadri V, Charles P. Detecting MLC errors in stereotactic radiotherapy plans with a liquid filled ionization chamber array. Australas Phys Eng Sci Med. 2016;39:247–52. 27. Nithiyanantham K, Mani GK, Subramani V, Mueller L, Palaniappan KK, Kataria T. Analysis of direct clinical consequences of MLC positional errors in volumetric-modulated arc therapy using 3D dosimetry system. J Appl Clin Med Phys. 2015;16:296–305. 28. Chen F, Rao M, Ye JS, Shepard DM, Cao D. Impact of leaf motion constraints on IMAT plan quality, deliver accuracy, and efficiency. Med Phys. 2011;38: 6106–18.

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A Feasibility Study on the Use of TomoTherapy Megavoltage Computed Tomography Images for Palliative Patient Treatment Planning

A feasibility study on the use of TomoTherapy megavoltage computed Tomograpy images for palliative Patient tratment planning

J Med Phys. 2017 Jul-Sep; 42(3): 163–170. doi: 10.4103/jmp.JMP_32_17: 10.4103/jmp.JMP_32_17

PMCID: PMC5618464 PMID: 28974863

A Feasibility Study on the Use of TomoTherapy Megavoltage Computed Tomography Images for Palliative Patient Treatment Planning Yunfei Hu,1 Mikel Byrne,2 Ben Archibald-Heeren,2 Matthew Squires,1 Amy Teh,1,2 Kylie Seiffert,1 Sonja Cheers,1 and Yang Wang2 1Radiation Oncology Centres, Gosford, NSW, Australia 2Radiation Oncology Centres, Wahroonga, NSW, Australia

Address for correspondence: Dr. Yunfei Hu, ROC Gosford, 41 William St., Gosford 2250, NSW, Australia. Email: yunfei.hu@roc.team Received 2017 Mar 1; Revised 2017 Jun 12; Accepted 2017 Jun 14. Copyright : © 2017 Journal of Medical Physics This is an open access article distributed under the terms of the Creative Commons Attribution-NonCommercialShareAlike 3.0 License, which allows others to remix, tweak, and build upon the work non-commercially, as long as the author is credited and the new creations are licensed under the identical terms.

Abstract Dedicated rapid access palliative radiation therapy improves patients’ access to care, allowing more timely treatment which would positively impact on quality of life. The TomoTherapy (Accuray, Sunnyvale, CA) system provides megavoltage (MV) fan-beam computed tomography (FBCT) as the image guidance technique, and a module called “statRT” that allows the use of these MV FBCT images for direct planning. The possibility of using this imaging modality for palliative radiotherapy treatment planning is assessed against accepted planning CT standards by performing tests following AAPM TG 66 and an end-to-end measurement. Results have shown that MV FBCT images acquired by TomoTherapy are of sufficient quality for the purpose of target delineation and dose calculation for palliative treatments. Large image noise and extended scan acquisition time are the two main drawbacks, so this imaging modality should only be used for palliative treatments at areas with well-known, easily distinguishable, and relatively immobile targets such as spine and whole brain. Keywords: Imaging, megavoltage computed tomography, palliative radiotherapy, TomoTherapy

INTRODUCTION Most cancer patients will require radiation therapy at some stage during their disease. Among all radiation treatments, 30%–50% of treatments are palliative.[1,2] For palliative treatments, radiation therapy is a locally effective tool, with little to no systemic side effects and mostly mild acute side effects. Furthermore, radiotherapy is important for oncological emergency procedures, such as treatment of obstructions, tumor bleeding, and spinal cord compression.[1] Dedicated rapid access palliative radiation therapy improves patients’ access to care and quality of life.[3] https://www.ncbi.nlm.nih.gov/pmc/articles/PMC5618464/?report=printable

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TomoTherapy is a ring gantry-based radiotherapy treatment system that is also capable of producing highquality megavoltage fan-beam computed tomography (MV FBCT) images for setup verification. TomoTherapy have created a module called “statRT (Accuray, Sunnyvale, CA)” that allows these MV CT images to be used for treatment planning. This module has the benefit of allowing simulation, treatment planning, and treatment to be carried out in a single-visit taking <1 h in total,[4] which in turn minimizes the time to treatment and movement required by patients, which is particularly beneficial for urgent palliative patients who are typically in considerable pain. In fact if patient-specific quality assurance (QA) is performed using calculation based methods, and sufficient time is available on the machine, the simulation, and treatment can actually be performed in a single setup rather than move the patient off the bed for the time required for planning[4] and later put him/her back on the bed. Thus far, research has focused on whether the statRT functionality gives comparable plans to the conventional planning method. [4,5,6] However, relatively little research has systematically verified the image quality of MV CT images against accepted planning CT standards (AAPM TG 66),[7] particularly since the significant changes to the image reconstruction algorithm introduced in the TomoTherapy HDA system (H series v2.0, Accuray, Sunnyvale, CA). The MV CT on TomoTherapy is a spiral CT using 3.5 MV X-rays from the therapeutic linear accelerator and detected with a xenon gas ion chamber array. The MV CT uses a 512 × 512 matrix in a field of view (FOV) of 40 cm resulting in a pixel resolution of 0.78 mm. Fine, normal or coarse slice thicknesses can be selected, which correspond to a couch travel speed of 4, 8, and 12 mm per rotation during imaging.[8] Depending on the selected slice thickness, a reconstruction interval of 1 or 2 mm for fine slices, 2 or 4 mm for normal slices, or 3 or 6 mm for coarse slices can be selected. Time required for one rotation during the CT scan is 10 s.[9] Compared to MV cone beam CT (MV CBCT), MV FBCT uses a thin fan-beam instead of a wide cone beam and acquires images slice by slice. It provides the advantage that scattered X-rays do not contribute as significantly as in MV CBCT and thus results in better image quality.[10] It has been reported that there is a linear relationship between MV FBCT Hounsfield Unit (HU) and the electron density (ED) of materials imaged on TomoTherapy and that the MV CT HU are quite stable, such that the dosimetric end-points vary by <2.0% with various MV CT acquisition parameters.[11,12] The typical imaging dose to patient per acquisition is about 1–2 cGy when a normal pitch with a 2 mm reconstruction interval is selected.[13] Some clinics use TomoTherapy MV CT directly for planning when high-atomic number materials, such as dental fillings or bilateral hip replacement are in the proximity of the PTV which can cause severe imaging artifacts in kV CT scans.[9,10] The aim of this study is to assess the quality of the MV CT images provided by TomoTherapy against accepted planning CT standards to see if MV CT can be used directly for planning with the statRT module, so that radiotherapy patients’ simulation, planning, and first-day treatment can be completed all in one visit on the TomoTherapy Unit, allowing the patients to have accurate, and yet rapid-access palliative radiotherapy treatment to improve their quality of life.

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A well-established CT simulation process should be able to provide spatial information for patient positioning and immobilization as well as anatomical information for contouring and dose calculation. If TomoTherapy MV FBCT was to be used for dose calculation, then it can be argued that the same scope of QA tests that apply to a kV CT scanner should be applied to TomoTherapy. AAPM TG 66[7] has a recommended list for CT QA. As for TomoTherapy, the imaging system and the treatment delivery system share the same gantry and laser systems. Some of the listed check items are already included in the linear accelerator's regular QA programs, such as QA on couch motion and gantry rotation. Apart from these tests, the following QA measures were added to test TomoTherapy's capacity for radiation therapy planning. Those QA tests were also repeated on the kV CT scanner currently used for clinical planning to provide a reference for comparison. https://www.ncbi.nlm.nih.gov/pmc/articles/PMC5618464/?report=printable

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In this study, all kV CT scans were acquired on a GE Discovery PET-CT scanner (GE Healthcare, Little Chalfont, United Kingdom) with 120 kV X-ray at 440 mA and a reconstruction interval of 2.5 mm at a large FOV. All MV CT scans were acquired on TomoTherapy HDA v2.0 with 3.5 MV X-ray and normal slice thickness and a reconstruction interval of 2.0 mm at an FOV of 40 cm. Alignment of wall lasers with respect to the imaging plane TomoTherapy does not have a gantry laser system and only uses a wall-mounted laser system. Its alignment and orientation with respect to the imaging plane must be checked. In this test, the TomoTherapy phantom, or “cheese” phantom, was used. The geometric center of the phantom was aligned to the lasers and then scanned using the MV CT system. The position of the scanned center of the phantom was then compared to the imaging center as indicated by the software to ensure laser-imaging coincidence. Geometric accuracy The geometric accuracy of the system was tested by checking the distance between two known points on a phantom. In this test, the CATPHAN 500 imaging phantom (The Phantom Laboratory, Greenwich, New York, USA), whose three dimensions were physically measured, was used. The phantom was scanned on both kV CT and MV CT, with the three dimensions of the scanned phantom measured and compared to the physically measured values. The difference was expected to be within 1.0 mm.[14] Field uniformity and image noise The field uniformity and image noise were assessed by measuring the CT numbers of a region of homogenous material using the uniformity section of the CATPHAN. The imaging uniformity section in CATPHAN was cast from a uniform material. The material's CT number was designed to be within 2% of water density at standard scanning protocols. After the phantom was scanned, a cylindrical structure of 5 cm radius and 2 cm length was created at the center of the uniformity module, whose average, minimum, and maximum HU values were then provided by the radiotherapy planning system (RTPS). Using the range rule of thumb, the standard deviation (SD) of the structure can then be estimated from the minimum and the maximum HU as: SD ≈ (Maximum – Minimum)/4 The average and the SD HU were then used to assess the field uniformity and the noise of both systems. The SD was estimated because it was not given by the RTPS and would take the authors too long to manually collect enough sample data to calculate it. Spatial resolution The spatial resolution of both imaging systems was assessed using the image resolution section in CATPHAN. This section of the CATPHAN contained a 1 through 21 line-pair per centimeter highresolution test gauge and two impulse sources which were cast into a uniform material. The number of visible pairs of lines was recorded for each imaging system to compare the resolution. Electron/mass density to computed tomography number conversion and computed tomography number constancy TomoTherapy treatment planning system (TPS) converts CT number to mass density (MD) to calculate dose. A CT-ED phantom with density plugs of known physical densities was used to generate CT-MD tables for both systems. The resultant CT-MD curves for both imaging systems were compared to see if a linear relationship can be established between the CT number (in HU) and the MD (g/cm3) for dose calculation. https://www.ncbi.nlm.nih.gov/pmc/articles/PMC5618464/?report=printable

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After the calibration curves were established, to ensure that the CT-MD calibration stayed valid for dose calculations, a simplified QA program, utilizing the TomoTherapy phantom, or the “cheese” phantom, was implemented. The cheese phantom, with a lung and a bone insert replacing the water inserts, was scanned on a regular basis. After scanning, the density of the lung, bone, and water inserts was recorded in the planning system and compared to the baseline data, whose difference was expected to be within 2.0%. The results for this constancy check would not be listed in this study. End-to-end measurement and calculation constancy An end-to-end measurement provides a direct method to quantify the potential errors in the procedure. The end-to-end measurement should be designed such that it simulates real treatment. For this reason, the authors performed end-to-end tests in the Computerized Imaging Reference Systems (CIRS) upper thorax phantom, as it provides multiple measurement positions and areas of inhomogeneity. A calibrated farmer chamber was used for chamber measurement. The CIRS thorax phantom was established according to the same setup used for Australian Clinical Dosimetry Service level III audits[15] as shown in Figures 1 and 2. The CIRS phantom was scanned both with the kV CT and the MV CT and saved as different QA phantoms in the TomoTherapy planning system for future calculations. Araki reported that when a thin-walled cylindrical chamber was used for measurements in a heterogeneous phantom that includes solid water, lung, and bone plastic materials, for a 6 MV photon beam on a conventional linear accelerator, the perturbation factor introduced by the chamber due to the replacement of the air cavity, nonwater equivalence of the chamber wall, and the stem and nonair equivalence of the central electrode could be up to 2% and 3.5% for lung and bone, respectively, depending on the field size. [16] This effect can be more significant for TomoTherapy because of the lack of electron equilibrium from the small segmented fields in TomoTherapy helical delivery mode. As a result, to reduce the chamber perturbation in the bone measurements, a water insert with chamber cavity was inserted in the bone cavity instead of the bone insert both in the measurement and in the TPS calculation. This is the same method applied in ARPANSA level III audits.[15] A total of three complex TomoTherapy helical plans were chosen whose 50% isodose distributions covered several chamber cavities so that multiple measurements at different points were possible. These plans were copied and recalculated on both the MV CT and the kV CT scanned CIRS phantom. Although scanned by different CT modalities, the exact same isocenter position was used when recalculating the plan. As is shown in Figure 2, 10 measurement points were available in the phantom. Points 1–5 sit in a homogeneous water density. Points 6–9 sit in a homogeneous lung density. Point 10 sits in a water density but is surrounded by a bone ring representing spine. Due to its large cavity, the farmer chamber was deemed unsuitable for measurement at areas with high-dose gradient. For this reason, with each plan, only some points were chosen as chamber measurement points depending on where the dose distribution was relatively homogeneous. The reading was converted to dose after corrections were applied. This dose reading was then compared to the predicted point doses calculated on the kV CT and the MV CT phantom. As a routine check of the dose calculation constancy, a plan was recalculated on an MV CT utilizing the adaptive planning module provided by TomoTherapy. The cheese phantom was scanned on the MV CT, and a predesigned QA plan was then recomputed on the MV scan in the adaptive module, whose resultant dose distributions were compared to the original plan computed on the same phantom scanned by the kV

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CT. The difference was expected to be within 2.0%. This test was relatively simple and provided neither inhomogeneity calculations nor direct detector measurement, but was efficient in quickly checking the dose calculation constancy of the MV CT. Its results were not listed in this study.

RESULTS Alignment of wall lasers with respect to the imaging plane Table 1 lists the results of this part of the test. Geometric accuracy Table 2 lists the results of this part of the test. Field uniformity and image noise Table 3 lists the result for this part of the test. Figures 3 and 4 show the screen capture of the CATPHAN uniformity section from both imaging systems. Spatial resolution Table 4 lists the result for this part of the test. Figures 5 and 6 show the screen capture of the CATPHAN image resolution section from both imaging systems. Electron/mass density to CT number conversion Table 5 shows the results of CT-MD tables generated from the CT-ED phantom for kV CT and MV CT. Figure 7 shows the CT-MD curve for both imaging systems. End-to-end measurements Table 6 lists the results for the end-to-end measurements.

DISCUSSIONS Alignment of wall lasers with respect to the imaging plane From Table 1, it is noted that TomoTherapy's laser system aligns well with the MV CT imaging system to within 1.0 mm. As such the laser system can be used as guidance for patient positioning during the initial image acquisition. This alignment is checked on a regular basis. Geometric accuracy From Table 2, it is noted that the detected dimensions from both imaging systems are within 1.0 mm of the physical dimensions. It indicated that geometric dimensions can be determined accurately from both imaging systems. The difference from the MV CT system was slightly higher but was of no statistical significance given the image pixel size, as the P value, when calculated by the N-1 Chi-square test,[17] is more than 0.05 (0.0586). No obvious geometric distortions were observed from both image sets. Field uniformity and image noise

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From the result in this section, it is noted that the average MD read from the kV CT was 1.007 g/cm3, and from MV CT was 0.995 g/cm3, converted from the average CT number calculated by the RTPS using the CT-MD table established in the MD to CT number conversion test. Both results were within ±1.0% of the expected MD of water (1.0 g.cm3). However, from the SD values as well as screen captures from Figures 4 and 5, it was noted that MV CT has a much larger noise compared to kV CT. MV CT tends to have a worse signal-to-noise ratio compared to kV CT for two main reasons: 1. In the MV CT range where Compton scattering dominates, most of the scattered photons produced travel forward at a small angle deviation from the incident photon and will likely be absorbed by the detector as noise. In contrast in kV CT range where the photoelectric effect is dominant, the photons are fully absorbed, and the ejected electrons are usually emitted at 90° to the incident photon and thus ignored by the detector;[18] and 2. The absorbed dose per photon emitted is much higher for MV than for kV and therefore to limit the imaging dose fewer photons are used in MV FBCT[14] compared to kV CT. Large image noise could make both automatic and manual anatomy delineation difficult. Intra-imaging motion from the patient would further increase the noise level. Spatial resolution From the results in this section, it is noted that the image resolution provided by MV CT is poorer compared to that from a conventional CT scanner. The poor spatial resolution alone would not reduce accuracy in dose calculation, but it would introduce difficulties in the delineation of targets and critical structures. As nowadays volume-based optimization is widely used in many commercial radiation planning systems such as the TomoTherapy planning station, accurate identification, and delineation of both the targets and the organs-at-risk are critical for optimal plan outcome. They are also important in the evaluation of the plan quality. The poor spatial resolution would consequently be likely to downgrade the plan accuracy and the plan quality, especially for those plans that use volume-based optimization. Electron/mass density to computed tomography number conversion From Figure 8, it was noted that for both kV CT and MV CT, the relationship between CT number and MD is linear, making it possible to establish a CT-MD curve for both scans to achieve dose calculation. Both curves are similar for materials with density equal to or lower than water (1.0 g/cm3), but for materials with density higher than water, the difference between the curves is significant. Compared to kV CT, the part of the curve beyond water density from MV CT is sharper. This indicates that the MV CTs would have a poorer contrast compared to kV CT, as the CT number difference for materials of different densities is smaller and thus more difficult to distinguish visually. This is because in the MeV photon energy range used in MV FBCT, Compton scattering effect is predominant in attenuating the beams, which is almost independent of the atomic number Z of the material. In contrast, in the keV range used in kV CT, the predominant interaction is the photoelectric effect, whose attenuation is highly dependent on the atomic number Z of the material. As a result, while both kV and MV CT depend on electron densities, kV CT tends to display sharper contrast in the visualization of materials with differing atomic numbers. At the same time, this also means MV CT produces less artifact and image distortion when high atomic number material is present within the scan.[10] Note that this effect was not specifically due to materials having a density greater than water, but rather was because materials with density greater than water tend to have greater atomic number. End-to-end measurements

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The average absolute difference for calculations based on kV CT images was 1.76%, with an absolute SD of ±1.30%. The average absolute difference for calculations based on MV CT images was 1.78%, with an absolute SD of ±0.87%. These results agree with what was reported in the previous studies.[11,12] From all the above results, it was noted that the largest problem with the MV FBCT was the large noise compared to kV CT, which resulted in uncertainties in target delineation. The noise could have larger impact on patients due to more complicated geometries and patient motion. MV CT also demonstrated a poorer spatial resolution and less contrast for materials of MD more than water, both of which would make accurate target delineation more difficult. As inverse planning optimization is fully based on structures, inaccuracy in target delineation can potentially degrade the plan quality. As a result, users should be cautious with the use of TomoTherapy MV CT as the primary image set in plans that use inverse planning technique. The results also indicate that for TomoTherapy MV CT an accurate CT-MD curve can be established for dose calculation and point doses calculated on both MV CT and kV CT agree well with the measured values, despite its relatively poor image quality due to high noise, low contrast, and low spatial resolution. The imaging system also provides accurate geometric measurements. As a consequence, the imaging system can be used for direct dose calculation in forward planning for areas with well-known structures, as long as proper commissioning tests are performed and proper QA systems are maintained. As such one suitable application of TomoTherapy MV CT is palliative radiation therapy treatment planning, where structure delineation is primarily determined from bony anatomy, and larger margins can be justified. All test results have indicated that adequate geometric and dosimetric information can be provided by the MV CT alone for these types of treatment. The use of TomoTherapy MV CT for palliative planning allows patients to gain rapid access to palliative radiation therapy with minimal patient movement required. Consequently, patients’ access to quality care and an improved quality of life is made possible.[3,19] The other advantage provided using TomoTherapy MV CT in conjunction with a TomoTherapy linear accelerator for palliative treatment is that as in this procedure; the patient is both scanned and treated on the same TomoTherapy couch, the accuracy in reproducing the patient's position from scanning to treatment delivery can be greatly improved. MV CT produces less artifact and image distortion when high atomic number material is present within the scan.[10] As such it provides a significant advantage over kV CT for patients with high atomic number implants such as metal dental fillings or hip prosthesis. One example is given below, where the patient not only requires treatment around the lower lip but also has titanium dental fillings. The patient was scanned with both kV CT and MV CT, displayed in Figure 8. It is noted that there is no image artifact on the MV CT scan, but considerable streaking appears on the kV CT scan. The presence of artifacts requires density overrides to the areas affected by the artifact and also reduces the accuracy of structure delineation. For this reason, for patients with high atomic number implants, TomoTherapy MV CT can be acquired and used as the secondary image set, which can be fused to the kV CT images to aid target delineation, if not used directly as the primary image set for planning. One potential source of error that was not analyzed by the described tests was the imaging artifact caused by patient's intrafractional motion. Since the MVFB CT acquisition on TomoTherapy takes much longer than a kV CT, patient motion becomes a significant problem. One example is shown below in Figure 9, where the artifact caused by patient's respiratory motion can be clearly observed. Although palliative treatments are most likely prescribed to patients with bone metastases, brain metastases, and spinal cord compression[1] which are relatively motionless anatomical sites compared to others such as lung and liver, the motion effect can still be significant with extended imaging acquisition time. This is more of a problem during initial image acquisition, as during treatment delivery patient motion can be accounted for by adding proper margin or overshoot in planning to account for organ motion.[20]

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CONCLUSION The study assessed whether TomoTherapy MV FBCT images have comparable image qualities to conventional kV CT images and can be used directly for radiotherapy planning. Despite its long image acquisition time and relatively large noise, the authors concluded that TomoTherapy MV CT images provide adequate information for the delineation and planning of palliative radiotherapy patients whose treatment sites are relatively immobile and well-distinguishable. As such, it can be used together with the statRT module provided by TomoTherapy for the simulation, planning, and treatment of palliative radiotherapy patients. Compared to a conventional radiotherapy treatment workflow that involves the use of a separate CT scanner and a treatment unit, using TomoTherapy as both the imaging unit and the treatment unit for palliative radiotherapy patients provides the following advantages: 1. Rapid access to treatment. Using the statRT software, the time to treatment has been reported as under 1 h.[4] Our test run results also support this timing. In contrast, the conventional planning workflow usually requires at least 1-day turnaround. As studies have shown that dedicated rapid access palliative radiation therapy improves patients’ access to care,[3] the quick access to radiation therapy, and the rapid workflow will potentially improve these patients’ quality of life significantly; 2. Better reproducibility in patient positioning from simulation to treatment, as the patient is simulated and treated on the same unit. The turnaround time from simulation to treatment is also greatly reduced; and 3. For less-mobile palliative patients, it is possible to allow the patient to stay on the TomoTherapy couch from simulation until treatment, which minimizes the chance of doing damage to the patients and reduces reduced potential aggravating morbidity pain during bed transfer. The pretreatment QA for these patients can be performed with QA programs that are based on calculations and do not require direct dose measurements. As a result, it is feasible to use the TomoTherapy unit for the simulation, planning, and treatment of palliative radiotherapy patients. Once TomoTherapy planning is available in an open-source planning system, the workflow can be further optimized through the implementation of scripting and automation in steps such as image transfers, contouring, plan setup and plan check, so that the turnaround time for the patient can be further reduced, thus further improving patient quality of life. Financial support and sponsorship Nil. Conflicts of interest There are no conflicts of interest.

REFERENCES 1. van Oorschot B, Rades D, Schulze W, Beckmann G, Feyer P. Palliative radiotherapy – New approaches. Semin Oncol. 2011;38:443–9. [PubMed: 21600376] 2. Mackillop WJ, Kong W. Estimating the need for palliative radiation therapy: A benchmarking approach. Int J Radiat Oncol Biol Phys. 2016;94:51–9. [PubMed: 26700702] 3. Dennis K, Linden K, Balboni T, Chow E. Rapid access palliative radiation therapy programs: An efficient model of care. Future Oncol. 2015;11:2417–26. [PubMed: 26271002] 4. Rong Y, Yadav P, Paliwal B, Shang L, Welsh JS. A planning study for palliative spine treatment using StatRT and megavoltage CT simulation. J Appl Clin Med Phys. 2010;12:3348. [PubMed: 21330983] https://www.ncbi.nlm.nih.gov/pmc/articles/PMC5618464/?report=printable

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5. McIntosh A, Dunlap N, Sheng K, Geezey C, Turner B, Blackhall L, et al. Helical tomotherapy-based STAT RT: Dosimetric evaluation for clinical implementation of a rapid radiation palliation program. Med Dosim. 2010;35:280–6. [PubMed: 19944589] 6. Dunlap N, McIntosh A, Sheng K, Yang W, Turner B, Shoushtari A, et al. Helical tomotherapy-based STAT stereotactic body radiation therapy: Dosimetric evaluation for a real-time SBRT treatment planning and delivery program. Med Dosim. 2010;35:312–9. [PubMed: 21055611] 7. Mutic S, Palta JR, Butker EK, Das IJ, Huq MS, Loo LN, et al. Quality assurance for computedtomography simulators and the computed-tomography-simulation process: Report of the AAPM Radiation Therapy Committee Task Group No 66. Med Phys. 2003;30:2762–92. [PubMed: 14596315] 8. TomoTherapy Incorporated. MVCT imaging with J1 TomoImage beam. Application Note for the Tomotherapy Hiart Treatment System. TomoTherapy Incorporated. 2010 9. Sterzing F, Kalz J, Sroka-Perez G, Schubert K, Bischof M, Roder F, et al. Megavoltage CT in helical tomotherapy – Clinical advantages and limitations of special physical characteristics. Technol Cancer Res Treat. 2009;8:343–52. [PubMed: 19754210] 10. Yang C, Liu T, Jennelle RL, Ryu JK, Vijayakumar S, Purdy JA, et al. Utility of megavoltage fan-beam CT for treatment planning in a head-and-neck cancer patient with extensive dental fillings undergoing helical tomotherapy. Med Dosim. 2010;35:108–14. [PubMed: 19931022] 11. Meeks SL, Harmon JF, Jr, Langen KM, Willoughby TR, Wagner TH, Kupelian PA. Performance characterization of megavoltage computed tomography imaging on a helical tomotherapy unit. Med Phys. 2005;32:2673–81. [PubMed: 16193798] 12. Langen KM, Meeks SL, Poole DO, Wagner TH, Willoughby TR, Kupelian PA, et al. The use of megavoltage CT (MVCT) images for dose recomputations. Phys Med Biol. 2005;50:4259–76. [PubMed: 16148392] 13. Held M, Cremers F, Sneed PK, Braunstein S, Fogh SE, Nakamura J, et al. Assessment of image quality and dose calculation accuracy on kV CBCT, MV CBCT, and MV CT images for urgent palliative radiotherapy treatments. J Appl Clin Med Phys. 2016;17:279–90. [PMCID: PMC5874969] [PubMed: 27074487] 14. Ruchala KJ, Olivera GH, Schloesser EA, Mackie TR. Megavoltage CT on a tomotherapy system. Phys Med Biol. 1999;44:2597–621. [PubMed: 10533931] 15. Australian Clinical Dosimetry Service. Instructions for the ACDS level III audit: Wedged and Asymmetric fields with Inhomogeneities for Lung treatments (WAIL) Int ACDS Rep. 2014 16. Araki F. Monte Carlo-based correction factors for ion chamber dosimetry in heterogeneous phantoms for megavoltage photon beams. Phys Med Biol. 2012;57:7615–27. [PubMed: 23103477] 17. Karl P. On the criterion that a given system of deviations from the probable in the case of a correlated system of variables is such that it can be reasonably supposed to have arisen from random sampling. Philos Mag Ser. 5 19;0;50:157–75. 18. Khan FM. The Physics of Radiation Therapy. 3rd ed. Baltimore: Williams & Wilkins; 2003. p. 67. 19. Yeo R, Campbell T, Fairchild A. Is weekend radiation therapy always justified. J Med Imaging Radiat Sci. 2012;43:3–24. 20. Squires M, Hu Y, Byrne M, Archibald-Heeren B, Cheers S, Bosco B, et al. Static beam tomotherapy as an optimisation method in whole-breast radiation therapy (WBRT) J Med Radiat Sci. 2017;6:1–9. [PubMed: 28580762] https://www.ncbi.nlm.nih.gov/pmc/articles/PMC5618464/?report=printable

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Figures and Tables

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Figure 1

CIRS thorax phantom setup on TomoTherapy for megavoltage computed tomography scan

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Figure 2

A computed tomography slice of the CIRS upper thorax phantom used in the end to end measurements. The numbers correspond to the measurement positions in the phantom

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Table 1 Laser alignment test results

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Table 2 Geometric accuracy test results

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Table 3 Field uniformity and image noise test results

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Figure 4

Megavoltage computed tomography uniformity scan results

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Table 4 Spatial resolution test results

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Figure 5

Open in a separate window kV computed tomography image resolution scan results

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Figure 6

Megavoltage computed tomography image resolution scan results

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Table 5 Mass density to computed tomography number conversion results

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Open in a separate window Computed tomography-mass density curves for GE kV computed tomography and TomoTherapy megavoltage computed tomography. At areas beyond water (mass density >1.0 g/cm3) megavoltage computed tomography showed a much sharper curve

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Table 6 End-to-end point dose measurement results

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Figure 8

On the left: Megavoltage computed tomography scan of a patient with titanium dental implant. On the right: kV computed tomography scan of the same patient. Imaging artifact caused by the implant is more obvious. If the kV scan is used solely for planning, a density override would be required for those areas affected by artifact, thus slowing down the workflow

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Lateral and longitudinal image artifact caused by patient's motion during imaging acquisition Articles from Journal of Medical Physics are provided here courtesy of Wolters Kluwer -- Medknow Publications

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Assessment of inter and intra-fractional volume of bladder and body contour by megavoltage computed tomography in helical tomotherapy for pelvic malignancy

Original Article Radiat Oncol J 2018;36(3):235-240 https://doi.org/10.3857/roj.2018.00185 pISSN 2234-1900 · eISSN 2234-3156

Assessment of inter- and intra-fractional volume of bladder and body contour by mega-voltage computed tomography in helical tomotherapy for pelvic malignancy Sunghyun Kim, MD, Sei Hwan You, MD, Young Ju Eum, BA, RTT Department of Radiation Oncology, Yonsei University Wonju College of Medicine, Wonju, Korea

Purpose: We describe the daily bladder volume change observed by mega-voltage computed tomography (MVCT) during pelvic radiotherapy with potential predictors of increased bladder volume variations. Materials and Methods: For 41 patients who received pelvic area irradiation, the volumes of bladder and pelvic body contour were measured twice a day with pre- and post-irradiation MVCT from the 1st to the 10th fraction. The median prescription dose was 20 Gy (range, 18 to 30 Gy) up to a 10th fraction. The upper and lower margin of MVCT scanning was consistent during the daily treatments. The median age was 69 years (range, 33 to 86 years) and 10 patients (24.4%) were treated postoperatively. Results: Overall bladder volume on planning computed tomography was 139.7 ± 92.8 mL. Generally, post-irradiation bladder volume (POSTBV) was larger than pre-irradiation bladder volume (PREBV) (p < 0.001). The mean PREBV and POSTBV was reduced after 10 fraction treatments by 21.3% (p = 0.028) and 25.4% (p = 0.007), respectively. The MVCT-scanned body contour volumes had a tendency to decrease as the treatment sessions progressed (p = 0.043 at the 8th fraction and p = 0.044 at the 10th fraction). There was a statistically significant correlation between bladder filling time and PREBV (p = 0.001). Conclusion: Daily MVCT-based bladder volume assessment was feasible both intra- and inter-fractionally. Keywords: Mega-voltage computed tomography, Radiotherapy, Pelvic neoplasms, Urinary bladder

Introduction Urinary bladder filling is a beneficial process for sparing the small intestine during radiotherapy (RT) to the pelvic area. The achievement of consistent daily bladder expansion is one of the significant issues. Bladder volume changes can affect radiation dose distribution to the bladder itself and adjacent pelvic organs. Significant volume changes can compromise sophisticated planning data such as intensity-modulated radiotherapy (IMRT) [1-3]. Thus, the bladder volume needs

to be kept consistent throughout all of the fractionated treatment sessions. Many attempts to assess bladder volume during RT have been conducted. Ultrasonography, which is one of the useful tools for bladder volume measurement, has its restrictions in accurate set-up and consistent daily bladder volume measurements because it is a separate process during RT [4-9]. An alternative method to compensate for this problem can be a mega-voltage computed tomography (MVCT) system, which is actively used for volumetric set-up error correction during

Received 11 April 2018, Revised 22 June 2018, Accepted 31 July 2018. Correspondence: Sei Hwan You, MD, Department of Radiation Oncology, Yonsei University Wonju College of Medicine, 20 Ilsan-ro, Wonju 26426, Korea. Tel: +82-33-741-1518, Fax: +82-33-741-1519, E-mail: ys3259@yonsei.ac.kr This is an Open Access article distributed under the terms of the Creative Commons Attribution Non-Commercial License (http://creativecommons.org/ licenses/by-nc/4.0/) which permits unrestricted non-commercial use, distribution, and reproduction in any medium, provided the original work is properly cited.

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Bladder volume change in tomotherapy tomotherapy. Despite a relatively low resolution, it is effective in improving treatment accuracy by combining a scanning system with RT. Due to mega-volt energy beam characteristics, bony landmark-dependent images are the main references for error correction. However, MVCT scanning has been applied without a definite protocol. In a typical example, the scanning range is usually different for each treatment session. In addition, soft tissues such as the urinary bladder are not used so actively in set-up process. Especially, the urinary bladder needs to be utilized for set-up because the anatomic boundary is detectable on MVCT images as seen in previous pelvic tomotherapy studies [10-14]. Most assessments of bladder volume are based upon an intentional filling method, which is associated with practical limitations such as lack of objectivity and unpredictable urination timing. Thus, the validity of bladder filling requires more detailed assessment in the era of IMRT. In this study, we intended to quantify the daily bladder volume changes during the initial course of RT for pelvic malignancy using MVCT images and to assess the feasible set-up techniques with systematic MVCT application.

Materials and Methods 1. Patient characteristics Between October 2014 and January 2016, 52 consecutive patients with pelvic irradiation indication were enrolled after patient approval for this prospective study. Among them, 11 patients were excluded because of treatment interruption or poor MVCT image quality and 41 patients were finally analysed. All patients received helical tomotherapy using the Hi-Art System (TomoTherapy Inc., Madison, WI, USA). None had severe urinary dysfunction initially. Their median age was 69 years (range, 33 to 86 years). Their diagnoses were prostate cancer, rectal cancer, cervix cancer, bladder cancer, and other pelvic area tumours. This study was approved by the Institutional Review Board of Yonsei University Wonju College of Medicine (No. YWMR-14-7-024). All patients underwent simulation with supine position using computed tomography (CT) of a 3–5 mm slice thickness including the pelvis and lower abdomen. Then target delineation was drawn using Pinnacle v7.6 radiotherapy planning systems (Philips, Cleveland, OH, USA) and was optimized to reflect each disease status. RT was planned as three-dimensional RT or IMRT. Ten patients (24.4%) were treated with postoperative RT. IMRT with a helical mode was applied to 13 patients (31.7%) and the others were irradiated https://doi.org/10.3857/roj.2018.00185

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by a three-dimensional conformal method with a direct mode. MVCT analysis was performed for the initial 10 consecutive fractions of each RT course regardless of the total prescription dose focusing on the bladder volume and its dose distribution. Patient characteristics related to clinical factors are displayed in Table 1.

Table 1. Patients’ characteristics (n = 41) Characteristic Age (yr) Median (range) Sex Male Female Diagnosis Prostate cancer Rectal cancer Cervix cancer Bladder cancer Others Postoperative radiotherapy Yes No Endorectal balloon insertion Yes No Radiotherapy technique Three-dimensional conformal Intensity-modulated

Value 66.3 ± 12.4 69 (33–86) 31 (75.6) 10 (24.4) 14 (34.1) 21 (51.2) 3 (7.3) 1 (2.4) 2 (4.9) 10 (24.4) 31 (75.6) 14 (34.1) 27 (65.9) 28 (68.3) 13 (31.7)

Values are presented as mean ± standard deviation or number (%).

2. Bladder dosimetry on MVCT images All patients were irradiated in a supine position with natural bladder filling. Patients with prostate cancer were treated with urination for 1–1.5 hours before treatment but were not strictly enforced, and no other bladder filling training was given to other patients. The MVCT scan was performed right before and after the daily irradiation. The pre-irradiation MVCT scan (PRESCAN) image was matched with the planning CT image based upon the three-dimensional bony structure followed by shifting the couch to the optimal position. After irradiation, a post-irradiation MVCT scan (POSTSCAN) was taken in the same position, in which the original reference point was maintained. Basically, the MVCT scan range was set from the sacral promontory level to the lower margin of the ischium and it was partially modified according to bladder www.e-roj.org

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Sunghyun Kim, et al volume extent. This scan range was maintained consistently from the 1st fraction to the 10th fraction for each patient’s RT course for both PRESCAN and POSTSCAN. The pelvic body outline volume (POV), which includes pelvic organs, skeletal, and soft tissue, was also calculated by contouring the outermost skin area on MVCT image slices for a consistent scan range from the 1st fraction to the 10th fraction for each patient’s RT course. This was also done by one radiation oncologist using the Hi-Art System for both PRESCAN and POSTSCAN and the method of volume measurement was the same as for bladder volume. Bladder volume at the planning CT was measured on a kilovoltage CT image of 3–5 mm thickness as a routine planning process. During the RT course, it was calculated by contouring the bladder wall on every 6-mm slice of the MVCT images. This was performed by one radiation oncologist using a HiArt System and the volume was measured by an operating planning process from the 1st fraction to the 10th fraction for each patient’s RT course for both PRESCAN and POSTSCAN (Fig. 1). We analysed the inter-fractional variability in daily bladder volumes according to the prescription dose to the clinical target volume (CTV) and bladder dose distribution from the 1st fraction to the 10th fraction. In addition, the intra-fractional variability was assessed by comparing PRESCAN data with POSTSCAN data for each RT fraction. Planning CT-based dosimetric parameters for the initial 10 fractions are shown in Table 2. 3. Clinical factors We assessed the correlations between bladder volume change and potential clinical predictors such as urinary ascorbic acid, urinary white blood cells, and urinary red blood cells along with surgical intervention, bladder filling sensation, bladder filling time, and time gap between PRESCAN and POSTSCAN. The bladder filling time was defined as the interval from the last urination to the PRESCAN time point for each fraction. 4. Statistical analysis A paired t-test was used for comparison of the PRESCAN and POSTSCAN data. Surgical intervention was analyzed by independent t-test, the correlations between other clinical factors and bladder volume changes were evaluated by the Pearson correlation method. Statistical significance was defined at the p < 0.05 level. The SPSS version 20.0 (IBM, Armonk, NY, USA) program was used for analysis.

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Fig. 1. An example of a mega-voltage computed tomography image and bladder contouring.

Table 2. Planning CT-based dosimetric parameters in terms of consecutive 10 fractions Parameter

Value 20.0 (18.0–30.0) 105.9 (24.9–354.5) 139.7

Prescription dose (Gy) Bladder volume (mL) Mean Bladder dose (Gy) Mean Max Min

14.9 (5.6–19.3) 20.3 (14.4–28.4) 7.0 (0.4–17.9)

Values are presented as median (range). CT, computed tomography.

Results All planned bladder volume data were acquired successfully. The median prescription dose to the CTV was 20 Gy (range, 18 to 30 Gy) for the initial 10 fractions. The mean bladder volume on planning CT was 139.7 ± 92.8 mL and its mean, maximum, and minimum doses were 14.7 ± 3.0 Gy, 20.8 ± 2.9 Gy, and 8.2 ± 3.6 Gy, respectively, up to the 10th fraction. The mean bladder filling time was 75.3 ± 44.8 minutes (range, 4 to 210 minutes). It took an average of 13.6 ± 4.8 minutes (range, 9 to 41 minutes) from PRESCAN to POSTSCAN. The bladder filling sensation was categorized into three stages of the patients’ subjective estimation for the overall treatment sessions, full, moderate, and empty comprised 10.4%, 53.7%, and 35.8%, respectively.

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2. Radiation influence on other clinical factors Mean POV values with standard deviation before and after irradiation from the 1st to the 10th fraction are displayed in Fig. 4. Unlike bladder volume (PREBV and POSTBV) change patterns, the intra-fractional POV changes were not remarkable. POSTSCAN volume showed a restrictive decrease tendency at the 8th (p = 0.043) and 10th (p = 0.044) treatment session compared with PRESCAN volume. These volume change patterns had a strong tendency towards a correlation with pre-irradiation surgery at some treatment sessions (p = 0.057 at the 3rd fraction, p = 0.069 at the 6th fraction). For the cystitis assessment, only the planning maximum dose was moderately correlated with an increase in urine white blood cell numbers after the 10th fraction (Pearson r = 0.49, p = 0.011). As age increased, PREBV was found to be statistically significantly reduced, but the correlation was very weak (Pearson r = -0.138, p = 0.005). The other potential clinical predictors such as urinary ascorbic acid, urinary red blood cells, surgical intervention, ERB, and time gap between PRESCAN and POSTSCAN did not show a significant relationship with the change pattern of bladder volume or POV. There was no statistically significant difference in PREBV between prostate cancer (118.23 ± 75.22 mL) and rectal cancer (116.80 ± 60.09 mL). In the case of other diseases, statistical significance could not be assessed because the number of the patients was too small.

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300

Before irradiation After irradiation

Bladder volume (mL)

250 200 150 100 50 0

4 5 6 7 Daily fraction number

Fig. 2. Mean values of bladder volume with standard deviation before and after irradiation from the 1st to the 10th fraction.

PRESCAN bladder volume (mL)

1. MVCT bladder volume The mean PRESCAN bladder volume (PREBV) from the 1st to the 10th fraction was 140.4 ± 90.2 mL (1st fraction), 111.9 ± 59.2 mL (2nd fraction), 126.1 ± 65.0 mL (3rd fraction), 124.5 ± 78.6 mL (4th fraction), 131.8 ± 75.4 mL (5th fraction), 112.6 ± 65.6 mL (6th fraction), 118.1 ± 72.7 mL (7th fraction), 107.6 ± 61.1 mL (8th fraction), 112.1 ± 77.4 mL (9th fraction), and 110.5 ± 63.8 mL (10th fraction), respectively. A mean PREBV reduction of 21.3% was observed between the 1st and the 10th fraction (p = 0.028). A significant mean POSTSCAN bladder volume (POSTBV) reduction was also found between the 1st and the 10th fraction (25.4%, p = 0.007) (Fig. 2). For all treatment sessions, the POSTBV was larger than PREBV (p < 0.001). Pre-irradiation surgery, irradiation technique, and bladder dosimetric parameters were not related to bladder volume changes. There was a weak relationship only between bladder filling sensation and bladder filling time (Pearson r = 0.282, p = 0.001) (Fig. 3).

400 350 300 250 200 150 100 50 0

100 150 Bladder filling time (min)

200

250

Fig. 3. Correlation of PRESCAN bladder volume and bladder filling time (Pearson r = 0.282, p = 0.001).

Discussion and Conclusion The main objective of this study was to assess inter- and intra-fractional bladder volume during RT to the pelvic area. Generally, MVCT was a useful option for bladder volume assessment as well as set-up error correction. Intra-fractional bladder volume changes were found to be different for each treatment. These data suggest that the current bladder filling system should be improved and more careful approaches are needed in IMRT. For the patients in our study, the natural bladder filling method was applied without strict urination training for full bladder. Our protocol for consistent bladder www.e-roj.org

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Before irradiation After irradiation

Scanned body contour volume (mL)

11,000 10,000 9,000 8,000 7,000 6,000 5,000

4 5 6 7 Daily fraction number

Fig. 4. Mean values of scanned pelvic body outline volume with standard deviation before and after irradiation from the 1st to the 10th fraction.

volume was based upon non-stressful urination with supine position to avoid the setup instability caused by respiratory movements. Also, elderly patients, which composed a large amount of groups in prostate cancer and rectal cancer in our study, usually had problems in urination control. Thus, despite our less strict regulation, our protocol seems to be efficient for the treatment of prostate cancer, bladder cancer, and rectal cancer, which may be supported by our MVCT results. When using ultrasound-based measurements, patients must have their bladder volume measured separately from the RT session, which results in anatomic inconsistency. In contrast, MVCT can be a good monitoring tool because the bladder volume changes can be easily detected as an extension of the radiation treatment without a separate set-up process. Due to its relatively low resolution, MVCT application has been usually confined to bony structure comparisons in setup error corrections. However, in most cases in our study, the bladder border was easily identified on MVCT except for a few patients with unstable bowel status. Unlike ultrasonograms, MVCT could provide information on its anatomic relationship to surrounding organs as well as volumetric values of the bladder. In addition, MVCT of a consistent scan range through all treatment sessions resulted in the same volume variation pattern as that of ultrasonography in previous studies [47,10,15]. Thus, the MVCT-mediated approach in our study appears to be valid. At present, due to large inter-fractional variation, it is 239

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difficult to find a suitable protocol that ensures consistent bladder volumes [5,7,10]. Actually, intra-fractional volume increase is an inevitable problem. However, dosimetric and clinical effects might not be large considering the modern irradiation process in pelvic area RT except bladder cancer. Rather, other clinical factors such as urination pattern, cystitis, or adjacent tissue effect may be more influential than the bladder volume itself. On the other hand, inter-fractional variation can be an issue to pay attention to because of its clinical effects and the possibility for improvement. Despite many unknown variables, regular volume reduction is observed as the treatment session progresses [4-7,10,15,16]. Our study also revealed a bladder volume decline even in the early phase of the treatment course, which can be explained by a low dose effect or tissue susceptibility including cystitis or fibrosis [17,18]. A similar decline of inter-fractional POV might not be overlooked considering the correlation with bladder volume change. Despite an intra-fractional bladder volume increase, the corresponding intra-fractional POV had a tendency to decrease paradoxically, which was contrary to existing concepts. From these results, we can guess the possibility of a physiological response to surrounding tissue elasticity changes. This point should be discussed with along with a more systematic approach in future studies. Subjective patient assessments or biofeedback has its limitations in controlling bladder volume consistently [6]. In our study, self-assessment for voiding and bladder filling sensation was partly reliable. However, it is not sufficient for precisely controlling bladder volume. For these reasons, a more systematic bladder filling method should be devised in the era of adaptive RT, especially for the pelvic area considering the need for whole pelvic tissue stability as well as bladder volume consistency for accurate dose delivery. Other limitations of this study might be the absence of principle identification of bladder volume decreases and the insufficient resolution of the MVCT image. Improvement of these design aspects is desirable in the future. Nevertheless, our results can be meaningful in that the method of maintaining a constant MVCT scan range was applied, demonstrating the feasibility of the standardized volumetric set-up method. In conclusion, daily MVCT-mediated bladder and body contour volume assessment was feasible both intra- and interfractionally. We expect that MVCT can be used to evaluate the bladder volume easily and accurately, and it will be of some help for better RT.

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Conflict of Interest No potential conflict of interest relevant to this article was reported.

Acknowledgments This study was supported by a grant from the Korea Health Technology R&D Project, Ministry of Health & Welfare, Republic of Korea (No. HI10C0051 [A100054]).

References 1. Nairz O, Merz F, Deutschmann H, et al. A strategy for the use of image-guided radiotherapy (IGRT) on linear accelerators and its impact on treatment margins for prostate cancer patients. Strahlenther Onkol 2008;184:663-7. 2. Tsai CL, Wu JK, Wang CW, Hsu FM, Lai MK, Cheng JC. Using cone-beam computed tomography to evaluate the impact of bladder filling status on target position in prostate radiotherapy. Strahlenther Onkol 2009;185:588-95. 3. Moiseenko V, Liu M, Kristensen S, Gelowitz G, Berthelet E. Effect of bladder filling on doses to prostate and organs at risk: a treatment planning study. J Appl Clin Med Phys 2006;8:55-68. 4. Chang JS, Yoon HI, Cha HJ, et al. Bladder filling variations during concurrent chemotherapy and pelvic radiotherapy in rectal cancer patients: early experience of bladder volume assessment using ultrasound scanner. Radiat Oncol J 2013;31:41-7. 5. Ahmad R, Hoogeman MS, Quint S, Mens JW, de Pree I, Heijmen BJ. Inter-fraction bladder filling variations and time trends for cervical cancer patients assessed with a portable 3-dimensional ultrasound bladder scanner. Radiother Oncol 2008;89:172-9. 6. Stam MR, van Lin EN, van der Vight LP, Kaanders JH, Visser AG. Bladder filling variation during radiation treatment of prostate cancer: can the use of a bladder ultrasound scanner and biofeedback optimize bladder filling? Int J Radiat Oncol Biol Phys 2006;65:371-7. 7. O'Doherty UM, McNair HA, Norman AR, et al. Variability of bladder filling in patients receiving radical radiotherapy to the prostate. Radiother Oncol 2006;79:335-40.

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8. Hynds S, McGarry CK, Mitchell DM, et al. Assessing the daily consistency of bladder filling using an ultrasonic Bladderscan device in men receiving radical conformal radiotherapy for prostate cancer. Br J Radiol 2011;84:813-8. 9. Orio PF 3rd, Merrick GS, Allen ZA, et al. cExternal beam radiation results in minimal changes in post void residual urine volumes during the treatment of clinically localized prostate cancer. Radiat Oncol 2009;4:26. 10. Nakamura N, Shikama N, Takahashi O, et al. Variability in bladder volumes of full bladders in definitive radiotherapy for cases of localized prostate cancer. Strahlenther Onkol 2010;186:637-42. 11. Kalz J, Sterzing F, Schubert K, Sroka-Perez G, Debus J, Herfarth K. Dosimetric comparison of image guidance by megavoltage computed tomography versus bone alignment for prostate cancer radiotherapy. Strahlenther Onkol 2009;185:241-7. 12. Fiorino C, Di Muzio N, Broggi S, et al. Evidence of limited motion of the prostate by carefully emptying the rectum as assessed by daily MVCT image guidance with helical tomotherapy. Int J Radiat Oncol Biol Phys 2008;71:611-7. 13. Yeung TP, Yartsev S, Rodrigues G, Bauman G. Evaluation of image-guidance strategies with helical tomotherapy for localised prostate cancer. J Med Imaging Radiat Oncol 2011;55:220-8. 14. Kupelian PA, Langen KM, Zeidan OA, et al. Daily variations in delivered doses in patients treated with radiotherapy for localized prostate cancer. Int J Radiat Oncol Biol Phys 2006;66:876-82. 15. Fiorino C, Foppiano F, Franzone P, et al. Rectal and bladder motion during conformal radiotherapy after radical prostatectomy. Radiother Oncol 2005;74:187-95. 16. Lebesque JV, Bruce AM, Kroes AP, Touw A, Shouman RT, van Herk M. Variation in volumes, dose-volume histograms, and estimated normal tissue complication probabilities of rectum and bladder during conformal radiotherapy of T3 prostate cancer. Int J Radiat Oncol Biol Phys 1995;33:1109-19. 17. Verit A, Yeni E, Unal D, Kafali H, Ozturk A, Ozardali I. Idiopathic retroperitoneal fibrosis mimicking a pelvic tumor: a case of pericystitis plastica. Yonsei Med J 2003;44:548-50. 18. Pinkawa M, Asadpour B, Gagel B, Piroth MD, Holy R, Eble MJ. Prostate position variability and dose-volume histograms in radiotherapy for prostate cancer with full and empty bladder. Int J Radiat Oncol Biol Phys 2006;64:856-61.

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Intensity-modulated radiotherapy using two static port of TomoTherapy for breast cancer after conservative surgery: dosimetric comparison with other treatment methods and 3-years clinical results

Journal of Radiation Research, 2017, pp. 1–8 doi: 10.1093/jrr/rrw132 Regular Paper

Intensity-modulated radiotherapy using two static ports of tomotherapy for breast cancer after conservative surgery: dosimetric comparison with other treatment methods and 3-year clinical results Aiko Nagai1,2,*, Yuta Shibamoto2, Masanori Yoshida1, Koji Inoda3 and Yuzo Kikuchi1 1

Radiation Therapy Center, Fukui Saiseikai Hospital, 7-1, Funabashi, Wadanaka-cho, Fukui 918-8503, Japan Department of Radiology, Nagoya City University Graduate School of Medical Sciences, 1 Kawasumi, Mizuho-cho, Mizuho-ku, Nagoya 467-8601, Japan 3 Department of Radiological Technology, Fukui Saiseikai Hospital, 7-1, Funabashi, Wadanaka-cho, Fukui 918-8503, Japan *Corresponding author: Department of Radiology, Nagoya City University Graduate School of Medical Sciences, 1 Kawasumi, Mizuho-cho, Mizuho-ku, Nagoya 467-8601, Japan. Tel: +81-52-853-8276; Fax: +81-52-852-5244; E-mail: love_child317@hotmail.com Received July 5, 2016; Revised October 23, 2016; Editorial Decision December 18, 2016

ABSTRACT This study investigated the differences in dose–volume parameters for the breast and normal tissues during TomoDirectTM (TD) intensity-modulated radiation therapy (IMRT), TD-3D conformal radiotherapy (3DCRT) and 3DCRT plans, all using two beams, and analyzed treatment outcomes of two-beam TD-IMRT for breast cancer after breast-conserving surgery. Between August 2011 and January 2015, 152 patients were treated using two-beam TD-IMRT with 50 Gy/25 fractions. Among them, 20 patients with left-sided breast cancer were randomly chosen, and two-beam TD-IMRT, TD-3DCRT and 3DCRT plans were created for each patient. The homogeneity and conformity indices and various dose–volume parameters for the planning target volume and OARs were evaluated. Clinical outcomes were evaluated at 3 years. Toxicities were evaluated using the Common Terminology Criteria for Adverse Events version 4.0. TD-IMRT and TD-3DCRT showed better whole-breast coverage than 3DCRT (P < 0.001). Most of the mean values of dosimetric endpoints for OARs were better in TD-IMRT than in TD-3DCRT and 3DCRT. Overall survival rates were 97.7% and local control rates were 99.1% at 3 years. Regional control and distant metastasis control rates at 3 years were 98.6% and 96.8%, respectively. Twenty-four of the 152 patients had Grade 2 or higher acute radiation dermatitis. Four patients (4/146 = 2.7%) had Grade 2 radiation pneumonitis. There were no late adverse events of Grade 2 or higher. Two-beam TD-IMRT appeared to yield better dose distribution for whole-breast external-beam radiation therapy than TD-3DCRT and two-beam 3DCRT. The treatment appeared to provide low skin toxicity and acceptable tumor control. KEYWORDS:

breast cancer, intensity-modulated radiation therapy, tomotherapy, Tomo-Direct, static

tomotherapy

IN TR ODU CT IO N Adjuvant whole-breast external-beam radiation therapy (WBRT) is an essential part of the current standard approach for early-stage breast cancer, because it yields excellent long-term local control and survival [1]. However, conventional 3D-conformal radiotherapy (3DCRT) for breast cancer occasionally causes treatment-related

complications (e.g. dermatitis, pneumonitis, cardiac injuries). The severity of both acute and late dermatitis is associated with increased breast dose inhomogeneity and resultant hot spots [2]. With conventional breast radiotherapy, a portion of the breast tissue receives 110% of the prescription dose, occasionally up to 120% [2]. Intensity-modulated radiation therapy (IMRT) has been shown

© The Author 2017. Published by Oxford University Press on behalf of The Japan Radiation Research Society and Japanese Society for Radiation Oncology. This is an Open Access article distributed under the terms of the Creative Commons Attribution Non-Commercial License (http://creativecommons.org/licenses/ by-nc/4.0/), which permits non-commercial re-use, distribution, and reproduction in any medium, provided the original work is properly cited. For commercial reuse, please contact journals.permissions@oup.com

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2 • A. Nagai et al. to improve breast dose homogeneity by decreasing hot spots and doses to normal tissues (e.g. the lung and heart) [3]. Breast IMRT is a developing area of active research, and several publications have shown feasibility, dosimetric superiority over 3DCRT [4], decreased acute side effects compared with conventional WBRT [5], and the potential for fewer late complications [6]. In particular, two Phase III studies have shown a reduction in skin toxicity by using IMRT [7, 8]. However, the use of IMRT for breast cancer has not yet become popular in Japan. Tomotherapy (TomoTherapy, Accuray, Madison, WI, USA) delivers IMRT with a high target-dose homogeneity, minimized doses to surrounding organs at risk [9], and a precise set-up using the onboard megavoltage (MV) computed tomography (CT) system enabling on-line image-guided radiotherapy (IGRT) [10]. TomoDirectTM (TD) is a fixed beam treatment method, allowing planning and delivery of static beams past binary multileaf collimators (MLCs) for fluence modulation [11, 12]. Recently, some clinical data on the use of helical tomotherapy (HT) and TD-IMRT in breast cancer have been reported [13–15]. TD-IMRT plans can decrease the dose for the contralateral lung and breast compared with HT plans. However, the previous reports only paid attention to dermatitis. In addition, there have been no reports that have compared the dosimetric parameters between two-beam TD-IMRT, two-beam TD-3DCRT and two-beam 3DCRT. In Japan, breast cancer patients are usually treated with two opposed tangential fields. Since our institution has no conventional linear accelerator (linac), we have used tomotherapy for all patients. Therefore, in this study, we investigated the differences in dose–volume parameters for the breast and normal tissues during TomoDirectTM (TD) intensity-modulated radiation therapy (IMRT), TD-3D conformal radiotherapy (3DCRT) and 3DCRT plans, all using two beams, and analyzed treatment outcomes of two-beam TD-IMRT for breast cancer after breast-conserving surgery.

M A T E R I A L S A ND M ET H O D S

Patient characteristics

Between August 2011 and January 2015, a total of 152 patients were treated at Fukui Saiseikai Hospital using TD-IMRT. All patients who underwent TD-IMRT were conventionally treated (2 Gy/day, 5 fractions/week) with two tangential ﬁelds using 6-MV photon beams to a total dose of 50 Gy/25 fractions. Our center had two tomotherapy machines but no linac. Written informed consent was obtained before treatment from all patients. Patient and tumor characteristics are shown in Table 1. Patient age ranged from 31 to 79 years (median, 52 years). All patients had a performance status score of 0. Concurrent chemotherapy was not used. We randomly chose 20 patients with left-sided breast cancer from the 152 patients for planning comparison of TD-IMRT, TD-3DCRT and 3DCRT. The Fukui Saiseikai Hospital Review Board approved this study (No. 2016-003).

CT simulation, planning target volume and organ at risk deﬁnition and contouring Our methods of tomotherapy have previously been described in detail [16]. All patients were immobilized in a supine position with a

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customized Blue BAG Cushion (Medical Intelligence, Schwabmuenchen, Germany) for simulation and treatment. Planning CT images were acquired with the ActivionTM 16 (Toshiba Medical Systems Corporation, Tochigi, Japan) and obtained from the midneck to the bottom of the lung with a 3-mm slice thickness under shallow breathing. All target volumes and normal structures were contoured on the Pinnacle3 workstation version 9.2 (Philips Medical Systems, Madison, WI, USA). The target for breast irradiation was determined by referring to preoperative sagittal CT and positron emission tomography (PET)-CT images. The planning target volume (PTV) for WBRT covered the superior border at the base of the manubriosternal joint and the inferior border at 1 cm below the inframammary line; the medial border was usually the midline of the sternum, and the lateral border was the midaxillary line, excluding the outermost 2 mm from the superﬁcial skin surface. Delineated organs at risk (OARs) were the ipsilateral, contralateral and bilateral lungs, heart, contralateral breasts, and skin. The skin was deﬁned as the volume with a depth of 2 mm from the external surface, and was automatically outlined.

Treatment plan comparison between TD-IMRT, TD-3DCRT and 3DCRT TD-IMRT and TD-3DCRT plans for 20 patients with left-sided breast cancer were created and optimized with the TomoTherapy version 5.0.5.18 treatment planning station (Accuray, Inc, Madison, WI, USA) using a convolution/superposition dose calculation algorithm. The planning parameters used for both plans were as follows: a field width of 2.51 cm, a pitch of 0.251, a modulation factor of 1.15–1.85, and a fine calculation grid (1.96 mm × 1.96 mm × slice thickness) for both optimization and calculation. The same beam angles were selected for both plans in order to minimize doses to the OARs. To account for possible breath-related target movements, 2 MLC leaves were opened on the anterior edge of each beam. The TD-3DCRT plans were made selecting the normal tissue homogeneity option and setting the tissue compensation to low, in order to allow for a more significant comparison with TD-IMRT plans. Details of the inverse planning algorithm used, the optimization method, and several parameters associated with the optimization in the tomotherapy planning station have been described previously [17]. A prescription dose of 50 Gy in 25 fractions to 50% of the PTV was chosen. The 3DCRT plans for 20 patients with left-sided breast cancer were created with the Pinnacle3 workstation using two open tangential 6-MV photon beams from a Varian Clinac 2100 C/D (Varian Medical System, Palo Alto, CA). Beam angles were chosen such that the edges matched those of the corresponding TD treatment beams. Adequate wedges were selected from 15, 30 and 45 degrees for the breast tissues. Final dose calculation employed a beam modeling based on the collapsed cone convolution/superposition. A prescription dose of 50 Gy in 25 fractions to the isocenter of the PTV was chosen.

Verification of treatment planning system calculations We compared the dose profiles calculated using each planning system with the dose profiles for beam modeling and actually measured doses in order to validate the accuracy of the treatment planning

TomoDirect for breast cancer

•

Table 1. Patient characteristics Characteristic

Number of patients (%)

Total number of patients

152

Age (years), median [range]

52 [31–79]

Follow-up (months), median [range]

33 [1–53]

Laterality

Right/Left

76 (50)/76 (50)

Clinical stage

0/I/II/III

37 (24.4)/83 (54.6)/28 (18.4)/4 (2.6)

Histology Ductal/Lobular/Mucinous/Scirrhous

147 (96.7)/2 (1.3)/2 (1.3)/1 (0.7)

Estrogen receptor

Positive/Negative

32 (21.1)/120 (78.9)

Progesterone receptor

Positive/Negative

107 (70.4)/45 (29.6)

HER2

Positive/Negative

61 (40.1)/91 (59.9)

Ki-67

≥20%/<20%/Unknown

101 (66.4)/45 (29.6)/6 (4.0)

Neoadjuvant chemotherapy

Yes/No

52 (34.2)/100 (65.8)

Concurrent chemotherapy

Yes/No

0 (0)/152 (100)

Adjuvant chemotherapy

Yes/No

5 (3.3)/147 (96.7)

Neoadjuvant hormonotherapy

Yes/No

72 (47.4)/80 (52.6)

Concurrent hormonotherapy

Yes/No

84 (55.3)/68 (44.7)

Adjuvant hormonotherapy

Yes/No

92 (60.5)/60 (39.5)

Neoadjuvant molecularly targeted therapy

Yes/No

22 (14.5)/130 (85.5)

Concurrent molecularly targeted therapy

Yes/No

23 (15.1)/129 (84.9)

Adjuvant molecularly targeted therapy

Yes/No

24 (15.8)/128 (84.2)

HER2 = human epidermal growth factor receptor type 2.

systems. The dosimetric quality indices for beam profiles differ considerably between the Varian linac on Pinnacle3 and TomoTherapy, since the latter has no flattening filter. For beam model verification of the Varian machine with a flattening filter, W50 (radiological width on a 50% dose level) and P80–20 (penumbra, defined as the distance between 80 and 20% dose levels) were used. On the other hand, full width at quarter maximum (FWQM) was used to check consistency between the beam model and the beam measurement for tomotherapy.

Planning evaluation Dosimetric comparisons of the treatment plans were performed based on the following parameters extracted from dose–volume histograms (DVHs): homogeneity index (HI); conformity index (CI); maximum dose for the PTV (Dmax); dose received by 95% of the PTV (D95%); dose received by 2% of PTV (D2%); V5 Gy, V10 Gy, V20 Gy and mean lung dose (MLD) for the bilateral, ipsilateral and contralateral lungs; V10 Gy, V25 Gy, V30 Gy, V35 Gy and mean heart dose (MHD) for the heart; mean dose for the

contralateral breast; and maximum dose for the skin. Furthermore, we divided the patients into a large PTV (above-median) group and a small PTV (below-median) group (n = 10 for each). The median PTV for all patients was 575.1 cm3. The median PTV was 685.7 cm3 (range: 586.1–1055.5) in the large PTV group and 456.2 cm3 (361.8–564.1) in the small PTV group (P = 0.002 by unpaired ttest). Maximum dose for the skin in the large and small PTV groups was compared between TD-IMRT, TD-3DCRT and 3DCRT. The HI was deﬁned as the ratio of the maximum dose in the PTV (Dmax) and the prescription dose in the PTV (Drx): HI = Dmax/ Drx. The CI, as proposed by ICRU 62 [18], was deﬁned as the ratio of the treated volume within the prescription isodose surface (VTV) to the PTV (VPTV): CI = VTV/VPTV.

Evaluation of clinical outcome In principle, physical examination and a blood test were performed at every follow-up visit, and CT, chest radiography, mammography and/or ultrasonography was performed whenever necessary until death. PET-CT and magnetic resonance imaging

145

4 • A. Nagai et al. were performed when history, physical examination, CT scan, and/or tumor marker assessment yielded suspicious ﬁndings. Toxicity was assessed according to the Common Terminology Criteria for Adverse Events version 4.0. Acute dermatitis and overall survival (OS) were evaluated for all 152 patients, and late dermatitis, pneumonitis, local control (LC) and regional control (RC) were evaluated for 146 patients with at least 6 months of follow-up. Cardiac injuries were evaluated for 74 patients with left-sided breast cancer followed for at least 12 months, and distant metastasis control (DMC) rates were evaluated for 126 patients who had been evaluated with follow-up CT, PET-CT and/or abdominal ultrasonography.

Statistical analysis Comparisons of dose–volume parameters of the PTV and OARs among the three plans for 20 patients were carried out using the factorial analysis of variance (ANOVA), followed by the Tukey– Kramer post hoc test. OS, LC, RC and DMC rates were calculated using the Kaplan–Meier method from the start of IMRT. A twosided P-value of ≤0.05 was considered to reﬂect statistical signiﬁcance. These univariate analyses were carried out using Prism (Graph Pad Institute Inc., San Diego, CA, USA).

TD-IMRT and TD-3DCRT. The PTV homogeneity of TD-IMRT and TD-3DCRT plans was better than that of the 3DCRT plan (P < 0.0001). Most of the mean values of OAR dosimetric endpoints were significantly better in TD-IMRT than in TD-3DCRT and 3DCRT. TD-IMRT provided lower values of ipsilateral lung V5 Gy and V10 Gy, bilateral lung V5 Gy and V10 Gy, and contralateral MLD than 3DCRT (P = <0.0001, 0.0091, <0.0001, 0.017 and 0.037, respectively). MHD and heart V10 Gy, V25 Gy, V30 Gy and V35Gy for TD-IMRT were significantly lower than those of TD-3DCRT (P = 0.0012, 0.0029, 0.0004, 0.0002 and 0.0003, respectively). Mean dose for the contralateral breast tissue was lower in TD-IMRT than in TD-3DCRT (P = 0.0018). Maximum dose for the skin was lower in 3DCRT than in TD-IMRT and TD3DCRT (P = 0.0055). In the small PTV group, the maximum dose for the skin was smaller in 3DCRT (mean ± SD: 48.4 ± 1.5 Gy) than in TD-IMRT (50.2 ± 0.5 Gy) and TD-3DCRT (50.2 ± 0.6 Gy; P = 0.0007). On the other hand, there were no significant differences in the large PTV group between the three plans (50.5 ± 0.3 Gy for TD-IMRT, 50.7 ± 0.4 Gy for TD-3DCRT, and 50.0 ± 2.1 Gy for 3DCRT; P = 0.53).

RESULTS

Verification of treatment planning system calculations W50, P80–20 and FWQM values are shown in Table 2. The difference in W50 between measured values and values calculated from the treatment planning systems in Pinnacle3 was 1.4 mm, which satisfied the <2 mm criteria [19]. In the same way, the difference in P80–20 was 0.5 mm, which satisfied the 3 mm criteria of distance to agreement [20]. For tomotherapy, the gamma-index of 2%/1 mm was 0.271, which satisfied the <1 criteria [21].

Treatment plan analysis for 20 patients with left-sided breast cancer PTV and OAR isodose distributions for a typical left-sided breast plan are illustrated in Fig. 1. The mean values ( ± SD) of the PTV and OAR dosimetric parameters of TD-IMRT, TD-3DCRT and 3DCRT plans are listed in Table 3. TD-IMRT and TD3DCRT showed better whole-breast coverage than 3DCRT; D95% was more than 95% in all TD-IMRT and TD-3DCRT plans (P < 0.0001). PTV Dmax and D2% were signiﬁcantly lower for the TD-IMRT and TD-3DCRT plans than 3DCRT (both P < 0.0001), and no signiﬁcant difference was observed between

Fig. 1. Isodose distribution for a left-sided breast cancer planned with TomoDirect (TD) intensity-modulated radiation therapy (IMRT) (A), TD-3D conformal radiotherapy (3DCRT) (B) and 3DCRT (C). The pink line in (A) to (C) indicates the planning target volume.

Table 2. Veriﬁcation of treatment planning system calculations for Pinnacle3 and TomoTherapy

W50 (mm) P80–20 (mm) FWQM (mm)

Measured value

Calculated value on Pinnacle3

Calculated value on TomoTherapy workstation

101.8

100.4

–

6.6

6.1

–

410.7

–

411.2

W50 = radiological width on a 50% dose level, P80–20 = penumbra deﬁned as distance between 80 and 20% dose levels, FWQM = full width at quarter maximum.

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TomoDirect for breast cancer

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Table 3. Dose parameter comparison among TD-IMRT, TD-3DCRT and 3DCRT plans for 20 left-sided breast cancer patients Parameters

TD-IMRT

TD-3DCRT

3DCRT

P-value

Dmax (%)

106 ± 1.0

105 ± 1.0

113 ± 4.3

<0.0001

D95 (%)

95.4 ± 0.3

96.0 ± 0.6

89.5 ± 2.5

<0.0001

D2 (%)

103 ± 0.7

102 ± 0.5

109 ± 2.4

<0.0001

1.8 ± 0.4

1.3 ± 0.1

4.3 ± 1.5

<0.0001

0.5 ± 0.0

0.6 ± 0.1

<0.0001

V5 Gy (%)

5.8 ± 1.3

6.6 ± 1.4

9.3 ± 2.7

<0.0001

V10 Gy (%)

4.4 ± 1.1

5.2 ± 1.2

6.0 ± 2.4

0.017

V20 Gy (%)

3.3 ± 0.9

4.0 ± 1.0

4.0 ± 2.1

0.17

MLD (Gy)

2.1 ± 0.7

2.3 ± 0.5

2.5 ± 1.0

0.22

Right lung

MLD (Gy)

0.2 ± 0.0

0.3 ± 0.1

0.037

Left lung

V5 Gy (%)

12.8 ± 3.2

14.8 ± 2.8

20.9 ± 6.1

<0.0001

V10 Gy (%)

9.7 ± 2.6

11.6 ± 2.4

13.5 ± 5.3

0.0091

V20 Gy (%)

7.2 ± 2.2

9.1 ± 2.1

9.1 ± 4.6

0.11

MLD (Gy)

4.1 ± 0.9

4.9 ± 1.0

5.0 ± 2.0

0.11

V10 Gy (%)

4.1 ± 2.4

7.9 ± 3.8

5.7 ± 3.4

0.0029

V25 Gy (%)

2.0 ± 1.5

5.3 ± 3.1

3.0 ± 2.5

0.0004

V30 Gy (%)

1.6 ± 1.3

4.7 ± 2.8

2.5 ± 2.2

0.0002

V35 Gy (%)

1.2 ± 1.1

4.0 ± 2.6

2.1 ± 2.0

0.0003

MHD (Gy)

2.2 ± 0.9

3.8 ± 1.6

3.5 ± 1.4

0.0012

Dmax (Gy)

46.7 ± 4.7

48.5 ± 1.2

47.1 ± 2.8

Right breast tissue

Dmean (Gy)

0.4 ± 0.1

0.5 ± 0.2

0.0018

Skin

Dmax (Gy)

50.4 ± 0.5

50.5 ± 0.5

49.3 ± 2.0

0.0055

PTV

Bilateral lung

Heart

0.18

3DCRT = 3D-conformal radiotherapy, IMRT = intensity-modulated radiation therapy, TD = TomoDirect, PTV = planning target volume, HI = homogenity index, CI = conformity index, MLD = mean lung dose, MHD = mean heart dose. P-values from the factorial analysis of variance (ANOVA) followed by the Tukey–Kramer post hoc test. Data presented as mean ± standard deviation.

Clinical outcome The median follow-up was 38 months for all patients (range, 1–58 months). The OS, LC, RC and DMC rates at 3 years were 97.7%, 99.1%, 98.6% and 96.8%, respectively. OS rates for Stage 0, I, II and III patients at 3 years were 100%, 100%, 91.4% and 100%, respectively (Fig. 2). LC rates were 100%, 98.4%, 100% and 100% at 3 years for Stage 0, I, II and III, respectively (Fig. 3). RC rates at 3 years were 100%, 98.7%, 100% and 100%, for Stage 0, I, II and III, respectively (data not shown). DMC rates at 3 years were 100%, 97.3%, 95.8% and 75% for Stage 0, I, II and III, respectively (data not shown). Twenty-four of the 152 (15.8%) patients had ≥Grade 2 acute radiation dermatitis. Grade 3 acute radiation dermatitis was seen in

4 of the 152 (2.6%) patients. Most patients (84.2%) had Grade 1 acute dermatitis. There was no late radiation dermatitis of Grade 2 or higher. Two of the 146 patients had Grade 2 radiation pneumonitis (1.4%). There were no acute or late adverse cardiac events of Grade 2 or higher.

DISCUSSION In this study, dose homogeneity of PTVs in TD-IMRT and TD3DCRT plans were better than in 3DCRT plans (both P < 0.001), and most of the mean values of the OAR dose parameters were better in TD-IMRT than in TD-3DCRT and 3DCRT. The maximum dose for the skin in 20 patients was lower in 3DCRT than in TDIMRT and TD-3DCRT, but there were no signiﬁcant differences in

147

6 • A. Nagai et al.

Fig. 2. Curves for overall survival (OS) according to clinical stages for all 152 patients.

Fig. 3. Curves for local control (LC) according to clinical stages for 146 patients. the large PTV group between the three plans. It has been reported that a larger breast size is associated with more severe dermatitis [22, 23], so the results of our study would indicate that the use of TD-IMRT might not increase the incidence of severe dermatitis. In a 3DCRT study using a 50-Gy dose, Grade 2 or higher acute dermatitis was seen in 22% [24]; that study used both 4 and 6 MV X rays, so it is not appropriate to compare the results with those obtained in our study that used 6 MV X rays only. Nevertheless, the incidence of Grade 2 or higher dermatitis of 15.8% in our study may be an acceptable level. Regarding late toxicity, palpable breast induration and negative changes in telangiectasia were reported to be reduced with breast IMRT compared with 3DCRT [25], while there was no late dermatitis in this study. TD-IMRT could also decrease bilateral V5 Gy and V10 Gy, ipsilateral V5 Gy and V10 Gy of the lung, and contralateral MLD, while bilateral MLD and V20 Gy could not be reduced. In the clinical study, the frequency of Grade 2 or higher pneumonitis (1.38%) was nearly equal to or possibly slightly higher than that in 3DCRT studies (0.9–1.28%) [19, 26]. The lung toxicity of TD-IMRT should be further investigated in future studies. Concerning doses for the heart, TD-IMRT was superior to TD-3DCRT regarding V10 Gy, V25 Gy, V30 Gy and V35 Gy. There was no pericarditis in this study, but a previous

148

study showed that pericarditis occurred in 3 of 831 patients (0.4%) [27]. A clinical study on IMRT showed a low rate of local relapse with mild acute/late effects [28]. Short follow-up is a limitation of our study, but the clinical outcomes obtained so far are comparable with those of the previous studies. From the above considerations, it seems that TD-IMRT provides more appropriate dose distribution for WBRT than the other two plans. Moreover, TD-IMRT has two other advantages for breast irradiation. First, TD-IMRT is an image-guided IMRT delivery using a fixed gantry; in that respect it is thus suitable for clinical use [9]. Daily MVCT assures set-up accuracy, and it can detect changes in the skin surface and occurrence of pneumonitis during treatment, so we can make a more accurate re-plan and cope with acute adverse events immediately. As a second advantage, compared with 3DCRT in our study TD-IMRT provided adequate target coverage of the whole breast, with a reduction of the high doses to the target and of the low doses to the contralateral tissues. The low-dose effect to the contralateral tissues is known to lead to an increased rate of radiationinduced secondary malignancies; women <40 years of age who received a radiation dose of >1.0 Gy to the contralateral breast had an elevated, long-term risk of developing a second primary contralateral breast cancer [29]. In this study, the dose to the contralateral breast was lower in TD-IMRT than in 3DCRT, but the Dmean was <1.0 Gy in both treatments, so the influence on the incidence of secondary breast cancer may be small. Regarding the dose of the MVCT, the mean dose delivered to the contralateral breast was ~26.8 cGy in 25 fractions in a previous study [30], so the influence of the MVCT dose on the contralateral breast appears to be small. However, it should be noted that daily MVCT increases MLD and MHD. On the other hand, breast TD-IMRT has three issues that need to be improved. One is the high cost of breast IMRT, so breast IMRT is not necessarily recommended for all patients [31]. In Japan, however, the cost of two-beam IMRT is equal to that of twobeam 3DCRT, so patients there receiving two-beam therapy could benefit from IMRT in terms of clinical outcome at no additional cost. Second, the current version of tomotherapy cannot use respiration gating or deliver treatment under breath holding. It is expected that this issue will be solved in the future version of tomotherapy. Third, breast hypofractionated radiotherapy over a shorter number of treatment days (15–16 fractions) is reported to have an advantage, with equivalent or even improved outcomes and acute/late toxicities compared with conventionally fractionated radiotherapy [17, 32, 33]. However, breast hypofractionated IMRT is not as frequently employed in Japan as it is in the rest of the world. By using TD-IMRT, the daily doses to OARs could be reduced, so the adverse effects caused by using a higher dose per fraction may be alleviated. Hypofractionated IMRT using TD may be a promising topic of future investigation.

CONCLUSION The two-beam TD-IMRT plan appeared to yield better dose distribution for WBRT than TD-3DCRT or two-beam 3DCRT. Our preliminary results for TD-IMRT suggest that the skin and other

TomoDirect for breast cancer toxicities and tumor control are acceptable, and further studies are warranted.

A C KN O W L ED G EM E NT S The authors are grateful to Dr Yoshio Kasahara, Dr Kojiro Horita, Dr Masayo Kimura, Dr Yoshiko Sudo, Yuichi Nushimo, Shinji Himeji, Naoki Nakajima, Tadashi Nakabayashi and Fuyumi Kobayashi for their valuable help in this research.

CONFLICT OF INTEREST The authors declare that there are no conﬂicts of interest.

R EF E RE N CE S 1. Clarke M, Collins R, Darby S, et al. Early Breast Cancer Trialists Collaborative Group. Effects of radiotherapy and of differences in the extent of surgery for early breast cancer on local recurrence and 15-year survival: an overview of the randomized trials. Lancet 2005;366:2087–106. 2. Buchholz TA, Gurgoze E, Brice WS, et al. Dosimetric analysis of intact breast irradiation in off-axis planes. Int J Radiat Oncol Biol Phys 1997;39:261–7. 3. Kestin LL, Sharpe MB, Frazier RC, et al. Intensity modulation to improve dose uniformity with tangential breast radiotherapy: initial clinical experience. Int J Radiat Oncol Biol Phys 2000;48: 1559–68. 4. Hong L, Hunt M, Chui C, et al. Intensity-modulated tangential beam irradiation of the intact breast. Int J Radiat Oncol Biol Phys 1999;44:1155–64. 5. Harsolia A, Kestin L, Grills I, et al. Intensity-modulated radiotherapy results in significant decrease in clinical toxicities compared with conventional wedge-based breast radiotherapy. Int J Radiat Oncol Biol Phys 2007;68:1375–80. 6. McDonald MW, Godette KD, Butker EK, et al. Long-term outcomes of IMRT for breast cancer: a single-institution cohort analysis. Int J Radiat Oncol Biol Phys 2008;72:1031–40. 7. Pignol JP, Olivotto I, Rakovitch E, et al. A multicenter randomized trial of breast intensity-modulated radiation therapy to reduce acute radiation dermatitis. J Clin Oncol 2008;26:2085–92. 8. Mukesh MB, Barnett GC, Wilkinson JS, et al. Randomized controlled trial of intensity-modulated radiotherapy for early breast cancer: 5-year results confirm superior overall cosmesis. J Clin Oncol 2013;31:4488–95. 9. Coon AB, Dickler A, Kirk MC, et al. TomoTherapy and multifield intensity-modulated radiotherapy planning reduce cardiac doses in left-sided breast cancer patients with unfavorable cardiac anatomy. Int J Radiat Oncol Biol Phys 2010;78:104–10. 10. Beavis AW. Is Tomotherapy the future of IMRT? Br J Radiol 2004;77:285–95. 11. Franco P, Catuzzo P, Cante D, et al. TomoDirect: an efficient means to deliver radiation at static angles with tomotherapy. Tumori 2011;97:498–502. 12. Murai T, Shibamoto Y, Manabe Y, et al. Intensity-modulated radiation therapy using static ports of tomotherapy (TomoDirect): comparison with the TomoHelical mode. Radiat Oncol 2013; 8:68.

•

13. Cendales R, Schiappacasse L, Schnitman F, et al. Helical tomotherapy in patients with breast cancer and complex treatment volumes. Clin Transl Oncol 2011;13:268–74. 14. Franco P, Zeverino M, Migliaccio F, et al. Intensity-modulated adjuvant whole breast radiation delivered with static angle tomotherapy (TomoDirect): a prospective case series. J Cancer Res Clin Oncol 2013;139:1927–36. 15. Zhang F, Wang Y, Xu W, et al. Dosimetric evaluation of different intensity-modulated radiotherapy techniques for breast cancer after conservative surgery. Technol Cancer Res Treat 2015; 14:515–23. 16. Nagai A, Shibamoto Y, Yoshida M, et al. Safety and efficacy of intensity-modulated stereotactic body radiotherapy using helical tomotherapy for lung cancer and lung metastasis. Biomed Res Int 2014;2014:473173. 17. Sugie C, Manabe Y, Hayashi A, et al. Efficacy of the dynamic jaw mode in helical tomotherapy with static ports for breast cancer. Technol Cancer Res Treat 2015;14:459–65. 18. International Commission on Radiation Units and Measurements. Prescribing, recording, and reporting photon beam therapy (Supplement to ICRU Report 50). ICRU Report 62. ICRU, Bethesda, MD, 1999. 19. Mijnheer B, Olszewska A, Fiorino C, et al. Accuracy requirements and tolerance levels. ESTRO Booklet No. 7: Quality Assurance of Treatment Planning Systems. Practical Examples for Non-IMRT Photon Beams. Brussels: ESTRO, 2004, 11–20. 20. Smilowitz JB, Das IJ, Feygelman V, et al. AAPM Medical Physics Practice Guideline 5.a. Commissioning and QA of treatment planning dose calculations—megavoltage photon and electron beams. J Appl Clin Med Phys 2015;16:5768. 21. TomoTherapy Service Instructions. Installation Dosimetric Verification Guide (T-PSC-HB0004). Accuray, Inc. 2013. Internal document. (22 September 2016, date last accessed). 22. De Langhe S, Mulliez T, Veldeman L, et al. Factors modifying the risk for developing acute skin toxicity after whole-breast intensity modulated radiotherapy. BMC Cancer 2014;14:711. 23. Fernando IN, Ford HT, Powles TJ, et al. Factors affecting acute skin toxicity in patients having breast irradiation after conservative surgery: a prospective study of treatment practice at the Royal Marsden Hospital. Clin Oncol (R Coll Radiol) 1996;8: 226–33. 24. Osako T, Oguchi M, Kumada M, et al. Acute radiation dermatitis and pneumonitis in Japanese breast cancer patients with whole breast hypofractionated radiotherapy compared to conventional radiotherapy. Jpn J Clin Oncol 2008;38:334–8. 25. Barnett GC, Wilkinson JS, Moody A, et al. Randomized controlled trial of forward-planned intensity modulated radiotherapy for early breast cancer: interim results at 2 years. Int J Radiat Oncol Biol Phys 2012;82:715–23. 26. Nozaki M, Kagami Y, Mitsumori M, et al. A multicenter investigation of late adverse events in Japanese women treated with breast-conserving surgery plus conventional fractionated wholebreast radiation therapy. Jpn J Clin Oncol 2012;42:522–7. 27. Pierce SM, Recht A, Lingos TI, et al. Long-term radiation complications following conservative surgery (CS) and radiation

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8 • A. Nagai et al. therapy (RT) in patients with early stage breast cancer. Int J Radiat Oncol Biol Phys 1992;23:915–23. 28. Keller LM, Sopka DM, Li T, et al. Five-year results of whole breast intensity modulated radiation therapy for the treatment of early stage breast cancer: the Fox Chase Cancer Center Experience. Int J Radiat Oncol Biol Phys 2012;84:881–7. 29. Stovall M, Smith SA, Langholz BM, et al. Dose to the contralateral breast from radiotherapy and risk of second primary breast cancer in the WECARE study. Int J Radiat Oncol Biol Phys 2008;72:1021–30. 30. Shah AP, Langen KM, Ruchala KJ, et al. Patient dose from megavoltage computed tomography imaging. Int J Radiat Oncol Biol Phys 2008;70:1579–87.

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31. Medscape. ASTRO: 5 Radiation Oncology Practices Should Stop. www.medscape.com/viewarticle/811528 (23 September 2013, date last accessed). 32. Haviland JS, Owen JR, Dewar JA et al. The UK Standardisation of Breast Radiotherapy (START) trials of radiotherapy hypofractionation for treatment of early breast cancer: 10-year follow-up results of two randomised controlled trials. Lancet Oncol 2013;14:1086–94. 33. Chan EK, Woods R, McBride ML, et al. Adjuvant hypofractionated versus conventional whole breast radiation therapy for early-stage breast cancer: long-term hospital-related morbidity from cardiac causes. Int J Radiat Oncol Biol Phys 2014;15;88: 786–92.

Patient dose from kilovoltage radiographs durin motion-synchronized treatments on Radixact

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Technical Note: Patient dose from kilovoltage radiographs during motionsynchronized treatments on Radixact® William S. Ferrisa)

and Wesley S. Culberson

Department of Medical Physics, School of Medicine and Public Health, University of Wisconsin-Madison, Madison, WI 53705, USA

(Received 9 June 2020; revised 27 August 2020; accepted for publication 27 August 2020; published 14 October 2020) Purpose: Synchrony is a motion management system available on the Radixact linear accelerator that utilizes kilovoltage (kV) radiographs to track target motion and synchronize the delivery of radiation with the motion. Proper management of this imaging dose requires accurate quantification. The purpose of this work was to use Monte Carlo (MC) simulations to quantify organ-specific patient doses from these images for various patient anatomies. Methods: Point doses in water were measured per TG-61 for three beam qualities commonly used on the Radixact. The point doses were used to benchmark a model of the imaging system built using the Monte Carlo N-Particle (MCNP) transport code. Patient computed tomography (CT) datasets were obtained for 5 patients and 100 planar images were simulated for each patient. Patient dose was calculated using energy deposition mesh tallies. Results: The MCNP model was able to accurately reproduce the measured point doses, with a median dose difference of less than 1%. The median dose (D50%) to soft tissue from 100 radiographs among the 5 patient cases ranged from 2.0 to 4.6 mGy. The max dose (D1%) to soft tissue ranged from 6.2 to 31.0 mGy and the max dose to bony structures ranged from 20.2 to 71.7 mGy. These doses can be scaled to estimate total patient dose throughout many fractions. Conclusions: Patient dose is largely dependent on imaging protocol, patient size, and treatment parameters such as fractionation and gantry period. Organ doses from 100 radiographs (an approximate number for one fraction) on the Radixact are slightly less than the doses from Tomo MVCT setup images. Careful selection of clinical protocols and planning parameters can be used to minimize risk from these images. © 2020 The Authors. Medical Physics published by Wiley Periodicals LLC on behalf of American Association of Physicists in Medicine. [https://doi.org/10.1002/mp.14461] Key words: intrafraction imaging dose, Radixact, tomotherapy 1. INTRODUCTION Active intrafraction motion management during radiotherapy often relies on kilovoltage (kV) imaging, magnetic resonance imaging (MRI), or radiofrequency tracking to determine the location of the target in real time.1 Kilovoltage image tracking techniques deposit dose to the patient in addition to the dose from the therapy itself. The American Association of Physicists in Medicine (AAPM) Task Group 180 (TG-180) reported on management of imaging doses in radiation therapy, and recommends that imaging dose be considered in the treatment planning process if the dose will likely exceed 5% of the therapeutic dose.2 Appropriate management of this imaging dose requires accurate quantification. The Radixact linear accelerator (Accuray, Inc., Sunnyvale, CA) contains an optional motion management system called Synchrony®, which uses kV imaging during treatment to monitor the location of the target and synchronize the delivery of radiation with the motion of the target. A description of target tracking and motion of the jaws and multileaf collimator (MLC) during treatment has been provided in the works of Schnarr et al. and Chen et al.3,4 Radiographs are acquired at two to six imaging angles every gantry rotation and are chosen by the operator. Synchrony can be used to manage both respiratory and nonrespiratory, or quasi-static 5772

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motion,3 both of which require the use of kV radiographs during treatment. Due to the recent release of Radixact Synchrony, there is limited literature on doses from kV radiographs acquired during these treatments. Accuray provides skin exposures at isocenter, which must be corrected for varying patient size and position and do not reflect dose at depth. Chen et al. measured the weighted computed tomography dose index (CTDIw) for 100 radiographs of the large thorax protocol on Radixact to be 8.4 mGy.4 This value provides a magnitude of expected doses to water, but it does not consider patient anatomy, imaging protocol, or dose to materials other than water such as bone. The purpose of this work is to use measurements and simulations to quantify volumetric, organ-specific patient doses for various disease sites that may commonly be treated using Radixact Synchrony. 2. MATERIALS AND METHODS A photograph of the kV imaging system mounted on the Radixact is shown in Fig. 1. The kV tube is manufactured by Siemens (Siemens AG, Munich, Germany) and is capable of tube potentials between 40 and 150 kVp. The kV tube is mounted 90° from the megavoltage (MV) source and is positioned such that the anode/cathode axis is parallel to the

0094-2405/2020/47(11)/5772/7

© 2020 The Authors. Medical Physics published by Wiley Periodicals LLC on behalf of American Association of Physicists in Medicine. This is an open access article under the terms of the Creative Commons Attribution-NonCommercial-NoDerivs License, which permits use and distribution in any medium, provided the original work is properly cited, the use is non-commercial and no modiﬁcations oradaptations are made.

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TABLE I. Default preset imaging protocols available for Synchrony treatments on Radixact.

FIG. 1. Photograph of a Radixact at UW-Madison with the cover removed, showing the kV tube and flat panel kV detector. The MV source-to-axis distance (SAD) is 85 cm, the kV SAD is 57.5 cm, and the kV source to imager distance is 113.5 cm. The MV source is hidden in the picture by the couch. [Color figure can be viewed at wileyonlinelibrary.com]

direction of table travel. The beam is statically collimated to irradiate just inside the detector’s usable pixels, which projects to approximately 20 × 20 cm2 at isocenter. The beam qualities investigated in this work were 100, 120, and 140 kVp, which are the beam qualities used in the preset imaging protocols that come default on the Radixact, shown in Table I. The imaging protocol is the same for every angle used in the Synchrony treatment, that is, images at different angles cannot be set to different parameters. 2.A. Beam data measurements The recommendations of the AAPM TG-61 were followed for measurement of kV point doses in water.5 TG-61 specifies beam quality in terms of half-value layer (HVL), which were measured for each beam quality in millimeters of aluminum and millimeters of copper using an A12 ionization chamber (Standard Imaging, Middleton, WI). The filters were 99.9% pure and the thicknesses were specified to the nearest 0.001 mm. Narrow-beam geometry was obtained for the HVL measurements by addition of a lead diaphragm. Point doses at depth in a water tank were determined using the TG-61 in-water method, described by Eq. (1).5 The ion chamber was moved to each position at depth or off-axis with the water tank software and three measurements were acquired at each position. During each measurement, the couch and gantry were static, the kV imager was at zero degrees (pointing toward the floor), and the MV beam was off. The measured charge was fully corrected per TG-61 including a shutter correction. Air-kerma calibration coefficients were obtained for the A12 chamber from the University of Wisconsin Accredited Dosimetry Calibration Laboratory (ADCL) for medium-filtered beam qualities. The HVLs of the calibrated beam qualities bracketed the HVLs of the three Radixact beam qualities of interest and logarithmic

Imaging protocol

mAs

kVp

XS thorax/pelvis

100

S thorax

0.8

120

S pelvis/ M thorax

120

M pelvis

1.25

120

L thorax

1.6

120

L pelvis XL thorax/pelvis

2 4

120 140

interpolation was used to obtain the air-kerma calibration for each beam quality. The overall correction factor, PQ,chamb , and the ratio of mean mass energy-absorption coefficient for water-to-air were obtained from the tables in TG-61 for the A12 chamber using the measured HVL of each beam. Field size correction factors were not used as these corrections are less than 1% for field sizes larger than the reference field size.5 Point doses were acquired for one source-to-surface distance (SSD) for an inline profile, a crossline profile, and a depth-dose profile. w μen (1) Dw ¼ M � N k � PQ,chamb � ρ air water 2.B. Monte carlo modeling The Monte Carlo N-Particle (MCNP) transport code version 6.2 was used for all simulations in this work.6 The simulation geometry is shown in Fig. 2. A point source of photons was used for the starting particles for all simulations, which was set at depth in the anode to approximate the heel effect. The spectrum for each beam quality was obtained using the MATLAB code Spektr.7 Beam hardening due to the inherent filtration, the mirror, and the monitor chamber were accounted for in the spectra of the starting particles using Spektr. Energy deposition tallies were used for all tallies in this work. The tally results were converted to a dose in mGy/mAs using the following equation, 0 mGy D mGy MeV ¼ X MC � Meas mAs , (2) DMC MeV mAs g � s:p: X 0 MC g�s:p: where D0Meas is the measured dose at the reference point in mGy/mAs, X 0MC is the simulated tally value at the reference point in MeV/g per source particle, and X MC is the simulated tally value in the conditions of interest. Doses to water at the measurement points were calculated for the purpose of benchmarking the MCNP model. 2.C. Patient dose calculations Five patient computed tomography (CT) datasets were acquired to be used for this imaging dose study. The disease

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FIG. 2. Geometry of the MCNP simulations showing the kV tube shell (a), the tungsten anode (b), the 1 mm aluminum and 0.5 mm copper filters (c), the static tungsten collimator (d), and the 1.6 mm polycarbonate bore material (e). The anode–cathode axis is parallel to the direction of table travel. [Color figure can be viewed at wileyonlinelibrary.com]

sites included in this work were lung (x2) and pancreas, which are likely candidates for respiratory Synchrony, and endothelium and prostate, which are likely candidates for nonrespiratory Synchrony motion management. All doses are provided for a single fraction and a standard number of radiographs per fraction (100). The imaging protocol for each patient was chosen based on patient size and disease site. The planning target volume (PTV) ranged from 2 to 146 cc among the five patients. Four or five imaging angles per gantry rotation were simulated in this work. Soft tissue was defined as all tissue excluding bone. The skin was defined as a 5 mm rind around the body. The CT datasets were aligned such that the target was centrally located in the bore (within the geometric restrictions of the bore). Couch travel was modeled by simulating the source at multiple superior/inferior locations for each gantry angle. The extent of superior/inferior point source locations was equal to the couch travel distance during treatment. The voxel size was 2.5 × 2.5 mm2 or smaller in the axial plane and 3 mm or smaller in the superior/inferior direction. The carbon fiber couch of the Radixact was included in the simulations. Each voxel in the original CT image was assigned a physical density using a measured HU-to-density calibration phantom8 and a material such as air, lung, adipose, muscle, cartilage, and bone based on the physical density. Equation (2) was used to convert the tally values into dose for each voxel. The dose calculation grid overlapped the CT grid.

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uncertainty (k = 1) of the measured reference doses were estimated to be 4% based on the uncertainty of the measurements (<0.5%) and the 3.6% uncertainty reported in TG-61 for in-water point doses at the reference depth.5 The standard uncertainty of nonreference-condition point doses (such as off-axis or depths not at 2 cm) was estimated to be 5%. The A12 ion chamber was observed to have a small energy dependence in the range of interest, as the air-kerma coefficients varied <0.2% between tube potentials of 100 and 140 kVp. Figure 3 shows a comparison of the measured and simulated point doses for each energy. The median and maximum global dose difference between the measured and simulated data were 0.6% and 6.0%, respectively. Organ dose statistics are shown for each patient in Table III and example CT datasets and dose distributions for two of the patient cases are shown in Fig. 4. Doses are for 100 total images to approximate the number of images that may be delivered in one fraction. Simulation uncertainty in the MCNP 3D mesh dose was summarized for each patient case using the value umed,10%, the median simulation uncertainty of voxels above 10% of the maximum dose. This value was 10% or less for all cases. The mesh doses are scaled by the reference dose measurements, whose uncertainty was estimated to be 4%. Therefore, the total uncertainty of voxel dose calculation in the patient geometries is estimated to have a median value of less than 11%, which is much less than the acceptable uncertainty of 20% stated in the TG-180 report.2 4. DISCUSSION The MCNP model reproduced the measured point-dose data within a median difference of 0.8%. The asymmetric profile in the inline direction from the heel effect is reproduced (Fig. 3) by simulating the point source at depth in the anode, which allows for modeling changes in output and spectrum as a function of superior/inferior position. The accuracy of the model in reproducing the measured data was far better than the accuracy tolerance of �20% stated in TG180 for imaging dose calculations during radiotherapy.2 The calculated doses to water in this work approximately agree with the work of Chen et al., who reported that the CTDIw for 100 radiographs of the large thorax protocol (120 kVp, 1.6 mAs) was 8.4 mGy.4 The point dose at isocenter for the large lung case using the large thorax imaging protocol in this work was 6.8 mGy. However, this work indicates TABLE II. Parameters used for calculation of TG-61 point-doses in-water for three beam qualities commonly used on the Radixact.

Tube potential (kVp)

Measured HVL (mm Cu, mm Al)

N k (Gy/C)

100

0.50, 9.07

4.412E7

120

0.63, 10.17

4.408E7

3. RESULTS

140

0.77, 11.01

4.406E7

The parameters used to determine point doses in water using the TG-61 protocol are shown in Table II. The standard

The conditions for the measured reference dose (D0Meas ) were open field (20 × 20 cm2 at iso), 55 cm source-to-point distance (SPD), and 2 cm depth.

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D0Meas (mGy/mAs) 0.120 � 0.005

0.216 � 0.009

0.336 � 0.013

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FIG. 3. Measured (A12) and simulated (MCNP) point-dose data in water for open-field radiographs (20 × 20 cm2). Error bars indicate standard error (k = 1). The standard error of all simulated points was less than 0.5%. The heel effect can be observed in the inline direction via the asymmetric profile. The gray lines indicate the location of the reference point, at 2 cm depth and 55 cm from the source along the central axis. [Color figure can be viewed at wileyonlinelibrary.com]

that doses to soft tissue may be much higher than ~7–8 mGy, such as a max dose (D1%) of 31.0 mGy for the endothelium patient imaged with the XL pelvis protocol. In addition, maximum doses to bony structures ranged from 20.2 to 71.7 mGy. The data in this work suggest that patient dose is highly dependent on imaging protocol. The reference point dose was proportional to kVp3.1 when fit with the data in Table II. Dose at this point increases by a factor of 1.76 from 100 to 120 kVp and by a factor of 2.84 from 100 to 140 kVp. Patient dose also scales linearly with mAs, therefore patient dose can increase by a factor of 5 among the mAs protocol considered in this work. The values reported in this work can be scaled using the observed trends (Dose / kVp3:1 � mAs) to approximate doses when the clinical imaging protocol differs from the protocol used in this work. Imaging protocol in this work was chosen based on the patient size and disease site alone. The imaging angles were

chosen to be approximately evenly spaced for this study. During a patient treatment, imaging protocol and angles can be chosen to optimize image quality and ensure visibility of the target. If angles are chosen such that they are unevenly spaced, this will result in a change in the hot and cold spots at the overlap of the beams. However, the user is prevented from choosing angles that are too close together and doses near the isocenter will likely not be largely changed since all imaging angles are centered on isocenter. The effect of varying imaging angles on patient dose was outside the scope of this work. Patient anatomy and geometric setup also has a large effect on patient dose. The maximum dose (D1%) to soft tissue ranged from 6.2 to 31.0 mGy among the five cases, which is a difference of a factor of 5. Even when scaled for kVp output using the fitted power law and to equal mAs, the maximum dose to soft tissue still varied by more than a factor of 2

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TABLE III. Simulated patient dose in mGy from 100 radiographs.

Patient Large lung L thorax

Small lung XS Thorax

Prostate M Pelvis

Endothelium XL Pelvis

Pancreas L Pelvis

umed,10%T (%)

Diso

6.8

4.1

6.8

Volume

Dave

D50%

Heart

6.8

6.9

8.5

10.1

Lungs

7.4

7.3

11.4

15.1

Ribs

12.7

8.9

33.4

47.7

Skin

3.8

1.5

11.4

16.3

Soft tissue

4.6

3.5

10.1

15.0

Spinal cord

6.6

6.4

10.0

32.2

10.9

6.9

D1%

Heart

3.2

4.4

5.3

Lungs

3.2

3.1

4.8

6.2

Ribs

6.4

4.7

15.0

20.2

Skin

1.7

1.1

4.2

6.6

Soft tissue

2.2

2.0

4.4

6.2

Spinal cord

1.8

1.6

3.3

6.0

Bladder

7.2

6.9

9.2

10.7

11.9

12.6

19.1

26.0

Prostate

5.4

6.1

6.8

Rectum

6.0

6.1

7.3

8.2

Skin

2.9

1.8

6.9

10.2

3.1 11.4

2.6 11.4

6.6 13.5

9.7 15.3 46.5

Pubic bone

D10%

Soft tissue Bladder Femurs

11.1

6.8

29.9

Pubic bone

29.8

25.4

52.0

71.7

Rectum

12.8

12.6

16.5

20.5 35.9

Skin

6.1

1.8

21.6

Soft tissue

7.3

4.6

18.4

31.0

Liver

8.3

10.6

13.3

4.4 10.4

3.7 10.5

8.4 12.2

11.9 13.6

Lungs Pancreas Skin

3.9

1.5

11.7

18.2

Soft tissue

4.5

3.0

10.6

15.5

Spinal cord

5.9

9.7

16.7

Doses may be scaled to approximate dose from multiple fractions or varying number of total images. The imaging protocol used in the simulation is indicated in italics. The median simulation uncertainty of voxels above 10% of the maximum dose is denoted umed,10%T.

among the five cases. The scaled maximum dose to soft tissue was lowest for the largest patients, since the individual fields are attenuated before overlapping. This can be observed in Fig. IV which displays dose distributions for a large and a small patient. The attenuation of the couch used in this study was explored by simulating dose to a homogenous water phantom from a posterior to anterior beam with and without the couch. The average dose to a 10 × 10 × 0.5 cm3 volume on the surface of the water closest to the couch decreased by 5% and the dose to a point at 2 cm depth from the couch decreased by 8% when the couch was added. Therefore, skin entrance dose is expected to decrease by ~5% when imaging through the couch.

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In addition to patient anatomy and imaging protocol, total patient dose will be highly dependent on treatment parameters. The number of images throughout a patient’s treatment is a function of total treatment time and the number of active gantry rotations, since images are acquired every gantry rotation. Highly modulated treatments are more likely to have a tight pitch, leading to more gantry rotations per treatment and thus more total images. Treatments with a large number of fractions will likely have more total images since images must be acquired prior to starting the treatment to build the model of the target motion. In addition, the number of images per fraction might increase substantially if the treatment is paused regularly due to inaccurate target motion modeling, as new images must be acquired to resume the treatment each time the treatment is paused with the MV beam off. Table IV compares the range of imaging doses in this work to imaging doses from other image-guidance procedures used in radiotherapy from the TG-180 report.2 These data suggest that dose from 100 radiographs on the Radixact is expected to be slightly less than that from typical kVCBCT scans or a Tomo MVCT setup scan. Cumulative dose from kV images throughout many Synchrony fractions can be estimated by scaling the per fraction values provided in this work by the total number of images acquired throughout treatment. In an initial study with 13 Synchrony treatment plans with various fractionation schemes, the number of images per fraction ranged from 50 to 206, and the total number of images over all fractions ranged from 310 to 1920, with an average of 810 images.9 When scaled to 2000 total images, the largest dose to any structure in Table III would be 1.4 Gy (D1% to the pubic bone for the endothelium patient). This value is slightly less than 5% of a typical therapeutic dose of 30, or 1.5 Gy. Therefore, it is expected that most cases will not exceed 5% of the therapeutic dose from these images alone, as 2000 images is an upper estimate and most therapeutic doses are greater than 30 Gy. However, these images will be combined with other routine imaging techniques and care should be used to reduce imaging dose from these procedures as choice of treatment parameters has a large effect on total number of images.

5. CONCLUSIONS Monte Carlo simulations were used to calculate volumetric patient dose from 100 images on the Radixact with tube potentials between 100 and 140 kVp. Patient median doses to soft tissue and bony structures ranged from 2.0 to 4.6 mGy and 4.7 to 25.4 mGy, respectively. These doses are lower than that from other imaging procedures such as kV-CBCT or Tomo MVCT scans. Total patient dose will depend on imaging protocol, fractionation, and parameters such as number of gantry rotations, therefore careful planning can reduce imaging doses. The values in this work can be used by healthcare professionals to quantify patient imaging dose for typical treatment sites and manage risk from these procedures.

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FIG. 4. Example computed tomography (CT) axial slices through isocenter and dose distributions in mGy resulting from 100 radiographs on the Radixact for two patient cases. Four imaging angles were used for the cases in this example. The target was placed at the geometric isocenter. The red line on the CT slice displays the AP location of the coronal dose distribution in this figure. Organ-specific dose statistics are provided for each patient case in Table III. [Color figure can be viewed at wileyonlinelibrary.com] TABLE IV. Comparison of imaging doses from 100 planar radiographs on the Radixact to doses from other imaging procedures.2 Procedure

Description

Dose range (mGy)

Soft tissue organs; median dose Soft tissue organs; median dose

1.6–12.6a 9.0–20.0

Varian pelvis kV-CBCT

Soft tissue organs; median dose

11.9–19.9

Tomo MVCT setup scan

Isocenter of 30 cm water phantom

8.0–25.0c

Radixact 100 radiographs Elekta pelvis kV-CBCT b

Analysis is limited to soft tissue organs and excludes the skin and the “soft tissue” contour. a Range from five patient cases in this work. b M cassette, no bow-tie filter, 120 kVp, 1 mAs/acquisition, 650 acquisitions. c Range corresponds to the range of available pitches (coarse, normal, fine).

ACKNOWLEDGMENTS The authors thank the students and staff of the UWMRRC for their continued support, the UWRCL and UWADCL customers whose calibrations help support ongoing student research at the UWMRRC. CONFLICT OF INTEREST The authors have no conflict of interest to disclose. a)

Author to whom correspondence should be addressed. Electronic mail: williamferris0@gmail.com; Telephone: (402) 889-3894.

REFERENCES 1. Keall PJ, Mageras GS, Balter JM, Emery RS, Forster KM, Jiang SB. The management of respiratory motion in radiation oncology report of AAPM Task Group 76. Med Phys. 2006;33:3874–3900. 2. Ding GX, Alaei P, Curran B, et al. Image guidance doses delivered during radiotherapy: quantification, management, and reduction: report of the AAPM therapy physics committee task group 180. Med Phys. 2018;45: e84–e99. 3. Schnarr E, Beneke M, Casey D, et al. Feasibility of real-time motion management with helical tomotherapy. Med Phys. 2018;45:1329–1337. 4. Chen GP, Tai A, Keiper TD, Lim S, Li XA. Technical note: comprehensive performance tests of the first clinical real-time motion tracking and compensation system using MLC and jaws. Med Phys. 2020;47:2814–2825. 5. Ma CM, Coffey CW, DeWerd LA, et al. AAPM protocol for 40–300 kV x-ray beam dosimetry in radiotherapy and radiobiology. Med Phys. 2001;28:868–893.

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6. Werner CJ. MCNP6.2 Release Notes. Los Alamos National Laboratory report LA-UR-18-20808; 2018. 7. Siewerdsen JH, Waese AM, Moseley DJ, Richard S, Jaffray DA. Spektr: a computational tool for x-ray spectral analysis and imaging system optimization. Med Phys. 2004;31:3057–3067. 8. Constantinou C, Harrington JC, DeWerd LA. An electron density calibration phantom for CT-based treatment planning computers. Med Phys. 1992;19:325–327.

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9. Ferris WS, Kissick MW, Bayouth JE, Culberson WS, Smilowitz JB. Evaluation of radixact motion synchrony for 3D respiratory motion: modeling accuracy and dosimetric fidelity. J Appl Clin Med Phys. 2020;21:96–106. https://doi.org/10.1002/acm2.12978.

Clinical Imprementation and Initial Experience of Real-Time Motion Tracking With Jaws and Practical Radiation Oncology® (2021) xx, e1-e10

Multileaf Collimator During Helical Tomotherapy Delivery www.practicalradonc.org

Clinical Investigation

Clinical Implementation and Initial Experience of Real-Time Motion Tracking With Jaws and Multileaf Collimator During Helical Tomotherapy Delivery Guang-Pei Chen, PhD,* An Tai, PhD, Lindsay Puckett, MD, Elizabeth Gore, MD, Sara Lim, PhD, Timothy Keiper, PhD, Candice Johnstone, MD, Monica Shukla, MD, Colleen Lawton, MD and X. Allen Li, PhD Department of Radiation Oncology, Medical College of Wisconsin, Milwaukee, Wisconsin Received 21 October 2020; revised 28 January 2021; accepted 29 January 2021

Abstract Purpose: This work reports the clinical implementation of a real-time motion tracking and correction system using dynamic multileaf collimator and jaws during helical tomotherapy delivery (Synchrony on Radixact; Accuray, Inc). Methods and Materials: The first clinical Synchrony on Radixact system was recently installed and tested at our institution. Various clinical workflows, including fiducial implantation, computed tomography simulation, treatment planning, delivery quality assurance, treatment simulation, and delivery, for both fiducial-free and fiducial-based motion tracking methods were developed. Treatment planning and delivery data from initial patients, including dosimetric benefits, real-time target detection, model building, motion tracking accuracy, delivery smoothness, and extra dose from real-time radiographic imaging, were analyzed. Results: The Synchrony on Radixact system was tested to be within its performance specifications and has been used to treat 10 lung (fiducial-free) and 5 prostate (fiducial-based) patients with cancer so far in our clinic. The success of these treatments, especially for fiducial-free tracking, depends on multiple factors, including careful selection of the patient, appropriate setting of system parameters, appropriate positioning of the patient and skin markers, and use of treatment simulation. For the lung tumor cases, difficulties in model building, due primarily to the changes of target detectability or respiration patterns, were observed, which led to important system upgrades, including the addition of a treatment delivery simulation capability. Motion tracking metrics for all treated patients were within specifications, for example, (1) delivery quality assurance passing rates >95%; (2) extra dose from radiograph <0.5% of the prescription dose; and (3) average Potential Diff, measured D, and Rigid Body were within 6.5, 2.9, and 3.9 mm, respectively. Conclusions: Practical workflows for the use of the first clinical motion tracking and correction system in helical tomotherapy delivery have been developed, and the system has now been successfully implemented in our clinic for treating patients with lung and prostate cancer. 2021 The Authors. Published by Elsevier Inc. on behalf of American Society for Radiation Oncology. This is an open access article under the CC BY license (http://creativecommons.org/licenses/by/4.0/).

Sources of support: This work had no speciﬁc funding. Disclosures: The authors’ institution received grants from Accuray, Inc, during the conduct of the study. L.P. received travel support from Accuray, Inc. X.A.L. received grants from Elekta AB, grants from Manteia Med, and grants from Siemens outside the submitted work. Research data are stored in an institutional repository and will be shared upon request to the corresponding author. * Corresponding author: Guang-Pei Chen, PhD; E-mail: gpchen@mcw.edu https://doi.org/10.1016/j.prro.2021.01.010 1879-8500/ 2021 The Authors. Published by Elsevier Inc. on behalf of American Society for Radiation Oncology. This is an open access article under the CC BY license (http://creativecommons.org/licenses/by/4.0/).

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Introduction Intrafraction organ motion can be significant during radiation therapy (RT) for tumors in thorax, abdomen, and pelvis, and is a major issue affecting RT delivery accuracy.1-4 Tumor motion management, including clinical approaches as simple as planning target volume (PTV) expansion, motion compression, or breath hold to more sophisticated techniques such as gating and tracking, has been investigated for decades.5-8 In 2019, a real time motion tracking and compensation technique using dynamic multileaf collimator (MLC) and jaws (Synchrony on Radixact; Accuray, Inc) was introduced for tomotherapy delivery.9 The first commercially available Synchrony on Radixact system was installed in our institution recently.10 The system can be used for both respiratory (with and without fiducials) and nonrespiratory (with fiducials) motion tracking. The fiducial-free tracking is attractive in lung tumor treatment, for example, stereotactic body RT, for possible PTV margin reduction.11 It also avoids the costs and risks associated with surgically inserted fiducial markers. Neither fiducial-free nor fiducial-based tracking, which have been previously used in RT, have been demonstrated with helical delivery.12 We have previously reported our comprehensive commissioning tests for this helical-based system.10 In this work, we report our clinical implementation of this technology focusing on our learning curve, practical workflows, and patient selection criteria. Our initial experience gained in using the system for treating patients with lung and prostate cancer is also included.

Methods and Materials Compliance with ethical standards All procedures performed in studies involving human participants were in accordance with the ethical standards of the institutional and/or national research committee and with the 1964 Helsinki Declaration and its later amendments or comparable ethical standards. Informed consent was obtained from all individual participants included in the study.

Technical description of the Synchrony system Technical details of the Synchrony on Radixact system have been reported elsewhere.10,13,14 A brief description of the system is provided. The hardware of the system consists of a kV x-ray source and a detector panel mounted with a 90 offset from the MV beam and a camera mounted on the ceiling to capture motion of a set of light-emitting diodes (LEDs) placed on the patient’s skin and treatment couch. By tracking the LEDs on the

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patient while simultaneously acquiring 2-dimensional (2D) kV x-ray radiographic images that detect tumor location, a model is built that correlates the external surface motion with respiratory tumor motion. For nonrespiratory tracking, a position model is built using radiographic images only. During the irradiation, the tumor motion is predicted based on the updated model at each newly acquired radiographic image and is compensated by dynamic MLC shifting and jaw sweeping. The success of model building is critical and is manipulated by adjusting radiographic image protocols (kVp and mAs) and angles, LED placement, ﬁducial selection if applicable, and thresholds of various system parameters.15 Such parameters include model quality, represented by a statistical prediction of the 3D distance error when the model is used (Potential Diff), predicted and measured target position difference on a plane at target centroid and parallel to the radiographic image (Measured D), maximum ﬁducial pair distance difference between detection and planning (Rigid Body), and predicted target motion in 3D (Target Offset). The radiation delivery can be paused manually or automatically when a parameter exceeds its threshold within a certain amount of time (Autopause Delay) or the target moves outside hardware tracking range (Target Outside of Jaw Range). During clinical implementation, the Synchrony system hardware and software were upgraded multiple times to add functionalities and to improve performance based on the feedback from our initial experience. Adaptive modeling off (allowing treatment to progress using the last good model) and treatment delivery simulation (allowing operators to carry out the entire Synchrony tracking without turning on the MV treatment beams) are among these additional functionalities.

Overview of clinical implementation The first clinical Synchrony on Radixact system was installed in our clinic in June 2019. Extensive commissioning and quality assurance (QA) tests were performed to ensure geometric and dosimetric accuracy of the motion tracking before implementing the technology in the clinic.10 To implement the technology in the clinic, we first performed a series of end-to-end tests of the entire Synchrony motion tracking process using a motion phantom with realistic motion signals. A workflow as shown in Figure 1 was designed based on the tests. A step-by-step checklist for each tracking mode was developed for the clinical team, including radiation oncologists, physicists, dosimetrists, and radiation therapists, to follow. As an example, Table 1 shows the checklist for the fiducial-free respiratory motion tracking treatment. To successfully use the Synchrony system, particularly for fiducial-free tracking, suitable patients need to be

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Figure 1

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Workﬂow for Synchrony tumor tracking treatment process.

selected carefully in consideration of (1) the size of the kV panel (20 20 cm2 projected at the isocenter) on which the target needs to be visible for the whole

treatment; (2) the jaw swing range ( 20.0 and 12.5 mm for the 10 and 25 mm jaw widths, respectively); and (3) model building reliability, which depends on multiple

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Table 1

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Checklist for the nonﬁducial RSM treatment

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kV included? Load/set up patient as usual (free breathing) Light-emitting diodes (LED) placement

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As usual kV protocol and mAs Potential Diff (mm) Measured D (mm) Target offset (mm) If more than 1 fiducial, rigid body (mm) Target outside jaw range threshold (% of time) Tracking range (mm) Auto pause delay (sec) Sensitivity Adaptive modeling Used fiducial identifiers Angles () used Assess images and parameters Adjustment when treatment cannot be started

Stability (1-3 on patient, 4 on couch) Visibility ( 2 of 1-3; and 4) Thorax (L) 120 kVp 1.6 mAs 10 5 20.0 1.5 10 40 60 Low On 0, 55, 120, 188, 240, 308

Select/deselect/change angle Turn off certain images Change thresholds Select/deselect/drag ﬁducials Select/deselect LEDs If cannot go through, troubleshooting, consult with phy/MC for stopping Synchrony treatment Assess images and parameters Adjustment when model building fails Adjust LED positions Select/deselect/change angle Turn off certain images Change thresholds Reset model If cannot go through, troubleshooting, consult with physicist/physician for stopping Synchrony treatment Adaptive modeling On If system pauses automatically Acquire images and/or build model again Pause if it is needed to Select/deselect/change angle Select/deselect LEDs Select/deselect/drag ﬁducials Change thresholds Stop if it is needed to Reposition LEDS Acquire another CTrue image If the next patient is not RSM tx, unplug and clean the LEDs Unload patient as usual QA PreciseArt Document Billing

Abbreviations: IGRT Z image guided radiation therapy; QA Z quality assurance; RSM Z respiratory motion tracking. Applicable lists for each patient depend on tracking mode being used; nonapplicable items are grayed out. Items in green boxes are speciﬁc to an individual patient/fraction that need to be determined before treatment.

factors, for example, visibility of the tracking target and regularity of the breathing pattern. Based on the phantom tests, we included the following considerations in the patient selection criteria: (1) target location (eg, lung tumor not attached to mediastinum and chest wall) and size (eg, within a sphere of 8 cm diameter or smaller, but a diameter >~2 cm is recommended); (2) contrast of the

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target on x-ray images (eg, computed tomography [CT] number); (3) respiratory motion pattern (not extremely irregular, eg, hyperventilation, frequent respiratory rate, rapid change of amplitude, phase, and baseline, etc); (4) motion range (eg, 2 to 20 mm in longitudinal direction) and rigidity if multiple targets exist; (5) separation and motion rigidity with target if ﬁducials are used; and

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(5) patient health (both physical and mental for a patient to tolerate possible long on-table time) and possible metal implants that could obstruct target detection. Six weeks after the installation, we started using the system for patients with lung tumor with fiducial-free respiratory tracking mode and for patients with prostate cancer with fiducial- tracking mode. The workflow, checklists, and patient selection criteria were iteratively refined and updated based on the experience gained from the clinical use on the patients. Described are details in each key step in using the Synchrony system on patients.

non-Synchrony treatment as a backup in case the Synchrony plan could not be delivered. In the Synchrony plan for a patient with a lung tumor the gross tumor volume (GTV) was delineated on the midP images, whereas in the non-Synchrony, the GTV was delineated based on the exhale phase CT together with 4D positron emission tomography, when available, and the internal target volume was created to enclose the GTV motions in the 10 phases. The organs at risk were segmented from the midP images. The PTV was created from the GTV with a 5-mm expansion for the Synchrony plan, whereas the PTV for the non-Synchrony plan was the internal target volume plus 5-mm margin. For the prostate cancer cases with fiducial tracking, no special consideration was taken in PTV and organs at risk delineation due to the use of Synchrony. The Synchrony plan was generated using a Precision workstation (Accuray, Inc), similar to a regular tomotherapy plan, with a few exceptions: (1) the jaw width was selected based on the target motion range and delivery efficiency; (2) for fiducial tracking, the fiducials were identified as tracking targets; (3) for fiducial-free tracking, tracking target volume (TTV), for example, solid tumor, was contoured with the soft tissue window level preset; (4) 2 to 6 radiograph angles were selected based on the visibility of the tracking target on the digitally reconstructed radiographs; (5) the patient might have been positioned with a lateral offset if a laterally off-centered target was to be treated; (6) the pitches and modulation factors might have been chosen to compromise the plan quality, gantry rotation speed, and total treatment time; and (7) a simulation plan, similar to the Synchrony plan but without the MV (treatment) beam, was generated for the treatment delivery simulation described in the following sections.

Fiducial implantation For prostate cancer treatment, 4 fiducials of 0.8 � 3.0 mm cylindrical gold markers (2021-1-2; Best Medical International, Inc, Springfield, VA) were implanted in urology with the patient under short-duration local anesthesia. The fiducials were placed using ultrasound guidance, with each at the left and right of the base and apex of the prostate, respectively. Images were taken before, at regular intervals during, and following the procedure to check for fiducial positioning and the absence of immediate complications. An interval of 1 to 2 weeks was planned to allow the fiducials to stabilize before the RT planning CT was acquired. CT simulation and treatment planning A conventional CT was acquired for each patient with prostate cancer and a 4DCT was acquired for each patient with lung tumor using a CT simulator (Drive; Siemens). The 4DCT was acquired with the patient free breathing and the breathing pattern recorded using a pressure sensor under an abdominal belt (Anzai Medical Co, Ltd, Japan). The CT images were reconstructed with 2-mm slice thickness using an iterative metal artifact reduction algorithm (Siemens) for patients with fiducials or other implanted metal objects or using a filtered back projection algorithm otherwise. For a 4DCT set, 10 respiratory phase sets were generated based on amplitude-sorting or phasesorting if breathing signal was cut off due to large diaphragm motion. The images were processed and a timeaveraged middle position (midP) CT was created using the 10 sets of phase images in MIM software (v6.8.6; MIM Software Inc, Cleveland, OH).16 A middle phase image set can be used if lung tumor density in midP is low due to inaccurate deformable registration. The respirationinduced tumor motion was measured based on the maximum edge motion of the tumor at all phases along the longitudinal (SI), vertical (AP), and lateral directions. For patient-specific QA purpose, the continuous breathing signal was used to generate patient-specific motion trace with the measured mean breathing period and amplitude set based on the assessed tumor motion in each direction. For each case treated, both Synchrony and conventional (non-Synchrony) plans were created with the

Patient-specific delivery QA Each Synchrony plan was delivered to a 3D phantom (ArcCheck; Sun Nuclear, Melbourne, FL, or Delta4 Phantomþ; ScandiDos, Uppsala, Sweden) with the Synchrony on Radixact system. The phantom was placed on a motion platform (CIRS; Norfolk, VA, or Hexamotion; ScandiDos) driven by an irregular motion trace for a patient with prostate cancer or the patient-specific breathing trace recorded during the 4DCT scan with LEDs placed on the motion platform surrogate (CIRS) or directly on the phantom itself (Hexamotion) for a patient with a lung tumor. Tracking targets used were inserts with embedded high-density block (fiducial-free tracking) or fiducials (fiducial tracking). The delivered dose was measured in the phantom and was compared with that from calculation.10 Dose agreement was analyzed using gamma analysis with the criteria of 3%, 3 mm, and 5% threshold. In addition, each non-Synchrony plan was measured per our institutional standard.

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Treatment simulation and delivery In our implementation, we schedule the first session as a delivery simulation to evaluate reliability of the model building and smoothness of the entire delivery process. This allows us to verify that the patient could be successfully treated with Synchrony. With a successful simulation, the Synchrony treatment proceeds. Otherwise, the non-Synchrony plan will be carried out. On each day with Synchrony simulation or treatment, a daily QA procedure was performed to verify appropriateness and consistency of the motion tracking functionality and the geometry and dosimetry accuracy. At the simulation or each fraction of treatment, the checklist with predetermined patient-specific parameters was followed by the clinical team. The patient, under free breathing for the whole treatment, was set up as usual, except that the LEDs were placed on both the couch and on the patient for respiratory tracking. The patient was repositioned by aligning the motion-averaged target from the daily image to the target in the midP planning image with the standard megavoltage CT (MVCT)-based image guided RT process. The Synchrony procedure was carried out with these steps: (1) acquiring pretreatment x-ray radiographs at preselected angles from the plan to initiate target detection and motion model building based on the real-time radiographs and LED signals, (2) adjusting various tracking parameters if necessary (mostly in the simulation session) to account for a variety of patient specific issues (eg, unexpected motion change, difficulty in target detection, low model confidence, lack of enough good-quality radiographs), (3) initiating beam on while the jaws and MLCs were tracking the target motion, and (4) closely observing patient treatment and taking necessary action (pause treatment, take more images to re-establish model with MV beam off, resume treatment, etc) while the target was tracked, with motion model updated at each newly acquired radiograph image at preselected angles. Postdelivery evaluation To evaluate the correctness of the treatment delivery, we analyzed the treatment data stored in the system during the delivery after each treatment fraction using an inhouse software tool. These data included: (1) target detection confidence and rate of successful detection; (2) model- building confidence, percentage of beam-on radiograph images (model building difficulty would lead to more images acquired initially and additional images acquired after interruption, both with MV beam off), and frequency of treatment interruption; and (3) tracking goodness as measured by average Potential Diff, Measured D, Rigid Body effectively used in compensation, and target position difference between current and updated models. Identified possible correlation with the successful tracking was used to adjust relevant parameters for the remaining treatment.

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To evaluate dosimetry accuracy after each fraction, we reconstructed the dose delivered on the daily MVCT using PreciseArt (Accuray, Inc). The dose volume parameters were evaluated and compared with their planning goals. When the Synchrony plan was not completely delivered, the reconstructed dose was used as a bias dose to create a new plan for the remaining treatment.

Results We have treated 10 patients with lung tumor and 5 patients with prostate cancer using Synchrony on Radixact. There was a steep learning curve in this initial period. The system (hardware and/or software) was upgraded 2 times to improve its performance with additional functionalities during the period. Based on our clinical implementation and the initial clinical experience, we observed that the success of Synchrony treatments relied on (1) careful selection of suitable patients, (2) optimal patient and LED positioning, (3) appropriate setting of tracking parameters, and (4) use of treatment simulation. In fact, the simulation tool was used for 3 potential patients and 2 of these patients were determined not suitable for Synchrony treatment due to substantial variation of the breathing pattern or patient health condition.

Fiducial-free tracking All 10 patients with lung tumors were treated with stereotactic body RT with doses of 54 or 45 Gy in 3 fractions or 50 Gy in 5 fractions. The total tumor motion ranged from 4.6 to 31.1 mm (median 6.4 mm). The Synchrony plan beam on times were between 504.1 and 1020.9 seconds (median 599.8 seconds). Comparing to the corresponding non-Synchrony plans, the Synchrony plans led to reductions of PTV volume, lung V5, V20, and mean dose by 26.4% 13.3%, 10.5% 16.8%, 16.0% 8.7%, and 12.0% 7.4%, respectively. Figure 2 compares dose-volume histograms and dose distributions of Synchrony and non-Synchrony plans for a representative case. For the cases treated, the average plan delivery QA passing rate was 99.2% 1.0% with the minimum of 97.4%, all above the 95% passing criteria. Various x-ray radiograph protocols, for example, 120 kVp and 2.0 mAs, 120 kVp and 1.6 mAs, and 140 kVp and 3.2 mAs, were used depending on patient body size, target visibility, and model building smoothness. Number of image angles per rotation ranged from 3 to 6 (median 4), and the average time between images ranged from 5.3 to 13.9 seconds (median 7.5 s). As an example, the radiographic image is compared with the corresponding digitally reconstructed radiographs for 1 of the cases treated in Figure 3. For the 10 patients with lung cancer,

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Implementation of real-time tracking for Radixact

A 100 90 80

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Figure 2 Comparison of (A) dose volume histograms (DVHs) and (B) planning target volumes (PTVs) (thick lines) and dose distributions (thin lines with colorwash, at prescription dose) of the Synchrony and non-Synchrony plans for a representative lung case. Compared with non-Synchrony plan, the Synchrony plan led to a reduction of 19.6% (115 cc) and 27.2% (30 cc) of lung V5 and V20, respectively. In (B), the Synchrony and non-Synchrony PTV difference is demonstrated in a sagittal view. The patient had biggest tumor motion in longitudinal direction and vertical next. The isodose lines shown are from the Synchrony plan on the left and non-Synchrony plan on the right.

the threshold setting ranges for Potential Diff, Measured D, and Target Offset were 5 to 10, 4 to 6, and 15 to 40 mm, respectively, depending on target motion range. In the early stage of this clinical implementation with unupgraded system, treatment might be interrupted primarily due to the unsuccessful model building during the delivery. The frequency of such interruptions (pauses) depended on multiple factors including (1) change of target detection capability on radiographs due to the obstacle of patient anatomy and/or implanted metal objects with patient traveling during helical delivery, (2) substantial change of the breathing pattern and LED signals, (3) tight Synchrony parameters, and (4) patient overall health condition. For 3 patients treated before the

upgrade, some planned Synchrony treatment fractions were aborted because the large number of pauses resulted in the treatment being too long to be delivered within our scheduled treatment slot (60 min). When a Synchrony fraction delivery was aborted, the remaining fraction dose was delivered with or without Synchrony at another fraction. For a non-Synchrony completion delivery, PreciseART was able to be used to reconstruct the delivered dose that was used as the bias dose for the nonSynchrony plan. When there was no pause or a low number of pauses, the Synchrony deliveries were smooth, with delivery times comparable with those of non-Synchrony deliveries (as low as 22 min from door to door).

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Figure 3 A typical radiograph image (A) and digitally reconstructed radiographs (DRRs) (B) for a patient with lung cancer. The cyan X indicates the predicted target position, and the purple þ indicates the found target position. The target offset calculated for this radiograph was 6.9 mm. Average target motions for this patient were �1.8, �4.1, and �2.6 mm in lateral, longitudinal, and vertical, respectively. (A color version of this ﬁgure is available at https://doi.org/10.1016/j.prro.2021.01.010.)

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Figure 4 (A)Variation of successful target detection rate with tracking target volume (TTV). (B)Variation of model conﬁdence with TTV volume. (C) Variation of percentage of beam-on radiograph image (BORI) with TTV volume (primary vertical axis), and variation of average number of BORI per Gy dose (NBORI/Gy) with TTV volume (secondary vertical axis). (D) Variation of treatment interruption frequency with average light-emitting diodes (LED) amplitude. One of the 10 patients was not included due to unavailable raw data for analysis. Patients with successful target detection rate lower than 80% were not included in (D).

Successful target detection based on real-time radiograph depended on multiple factors, as shown in Figure 4. The successful target detection rate was found to be not deﬁnitely lower with a smaller TTV (Fig 4A). The model building conﬁdence and percentage of beam-on radiograph image showed the trend of being lower with a

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smaller TTV, as shown in Figure 4B and 4C, respectively. The average number of beam-on radiograph images per unit dose for each patient is also shown in Figure 4C. In general, number of beam-on radiograph images per unit dose is bigger with larger irradiated volume but the jaw width and pitch used also play a role, as indicated by the

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Figure 5 (A) Variation of average ﬁducial detection rates and total number of acquired images with treatment fraction for a patient with prostate cancer. (B) Variation of average Potential Diff, Rigid Body, Target Offset, and model conﬁdence with treatment fraction for the patient. Error bars are from the daily standard deviations.

outlier in the plot, for which the delivery had too many rotations due to a small jaw width (1 cm) combined with a small pitch (0.1) being used in the plan. It was also observed that the model building experienced a smaller number of interruptions with LED signal amplitude exceeding a certain threshold (eg, 5 mm) when patients with low successful target detection rate (eg, 80%) were excluded (Fig 4D). For this reason, we normally placed LEDs on stable locations on the abdomen or chest where relatively large motion was observed. For all patients with lung tumor treated, the patient’s average Potential Diff and Measured D ranged from 2.9 to 6.5 mm (median, 3.9 mm) and from 1.5 to 2.9 mm (median, 1.8 mm), respectively. The Potential Diff was found to be strongly correlated with the root means square (RMS) offset error (Potential Diff z 1.5 RMS offset error) based on phantom tests. The imaging dose from the real-time radiographs was low. For the cases treated, the maximum average number of radiograph images (including those with MV beam off) per unit Gy RT dose was 45.3/Gy (typically below 10/ Gy), which leads to an imaging dose of approximately 0.5% of the prescription dose.10,17

Fiducial tracking Plans with a prescription of either 70 Gy in 28 fractions (4 patients) or 75.6 Gy in 42 fractions (1 patient) were generated for both Synchrony and non-Synchrony (a backup) delivery for the prostate cancer cases with beam on time range of 149.5 to 372.0 seconds (median, 315.1 seconds). The Synchrony treatment deliveries were smooth. All 4 fiducials for each patient were identified in plan generation with CT numbers >5000. The minimum fiducial separation from all patients was 14.0 mm. The number of radiograph image angles picked was 4 to 6 (median, 6). The average time

between images ranged from 3.7 to 6.9 seconds (median, 4.2 seconds). The radiograph protocol with 120 kVp and 1.6 mAs was used. Thresholds of several key parameters were 6, 16, and 10 mm for Potential Diff, Target Offset, and Rigid Body, respectively. All 4 fiducials were detected confidently 94.0% of the time for the first patient and >99.5% of the time for other patients. There was a slight difficulty in detecting fiducial 4 for the first patient on some days because this fiducial was close to the rectum wall (Fig 5A). The average model confidence for each patient was 0.96 to 1.00 (median, 0.99). The overall percentage of beam-on radiograph image was 85.3% to 94.9% (median, 88.6%). The maximum number of radiograph images per unit dose among all patients was 38.9/Gy, which is equivalent to approximately 0.3% of the planned dose.10,17 The maximum values of patient overall average of Potential Diff, Rigid Body, and Target Offset were 1.4 3.3, 3.9 1.7, and 4.8 2.7 mm, respectively. The variations of their daily averages are shown in Figure 5B for the first patient. The intrafraction motion of the prostate varied between different fractions and moved up to 8 mm but was typically 2 to 5 mm within ~6 min primarily in SI and AP directions. This motion is consistent with those observed with ultrasound systems.3,18 The average difference between target positions predicted by the existing and updated models was small; for example, such values for a typical patient were 0.0 0.4, 0.0 0.4, and 0.0 0.6 mm in lateral, AP, and SI directions, respectively, indicating that the target tracking metrics were within specifications.

Discussion Intrafraction motion remains a key challenge in radiation therapy. With a steep learning curve, we have

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successfully implemented the Synchrony on Radixact system to manage intrafraction motion in our clinic. The capability of motion tracking and compensation with Synchrony on Radixact combined with high dose conformity with the helical delivery19 can lead to minimized PTV volume, improving normal tissue sparing. As shown in this work, successful use of the Synchrony on Radixact system requires special considerations, including careful selection of suitable patients (eg, general health condition, tumor size and location, motion pattern, feasibility for fiducial implantation) and effective use of the technology (eg, informative treatment simulation, appropriate tracking parameters, and robust workflow). The motion tracking accuracy and dose delivery accuracy were demonstrated adequately,10,14; however, it is still desirable to reconstruct the delivered dose based on actual information (eg, delivered sinogram, real-time motion incorporated images). The current dose reconstruction with PreciseART is based on planned sinogram on pretreatment MVCT, not accounting for actual delivered information such as intrafraction motion, variation in motion tracking, and so forth. Due to the nature of helical delivery, incomplete fractional Synchrony treatment should be avoided, as the subsequent delivery may not be able to fully account for the variations of motion and anatomy. As shown in this study, continuing technology advancements and user group clinical experience will flatten the learning curve and improve the applicability of the system for patient treatments.

Conclusions Performance of the first clinical motion tracking and correction system (Synchrony on Radixact) for helical tomotherapy delivery has been tested within specifications. Practical workflows, including patient selection technical criteria, treatment planning, patient specific QA, treatment simulation and delivery, and posttreatment evaluation, were developed. The system has now been successfully implemented in our clinic for treating selected patients with lung and prostate cancers. Despite the steep learning curve we experienced in the initial phases of clinical implementation, the dosimetry benefits of using the motion tracking and compensation are now achievable for our patients.

Acknowledgments We thank Kevin Sonnemann, CMD, for planning support; Sarah McDonald, RTT, for treatment support; and Rick Vaden, CMD, Nancy Schauer, CMD, Jeremy Heil, MS, and Andrea Cox, PhD for technical support.

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References 1. Abdul Ghani MN, Ng WL. Management of respiratory motion for lung radiotherapy: A review. J Xiangya Med. 2018;3:27. 2. Suramo I, Päivänsalo M, Myllylä V. Cranio-caudal movements of the liver, pancreas and kidneys in respiration. Acta Radiol Diagn (Stockh). 1984;25:129-131. 3. Sihono DSK, Ehmann M, Heitmann S, et al. Determination of intrafraction prostate motion during external beam radiation therapy with a transperineal 4-dimensional ultrasound real-time tracking system. Int J Radiat Oncol Biol Phys. 2018;101:136-143. 4. Keall PJ, Mageras GS, Balter JM, et al. The management of respiratory motion in radiation oncology report of AAPM Task Group 76. Med Phys. 2006;33:3874-3900. 5. Mah D, Hanley J, Rosenzweig KE, et al. Technical aspects of the deep inspiration breath hold technique in the treatment of thoracic cancer. Int J Radiat Oncol Biol Phys. 2000;48:1175-1185. 6. Wong JW, Sharpe MB, Jaffray DA, et al. The use of active breathing control (ABC) to reduce margin for breathing motion. Int J Radiat Oncol Biol Phys. 1999;44:911-919. 7. Berbeco RI, Nishioka S, Shirato H, et al. Residual motion of lung tumours in gated radiotherapy with external respiratory surrogates. Phys Med Biol. 2005;50:3655-3667. 8. Paganelli C, Seregni M, Fattori G, et al. Magnetic resonance imaging-guided versus surrogate-based motion tracking in liver radiation therapy: A prospective comparative study. Int J Radiat Oncol Biol Phys. 2015;91:840-848. 9. PRNewswire.com. Chicago, IL: Cision Ltd. Available at: https:// www.prnewswire.com/news-releases/accuray-launches-synchronymotion-tracking-and-correction-technology-for-the-radixact-sys tem-300836858.html. Accessed July 1, 2019. 10. Chen GP, Tai A, Keiper TD, et al. Technical Note: Comprehensive performance tests of the ﬁrst clinical real-time motion tracking and compensation system using MLC and jaws. Med Phys. 2020;47: 2814-2825. 11. AAPM. The MArkerless Lung Target Tracking CHallenge (MATCH). Available at: https://www.aapm.org/GrandChallenge/ MATCH/default.asp. Accessed September 1, 2020. 12. Kilby W, Dooley J, Kuduvalli G, et al. The CyberKnife robotic radiosurgery system in 2010. Technol Cancer Res Treat. 2010;9: 433-452. 13. Schnarr E, Beneke M, Casey D, et al. Feasibility of real-time motion management with helical tomotherapy. Med Phys. 2018;45:13291337. 14. Ferris WS, Kissick MW, Bayouth JE, et al. Evaluation of radixact motion synchrony for 3D respiratory motion: Modeling accuracy and dosimetric ﬁdelity. J Appl Clin Med Phys. https://doi.org/10.1 002/acm2.12978. 15. Accuray training document 1064193.A. In: Synchrony Real-Time Motion Tracking and Correction on the Radixact Treatment Delivery System. Sunnyvale, CA: Accuray Inc; 2019. 16. Wolthaus JWH, Sonke JJ, ven Herk M, et al. Comparison of different strategies to use 4DCT in treatment planning for lung cancer patients. Int J Radiat Oncol Biol Phys. 2008;70:1229-1238. 17. Ferris WS, Culberson WS. Technical note: Patient dose from kilovoltage radiographs during motion-synchronized treatments on radixact. Med Phys. https://doi.org/10.1002/mp.14461. 18. Huang E, Dong L, Chandra A, et al. A Pollack, intrafraction prostate motion during IMRT for prostate cancer. Int J Radiat Oncol Biol Phys. 2002;53:261-268. 19. Murthy V, Mallik S, Master Z, et al. Dose helical tomotherapy improve dose conformality and normal tissue sparing compared to conventional IMRT? A dosimetric comparison in high risk prostate cancer. Tech Cancer Res Treat. 2011;10:179-185.

Organ sparing total marrow irradiation compared to total body irradiation prior to allogeneic stem cell transplantation

Received: 22 March 2021 Revised: 1 June 2021 Accepted: 7 June 2021 DOI: 10.1111/ejh.13675

ORIGINAL ARTICLE

Organ sparing total marrow irradiation compared to total body irradiation prior to allogeneic stem cell transplantation André Haraldsson 1,2 | Stina Wichert 3 | Per E. Engström 1 | Stig Lenhoff 3 | Dominik Turkiewicz 4 | Sarah Warsi3,5 | Silke Engelholm 3 | Sven Bäck 1,2 | Jacob Engellau 1,3 1 Radiation Physics, Department of Hematology, Oncology and Radiation Physics, Skåne University Hospital, Lund, Sweden 2

Department of medical radiation physics, Clinical Sciences, Lund university, Lund, Sweden 3

Department of Hematology, Oncology and Radiation Physics, Skåne University Hospital, Lund, Sweden 4

Abstract Objectives: Total body irradiation (TBI) is commonly used prior to hematopoietic stem cell transplantation (HSCT) in myeloablative conditioning regimens. However, TBI may be replaced by total marrow irradiation (TMI) at centres with access to Helical TomoTherapy, a modality that has the advantage of delivering intensity-modulated radiotherapy to long targets such as the entire bone marrow compartment. Toxicity after organ sparing TMI prior to HSCT has not previously been reported compared to

Department of Pediatric Oncology and Hematology, Skåne University Hospital, Lund, Sweden

TBI or with regard to engraftment data.

Division of Molecular Medicine and Gene Therapy, Lund Stem Cell Center, Lund University, Lund, Sweden

ceived organ sparing TMI prior to HSCT and compared this cohort to retrospective

Correspondence André Haraldsson, Radiation Physics, Department of Hematology, Oncology and Radiation Physics, Skåne University Hospital, Lund, Sweden. Email: andre.haraldsson@med.lu.se

67.5% for all patients treated with TMI and 80.5% for patients with matched unrelated

Methods: We conducted a prospective observational study on 37 patients that redata on 33 patients that received TBI prior to HSCT. Results: The 1-year graft-versus-host disease-free, relapse-free survival (GRFS) was donor and treated with TMI, which was a significant difference from historical data on TBI patients with a hazard ratio of 0.45 (P = .03) and 0.24 (P < .01). Engraftment with a platelet count over 20 [K/µL] and 50 [K/µL] was significantly shorter for the TMI group, and neutrophil recovery was satisfactory in both treatment cohorts. There was generally a low occurrence of other treatment-related toxicities. Conclusions: Despite small cohorts, some significant differences were found; TMI as part of the myeloablative conditioning yields a high 1-year GRFS, fast and robust engraftment, and low occurrence of acute toxicity. KEYWORDS

ALL, HSCST, TBI, TMI, Tomotherapy

This is an open access article under the terms of the Creative Commons Attribution-NonCommercial-NoDerivs License, which permits use and distribution in any medium, provided the original work is properly cited, the use is non-commercial and no modifications or adaptations are made. © 2021 The Authors. European Journal of Haematology published by John Wiley & Sons Ltd. Eur J Haematol. 2021;00:1–15.

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1 | I NTRO D U C TI O N Total body irradiation (TBI) is used in myeloablative conditioning regimes prior to hematopoietic stem cell transplantation (HSCT), primarily to younger patients with high-risk haematological malignancies.1,2 The rationale of TBI is shown by lower relapse rate and improved overall survival (OS) when radiotherapy combined with chemotherapy is compared to chemotherapy alone.1-3 However, the standard radiotherapy treatment with whole-body anterior-posterior irradi4

ation is toxic, especially in combination with chemotherapy, and may cause significant side effects to several organs such as lungs, kidneys, bowel and liver. Increased toxicity has previously haltered attempted dose escalation, a lower relapse rate with higher radio5

therapy dose has not affected the overall survival. A consensus on TBI technique and fractionation 6,7 has been lacking, which hampers comparisons between centres. Helical Tomotherapy (HT; Accuray, CA, USA) is a radiotherapy

Summary of significance • This is the first reported comparison between two specific radiotherapy techniques with regard to haematological recovery and toxicity, where the newer technique irradiates less to the tissue surrounding the bone marrow as compared to the older radiotherapy technique. • From our data, we conclude that the newer targeted radiotherapy is not worse than the older total body irradiation, and more patients survive without complications associated with side effects from either radiation or the transplantation. • Patients irradiated prior to hematopoietic stem cell transplantation should be considered for the newer, more targeted radiotherapy, and could potentially reduce adverse events associated with the treatment.

treatment modality capable of delivering intensity-modulated treatments to complex and long targets like the bone marrow, generally referred to as total marrow irradiation (TMI). HT allows precise treat-

cyclosporine and methotrexate were used as standard GvHD proph-

ment and imaging of targets up to about 135 cm length without any

ylaxis. In addition, in both cohorts, patients with a matched unre-

field junctions, and with the built-in imaging, it delivers precise radio-

lated donor (MUD) all received Thymoglobuline, an anti-thymocyte

8,9

This provides for the opportunity to deliver bone marrow

globulin (ATG) in the conditioning, 4 mg/kg if the HLA match was

targeted radiotherapy while sparing other organs, which may affect

≥8/8 and 6 mg/kg if the HLA match was 7/8. The date of the last

recovery, toxicity and outcome.

follow-up is the 20th of August 2020. The study was approved by

therapy.

Toxicity after organ sparing TMI prior to HSCT has previously 10,11

been reported,

the Regional Ethical Review Board in Lund, Sweden (2013/149 and

and dose escalation trials have been con-

2017/132). Signed informed consent according to local guidelines,

ducted12,13 as well as reduced intensity studies,14 but has thus far

the guidelines of the European Blood and Marrow Transplantation

not been compared to standard TBI treatment with patients from the

Group (EBMT), and the Declaration of Helsinki was obtained in all

same clinic nor reported with regard to graft-versus-host disease-

patients prior to treatment to register patients demographics, diag-

free, relapse-free survival (GRFS) or engraftment. In this paper, we

nosis, transplant characteristics, outcome and length of follow-up.

compare prospectively observed patients that received TMI with

The data were then retrieved from our institution's local transplant

retrospective data on a similar patient cohort receiving the same

registry and supplemented in case of missing data by reviewing the

fractionated TBI during the 5-year period that preceded the intro-

patient's clinical charts.

duction of the new TMI irradiation technology, with other treatment standards unchanged.

2 | M ATE R I A L S A N D M E TH O DS 2.1 | Patient characteristic

2.2 | Radiotherapy treatment Our method for TMI has previously been described in detail,15 but is summarised in this section. The patients were irradiated with 2 Gy/ fraction twice daily, to a total dose of 12 Gy unless stated otherwise. The treatment was performed with a TomoTherapy HD that delivers

In this study, all patients at our JACIE accredited transplant centre

radiation at a maximum of 860 cGy/min at 1.5 cm depth in a helical

in Lund (Sweden) receiving TMI-based myeloablative conditioning

fashion. All patients were immobilised, scanned and treated in two

prior to HSCT were consecutively included since the introduction of

positions due to the maximum treatment length of 140 cm on the

the treatment modality in October 2014. For comparison, we used

TomoTherapy, and the upper body treated head-first followed by

retrospective data on all patients that have received TBI as part of

the lower body treated feet-first at every fraction. For all patients,

a myeloablative conditioning regimen during the previous 5-year

the clinical target volume included the skeletal structures and the

period, between July 2009 until August 2014. Patients receiving a

spleen. For patients with acute lymphoblastic leukaemia (ALL) the

haploidentical alfa/beta T–cell-depleted transplant were excluded.

CNS and for male children, testicles were included. A 5-10 mm mar-

The stem cell source was for all adult patients’ peripheral blood stem

gin, depending on immobilisation of body site, was added as a plan-

cells (PBSC) and for children's bone marrow (BM). For all patients,

ning margin to account for movement and geometrical uncertainties

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HARALDSSON et AL.

called planning target volume (PTV). Dose to organs at risk was mini-

non-relapse death as a competing risk. GRFS events were defined

mised without compromising dose to this PTV.

as the first occurrence from severe (grade >II) acute GVHD, severe

Patients receiving TBI were treated immobilised in a side posi16

chronic GVHD, relapse or death from any cause. Patients’ that did

with lead blocks to

not reach the specific time point was censored. For GVHD, compet-

shield the lungs. The absorbed dose rate at the dose maximum depth

ing risk included treating deaths, relapse and graft failure. For time to

of 1.5 cm was approximately 30 cGy/min.

engraftment, patient with relapse or death was censored. The sub-

tion at 4.5 m distance from the radiation source

distribution hazard model28 was used for the analysis of outcomes with competing events.

2.3 | Evaluation of toxicity and outcome

All tests were two-sided and considered significant at P < .05, using 95% confidence intervals. All statistical analyses were per-

Follow-up included overall survival (OS), 1-year GvHD-free/

formed with Python 3.629 or R.30

relapse-free survival (GRFS),17 1-year transplant-related mortal-

The following variables were included in the analysis: recipient

ity (TRM), engraftment data, acute toxicities, scoring of acute and

age, disease, disease status at HSCT, donor type, in vivo T-cell de-

chronic graft-versus-host disease (GvHD) and relapse rate (RR).

pletion, GVHD prophylaxis, Karnofsky performance score (KPS) for

Where GRFS was defined as the fraction of patients that survived

adult patients, donor-recipient sex match and year of transplant. All

with no adverse event described in depth in the original article.

clinical variables were tested first for the affirmation of the propor-

For late effect complications, the median time of follow-up for the

tional hazard assumption.

TMI cohort is slightly over one year, but we report on pulmonary and renal function tests before and at 3, 6 and 12 months, respectively, after HSCT.18 Engraftment was defined according to EBMT criteria: the first of three consecutive days with neutrophil count

3 | R E S U LT S

≥0.5 × 109/L and ≥1.0 × 109/L, and platelet count ≥20 × 109/L and

3.1 | Patient characteristics

mainly scored according to the modified Glucksberg criteria.19 The

A total of 37 TMI patients and 33 TBI patients were analysed.

TMI cohort was additionally scored according to the MAGIC crite-

Patient characteristics were very similar with respect to age, gender,

ria. 20 For the assessment of chronic GvHD, we have used stand-

diagnosis distribution, stem cell source and CD34 cell doses for the

ard NIH criteria. 21,22 Glomerular filtration rate has previously been

cohorts, Tables 1 and 2. Median follow-up (range) was 13 (2-70) and

used to estimate the radiation and chemotherapy-related renal tox-

72 (2-134) months for the TMI and TBI groups, respectively. There

icity in TBI23 and was calculated from the pre- and post-treatment

were more patients in the TMI cohort that had a disease of second

S-creatinine. Idiopathic pneumonia syndrome (IPS) was defined as

complete remission (CR2) or worse. Dose distribution to the target

lung symptoms, dyspnoea and hypoxia, with radiological evidence

was similar for the cohorts, two patients in the TMI group received

of widespread alveolar injury, in which infectious aetiologies, as well

reduced 10 Gy in 5 fractions, and one received 8 Gy on four frac-

≥50 × 109/L (without transfusion), respectively. Acute GvHD was

as cardiac and renal dysfunction, has been excluded. 24 Function

tions. Two patients from the TBI group received 10 Gy in 5 fractions.

pulmonary test constituted of FEV1 (Forced Expiratory Volume in

For the TMI patients, the dose was kept to a minimum in the kidneys,

one second). The probability for complications was calculated using

heart, bowel bag and liver, Figure 1. Generally, lower to (surround-

normal tissue complication probability (NTCP),

25,26

a widely used

ing) normal tissue. Also, with TMI a larger portion of the bone mar-

logistic model for estimating the probability of radiation-induced

row received closer to a prescribed dose, that is better homogeneity.

toxicity in radiotherapy. Radiation toxicity scoring was done according to the common Radiation Therapy Oncology Group (RTOG) criteria. 27

3.2 | Survival

2.4 | Statistical analysis

treatment types was 67.5% for TMI and 39.4% for TBI patients

The 1-year GRFS (no GRFS-related event at 1 year) for the two (HR = 0.45, 95% CI: 0.21- 0.93, P = .027), Figure 2A. When only con-

Hypothesis testing was performed using Mann-Whitney U test

sidering patients with MUD, the GRFS at 1 year was 80.5% for TMI

for continuous variables, and chi-squared or Fisher's exact test for

and 42.3% for TBI patients, respectively (HR = 0.24, 95% CI: 0.09-

categorical variables. Covariates and significance for toxicities and

0.67, P = .003), Figure 2B. More patients in the group that received

recovery where time to event existed was tested using Cox's propor-

TMI as radiotherapy survived without any adverse events such as

tional model. Kaplan-Meier was used to assess the non-parametric

graft-versus-host disease compared to historical data on TBI pa-

survival on group level for overall survival, and the log-rank test

tients. A total of 27 patients treated with TMI had a follow-up time

was used to compare the survival distribution between the two pa-

longer than 1 year, and 33 patients treated with TBI. Several vari-

tient groups. The probability of relapse was calculated using non-

ables were tested univariate and GRFS was additionally modelled

relapse death and TRM as competing risk and TRM using relapse and

with multivariate logistic regression, Table 3, where radiotherapy

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HARALDSSON et AL.

TA B L E 1 [Patient characteristics]: Thymoglobuline, an anti-thymocyte globulin (ATG), was used for all patients with matched unrelated donor (MUD). Diagnosis included was: B-Acute Lymphoblastic Leukaemia (B-ALL), T-Acute Lymphoblastic Leukaemia (T-ALL), Mixed Phenotype Acute Leukaemia (MPAL), Acute Myeloid Leukaemia (AML), Blastic Plasmacytoid Dendritic Cell Neoplasm (BPDCN), Chronic Myeloid Leukaemia (CML), MyeloProliferative Neoplasms (MPN), Multiple Myeloma (MM), Non-Hodgkin's Lymphoma (NHL), Myelodysplastic Syndrome (MDS). Stem cell sources included bone marrow (BM) or peripheral blood stem cells (PBSC). Human leukocyte antigens (HLA) for a matched unrelated donor (MUD) was compared as perfect match (8/8) versus less than 8/8. Similar, the number of patients in first complete remission (CR1) was compared to second complete remission (CR2) and partial remission (PR) or worse. Finally, the Hematopoietic Cell Transplantation-Comorbidity Index (HCT-CI) was available for all adult patients in both cohorts, 31 of the TMI patients and 29 of the TBI patients. *Cyclophosphamide 60 mg/kg day −6 and day −5, Etoposide 60 mg/kg day-5 (maximum dose of 3600 mg) Patient characteristics

TMI (N = 37)

TBI (N = 33)

Median age (range) /years

29 (5-57)

28 (10-53)

19 (51%)

19 (58%)

HCT-CI Score 0 Score 1

3 (8%)

4 (12%)

Score 2

7 (19%)

6 (18%)

Score 3

1 (3%)

0 (0%)

Missing

7 (19%)

4 (12%)

Female

Male

B-ALL

T-ALL

Gender

Diagnosis

MPAL

AML (incl. BPDCN)

CML

MPN

NHL

MDS

Stem cell source BM

PBSC

6.0 (σ = 1.2)

6.0 (σ = 1.1)

CD34 cell dose, median [×10 6/kg] Transplantation type MUD

MRD

Donor age, median (range)

27 (16-55)

32 (15-55)

MUD HLA match 7/8

CR1

>CR1 (or MDS)

Stage at tx

Chemotherapy* Cyclophosphamide

Etoposide

technique was a significant contributing factor. There was no signifi-

3.3 | Engraftment

cant difference in OS between the radiotherapy treatment types at 12 months (P = .509), TRM P = .239 or relapse P = .309. However,

The engraftment time for patients with peripheral blood stem cells

the cohorts are small, and the follow-up too short to assess long-

(PBSCs) as stem cell source was generally satisfactory for both TMI

term effects, and they are included merely for reference.

and TBI. The median (range) was 14 days (11-124) for TMI and 16 days

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HARALDSSON et AL.

TA B L E 2 [Disease characteristics]: Disease characteristics with radiotherapy type (RT), diagnosis, subclassification, disease stage at Tx, HCT-CI score for adults, age at Tx and Disease Risk Index (DRI) according to CIBMTR HCT- CI score

DRI (Disease Risk Index CIBMTR)

Age at Tx

Diagnosis

Subclassification

Disease stage at Tx

TMI

MPN

8p11-syndrome (t(8;13)) with T lymphoblastic lymphoma

PR1 (FISH positive for FGFR-1 -rearrangement)

Intermediate

CML

Ph+, p210, with lymphoid blast crisis

CP2, no CHR (complete hematologic response) b

Low

ALL

Pre-B-ALL

CR2

ALL

Ph+, p210

CR1

Intermediate

ALL

Pre-B-ALL, t(12;21)

CR2 (CNS relapse)

Myeloma

IgG st IIIA, ISS stage II

PR2a

Intermediate

ALL

Pre-B-ALL, non responder day 29.

CR1

Intermediate

ALL

Pre-B-ALL, Ph+, p190

CR1

Intermediate

MPAL

MPAL (dominant pre-B-ALL clone)

CR1

ALL

T-ALL, del(9p)

CR2

High

ALL

Pre-B-ALL

CR2

High

AML

Blastic plasmacytoid dendritic cell neoplasm

CR1

Intermediate

ALL

Pre-B-ALL

CR1

Intermediate

ALL

B-ALL

CR2

High

ALL

T-ALL/LBL, bulky disease

CR1

Intermediate

ALL

B-ALL Ph-like SFPQ-ABL1 fusion gene

CR1

Intermediate

ALL

Pre-B-ALL, Ph+p190

CR3

NHL

FL, FLIPPI 3A

VGPR3

Intermediate

ALL

B-ALL

CR2 (CNS and BM relapse)

High

ALL

Pre-B-ALL, complex karyotype, LiFraumeni mosaicism

CR1

Intermediate

Myeloma

IgA, ISS 3, t(4;14)

CR2 a

Intermediate

ALL

Pre-B-ALL

CR2 (CNS and BM relapse)

NHL

hepatosplenic T cells lymphoma (gamma/delta)

CR1

Intermediate

CML

Ph+, p210, with lymphoid blast crisis

CP2, Ph+ 96%b

Low

CML

Ph+, p210, with lymphoid blast crisis

CP2 with MMR (major molecular response)b

Low

ALL

Pre-B-ALL

CR2

Myeloma

RRMM with del(17p), PR3 on 6th line of therapy with VTD-PACE

PR3

High

NHL

hepatosplenic T cells lymphoma (gamma/delta)

CR1

NHL

DLBCL

PR3

Intermediate

AML

MLL-rearrangement, complex karyotype, extensive extramedullary disease

CR1

High

ALL

B-ALL

CR1

Intermediate

NHL

Waldenstrom macroglobulinemia

CR3

Low

ALL

T-ALL, bulky disease

CR1

Intermediate

(Continues)

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TA B L E 2 (Continued)

Diagnosis

Subclassification

ALL

Ph+, p190

MPAL

TBI

Disease stage at Tx

HCT- CI score

DRI (Disease Risk Index CIBMTR)

Age at Tx

CR1

Intermediate

CR1

ALL

Pre-B-ALL

CR2

High

ALL

Pre-B-ALL, ABL2-translocation

CR2 (CNS and BM relapse)

ALL

Pre-B-ALL, t(1;22)

CR1

MDS

RAEB-2 (10% blasts), normal karyotype

cytological remission

Intermediate

ALL

pre-B-ALL, Ph+, p190

CR1

Intermediate

AML

trisomy 13, FLT3 neg, NPM1 neg.

CR1

Intermediate

AML

M4. Inversion 16

CR2

Low

AML

Ph+, p210

CR1

Intermediate

ALL

T-ALL, t(7;11)

CR1

AML

normal karyotype, FLT3-ITD+, NPM1+

CR1

Intermediate

AML

normal karyotype, FLT3-ITD+, NPM+

CR1

Intermediate

ALL

T-ALL

CR1

Intermediate

MPN

sAML post-PV, trisomy 13, FLT3-ITD+,NPM1+

CR1

Intermediate

MDS

RAEB-2 (14% blasts), t(3;3)

PR (reduction of blasts to 6%-7%)

Intermediate

AML

FLT3-ITD+, NPM1 neg

CR1

Intermediate

ALL

Pre-B, t(8;14), not Burkitt

CR2

High

ALL

Pre-B, trisomy 21

CR1

ALL

Pre-B, t(4;11), MLL+

CR1

Intermediate

NHL

T lymphoblastic lymphoma (LBL)

CR2

Intermediate

AML

FLT3 neg, NPM1+.

CR2

Intermediate

MDS

RAEB-2/AML (20% blasts), complex monosomal karyotype, including −5 och −7

cytological remission

High

ALL

T-ALL + minor clone with pre-B-ALL and CNS involvement

CR1

NHL

Lymphoplasmacytic lymphoma, stage IV

PR1

Low

ALL

Pre-B-ALL

CR1

Intermediate

CML

Ph+, p210, with lymphoid blast crisis

CP2 with MMR (major molecular response) b

Low

ALL

Pre-B-ALL

CR2

High

NHL

T lymphoblastic lymphoma (LBL)

CR2

Intermediate

ALL

T-ALL, t(1;1), del(9), extramedullary bulky disease

CR1

Intermediate

ALL

Pre-B-ALL

CR2

High

ALL

MLL-rearrangement, t(4;11), XXY

CR1

Intermediate

ALL

Pre-B-ALL

CR1

Intermediate

ALL

Pre-B-ALL, t(4;11)

CR1

Intermediate

(Continues)

174

HARALDSSON et AL.

TA B L E 2 (Continued)

DRI (Disease Risk Index CIBMTR)

Age at Tx

Diagnosis

Subclassification

Disease stage at Tx

HCT- CI score

ALL

T-ALL, t(8;22) with fusion bcr/FGFR1

CR1

Intermediate

ALL

Pre-B-ALL

CR1

Intermediate

NHL

Sezarys syndrome with lymphadenopathy and bone marrow involvement

PR 1

Intermediate

According to IMWG response criteria for multiple myeloma [56].

CML response according to ELN (European Leukaemia Net) criteria [57].

F I G U R E 1 [Example dose distribution for the two radiotherapy types] Reconstructed dose distribution for total body irradiation (left/middle upper) and planned dose distribution for total marrow irradiation (right/middle lower) for the same patient and prescribed dose. The dose for TBI was reconstructed using delivered monitor units and reconstructed blocks from saved data. Absorbed dose is presented in Gy

(11-52) for TBI for a thrombocyte count of 20 [K/µL] (P < .01), and me-

Three months after transplantation, all but two patients in the

dian (range) of 16 days (12-144) and 19 days (12-136), respectively, for

TMI cohort and three patients in the TBI cohort showed complete T-

a count over 50[K/µL] (P < .01). Similar for neutrophil recovery with

lymphocytic and myeloid chimerism in peripheral blood. Two patients

absolute neutrophil count (ANC) over 0.5 [K/µL] and PBSC as stem

in the TMI cohort had mixed T-lymphocytic chimerism with 10%-15%

cell source, the median (range) was 18 (12-26) days and 18 (12-31)

and 6%, respectively, of their recipient cells. Both patients are alive

for TMI and TBI, respectively. Similar, for an ANC over 1.0 [K/µL], the

and disease-free 53 and 16 months after transplantation. Three pa-

median (ranges) was 20 (13-29) days and 19 (12-39) for TMI and TBI,

tients in the TBI cohort with mixed chimerism had progressive dis-

respectively. Similar for bone marrow (BM) as stem cell source, the

ease four, five and eight months, respectively, post-transplant.

time to engraftment for the TMI and TBI patients was 26 days (14-33) versus 29 days (20-176), 30 days(17-76) versus 72.5 days (23-226), 18 days (12-29) versus 25.5 days (19-29) and 21 days (13-33) versus

3.4 | Graft-versus-host disease

26 days (19-34) for a thrombocyte count of 20 [K/µL], thrombocyte count of 50 [K/µL], ANC over 0.5 [K/µL] and ANC over 1.0 [K/µL].

The incidence of acute GvHD scored >II according to the modified

Engraftment with a platelet count over 20 [K/µL] and 50 [K/µL]

Glucksberg criteria was 4 for the TMI cohort (N = 37) and 6 for the

was significantly shorter for the TMI group for patients with PBSCs

TBI cohort (N = 33), Table 3. Using standard NIH criteria for chronic

as a stem cell source (P = .01, P = .03) Figure 3, but not for patients

GvHD, there were 3 moderate-to-severe incidents for the TMI co-

with BM as stem cell source (P = .25, P = .25). With a subdistribution

hort (N = 36) and 8 for the TBI cohort (N = 32), Table 3. Only con-

hazard model, the difference between radiotherapy treatment types

sidering patients with MUD, the incidence was 0/28 and 5/25 for

was significant for time to platelet count over 20 [K/µL], Table 4.

TMI and TBI. Further, with multiple regression analysis, moderate-

Further, time to engraftment was modelled as a dependent variable

to-severe chronic GvHD was modelled as dependent where trans-

with a neutrophil count over 1.0 [K/µL] and a thrombocyte count

plantation was significant as independent variables, Table 3. Similar,

over 20 [K/µL], Table 4, where the difference was significantly im-

acute GVHD with grade >II was analysed with multiple regression,

pacted by radiotherapy type and stem cell source for time to platelet

Table 3. Similar results were obtained with Cox's regression, where

recovery, but no such correlation was seen for time to neutrophil

donor age (P < .01) and CMV serostatus status (P < .01) were signifi-

count.

cant factors influencing acute GVHD but radiotherapy type (P = .29)

175

F I G U R E 2 [Kaplan-Maier plot for graft-versus-host disease-free survival]. GRFS over time presented for all patients (top) and for patients transplanted from MUD (bottom). Hazard ratio (HR) was calculated using Cox's proportional model, with radiotherapy treatment type as independent variable and significance testing with the log-rank test

176

HARALDSSON et AL.

TA B L E 3 [Graft-versus-host disease-free/relapse-free survival and graft-versus-host disease]: Regression for GRFS, acute GvHD and chronic GvHD, presented with hazard ratio (HR), confidence intervals (CI) and significance. The variables were Radiotherapy treatment type, total marrow or total body irradiation, Cytomegalovirus (CMV) serostatus (D-/R-), type of donor, matched unrelated (MUD) or matched related (MRD), if the donor was over 40, Hematopoietic Cell Transplantation-Comorbidity Index (HCT-CI). Numbers in bold was found significant P < .05. Multivariate analysis with all the corresponding dependent variables listed under the independent variable, four dependents for GRFS and acute GvHD, and three dependents for chronic GvHD, with independent variables in bold Univariable

Multivariable

(N)

HR (95% CI)

TMI (37)

0.45 (0.21- 0.93)

.03

0.39 (0.18- 0.84)

.02

2.29 (1.09- 4.79)

.03

2.08 (0.98- 4.38)

.05

1.78 (0.88-3.63)

.11

2.30 (1.10- 4.79)

.03

0.55 (0.16-1.92)

.35

0.49 (0.08-1.62)

.25

1.70 (0.43-6.61)

.45

4.29 (0.68-27.06)

.12

2.68 (0.76-9.09)

.13

7.25 (1.47-35.59)

.01

cont.

1.06 (1.02-1.13)

.01

1.08 (1.04-1.12)

<.01

TMI (37)

0.35 (0.10-1.30)

.11

0.33 (0.09-1.18)

.08

4.54 (1.43-14.37)

.01

4.99 (1.44-17.35)

.01

0.80 (0.18-3.52)

.76

1.66 (0.35-7.97)

.52

GRFS (1 year) Radiation treatment type

TBI (33) Transplantation type

MRD (15) MUD (55)

Disease stage

>CR1 (32) CR1 (38)

Acute GvHD Radiation treatment type

TMI (37) TBI (33)

Transplantation type

MRD (15) MUD (55)

CMV serostatus status

D-/R- (15) <D-/R- (55)

Donor age Chronic GvHD Radiation treatment type

TBI (33) Transplantation type

MRD (15) MUD (55)

CMV serostatus status

D-/R- (15) < D-/R- (55)

and transplantation type (P = .13) did not. Most notable, the pattern

3.5 | Radiation-induced normal tissue toxicity

of acute GvHD differed between the two cohorts with more cases of lower GI involvement for patients receiving TBI, 4 with stage >2

The probability of radiation-induced normal tissue complication

in the TBI cohort, versus 2 with stage >2 in the TMI cohort. Hence, a

(NTCP) grade over stage II, as graded according to RTOG criteria,

regression for lower GI acute GVHD stage >2 as the dependent vari-

was calculated for TMI and TBI, respectively. Estimated glomeru-

able was performed but none of the independent variables was sig-

lar filtration (eGFR) was lower after radiotherapy for the TBI group

nificant. Twelve patients in the TMI cohort fulfilled the new MAGIC

than for the TMI group, the difference was significant (P = .020)

criteria for mild acute GVHD with upper GI involvement stage 1,

but too small to be clinically relevant, Table 5. With linear regres-

whereas only two were biopsy-verified with a typical histologic pic-

sion to predict eGFR, no significant regression equation was found

ture, thereby fulfilling the older modified Glucksberg criteria for this

(P = .186, N = 44), where a few patients lacked follow-up serum

diagnosis.31 In the TBI cohort, only one patient was diagnosed with

creatine.

acute GVHD with upper gastrointestinal (GI) involvement according

There was only one incident of IPS in each cohort, a grade 4 event

to older criteria. In an attempt to retrospectively re-evaluate the TBI

from the TMI cohort versus a grade 5 event from the TBI group ac-

cohort according to the modern MAGIC criteria, at least five more

cording to CTCAE v.5. Both patients were older, 45 and 47 years re-

patients would have been scored with mild upper GI acute GVHD.

spectively, the TMI patient diagnosed with CML in a second chronic

There was one case of acute severe liver GvHD stage 4 in the TBI

phase and the TBI patient with AML in second complete remission.

cohort, compared to one case with milder stage 2 liver engagement

There was no incident of hepatic sinusoidal obstruction syndrome

of acute GVHD in the TMI cohort.

(HSOS) in either cohort.

177

HARALDSSON et AL.

F I G U R E 3 [Time to engraftment]. Cumulative time to engraftment comparing radiotherapy treatment type. Time to engraftment according to EBMT criteria plotted for patients transplanted from peripheral stem cells (PBSCs)

4 | D I S CU S S I O N

except for the radiotherapy technique. The TMI cohort had more patients in second complete remission or worse. One factor that

The GRFS was significantly better for patients treated with TMI

could attribute to increased GRFS was the year of treatment, where

prior to HSCT than for patients irradiated with TBI when consider-

the TMI cohort was treated more recently. GRFS has been shown

ing matched unrelated donors. The difference remained significant

to increase to some extent over time and Holtan et al17 stratified a

when modelled with multivariate logistic regression. This result

number of variables related to HSCT and found in multivariate logis-

strengthens the impression that conditioning with TMI generally re-

tic regression that the period of treatment was significant with an RR

sults in a lower occurrence of toxicity, treatment-related mortality

of 0.8. This can be compared to the HR of a GRFS-related adverse

and GvHD. The treatment groups were very similar with regards to

event for our two cohorts of 0.24 in our study when considering

HCT-CI score, age, donor age, diagnosis, infused CD34+ cell count,

only patients transplanted from a matched unrelated donor. Thus,

and patients were given the same GvH prophylaxis and treatment

post-treatment care and other factors that have improved over time

178

HARALDSSON et AL.

TA B L E 4 [Engraftment data for days to platelet count over 20 K/µL and days to neutrophils over 1.0 K/µL]: The variables were radiotherapy treatment type, total marrow or total body irradiation, stem cell source bone marrow or PBSCs and donor age over or under 40. Numbers in bold was found significant P < .05. Independent variables in bold using all the dependent variables listed for multivariable regression. Higher hazard ratio (HR) should be interpreted in favour of faster engraftment

Univariable N

HR (95% CI)

Multivariable Pvalue

HR (95% CI)

Pvalue

Days to platelets >20 [K/µL] Radiation treatment type

TMI (37)

1.61 (1.02-2.55)

.04

2.04 (1.28-3.23)

<.01

TBI (33) Infused cell count CD34+

1.30 (1.10-1.53)

<.01

1.28 (1.02-1.61)

.03

Stem cell source

PBSC (59)

2.01 (1.33-3.05)

.01

2.12 (1.24-3.63)

<.01

0.98 (0.96-1.01)

.14

0.97 (0.95- 0.99)

.03

1.29 (0.79-2.09)

.31

1.20 (0.72-1.98)

.49

BM (11) Donor age

Days to neutrophils >1.0 [K/µL] Radiation treatment type

TMI (37) TBI (33)

Infused cell count CD34+

0.95 (0.78-1.15)

.59

0.83 (0.63-1.07)

.15

Stem cell source

PBSC (59)

1.60 (0.83-3.10)

.16

2.46 (1.04-5.80)

.04

0.99(0.97-1.02)

.66

0.98 (0.96-1.01)

.19

BM (11) Donor age

TA B L E 5 [Outcome data] The median follow-up for the TMI cohort is 12 months and for TBI patients 60 months. Estimated glomerular filtration rate (eGFR), median difference between the pre-transplant measurement versus 12 months after HSCT. Acute graft-versus-host-disease (aGvHD) patients with symptoms over grade II and which organ, with some patients experiencing symptoms in several organs. Abbreviations: Idiopathic Pneumonia Syndrome (IPS) and Hepatic Sinusoidal Obstruction Syndrome (HSOS) and aGvHD according to the modified Glucksberg criteria (MG). FEV1 is presented as the difference versus pre-treatment FEV1. *Number of patients with chronic graft-versus-host disease for patients alive at day 100. †Significant difference (p = .02). **number of patients with aGvHD with the number of incidence at each site

TMI (N = 37)

TBI (N = 33)

IPS incidence <Grade 4 Grade 4

1 (3%)

Grade 5

1 (3%)

eGFR difference (σ) [mL/min/1.73 m2]

−8.6 (13.7)†

−9.8 (16.7)†

FEV1 3 mo difference, median (σ) [L]

0.0 (0.3)

0.0 (0.4)

FEV1 6 mo difference, median (σ) [L]

0.1 (0.4)

0.1 (0.7)

VOD incidence

0 (0%)

cGvHD*, moderate to severe

3 (9%) (N = 35)

8 (25%) (N = 32)

AGvHD > grade 2**

4 (8%)

6 (18%)

Skin

Lower GI

Liver

could, to some extent, explain the improved GRFS. However, the dif-

such a risk. Kim et al32 investigated patterns of relapse following

ference we present is more prominent than shown in other publica-

TMI prior to HSCT and found no evidence of increased extramedul-

tions attributed to the difference in time of treatment.

lary relapse related to total marrow or total lymph node irradiation

Limiting the dose to organs at risk and to a higher degree tar-

compared to published results of regimens with TBI, nor did they

get the bone marrow with TMI will subsequently lower the dose

find any increased risk of relapse in part of the patients irradiated

to circulating blood. There have been speculations that circulating

with over 10 Gy versus under 10 Gy. Similar, Stein et al33 found no

leukemic cells could increase the risk of relapse when decreasing

higher risk of extramedullary relapse with TMI as a radiotherapy

the dose to non-stem cell sites. The follow-up is too short to assess

technique prior to HSCT when compared to similar studies with TBI.

179

HARALDSSON et AL.

In addition, in a review of literature by Kogut et al,34 including 246

incidence of radiotherapy-related early toxicity in the TMI cohort

patients, no risk of extramedullary relapse was found for patients

may be expected to also yield a lower risk of late side effects. This

that did not receive TBI.

will be reported in later studies with longer follow-up for this group.

Engraftment was significantly faster in the TMI group when mea-

The incidence of chronic GvHD was lower in patients who re-

sured by platelet count and with a lower incidence of both acute and

ceived TMI prior to SCT than the control group that received TBI, but

chronic GvHD. This has previously only been found in pre-clinical

the difference was not found significant. The prevalence of GvHD

trials,35,36 where both a dose distribution and dose rate have been

has been found to correlate with dose distribution36 in preclinical tri-

found to correlate with engraftment. Hui et al36 hypothesise that in

als. The prevalence of moderate-to-severe GvHD of 9% was similar

TMI, compared to TBI, the reduced radiation dose to the non-skeletal

to other studies for TMI46 in general, and more notable thus far no

organs results in a chemokine stromal-derived factor-1 (SDF-1) gra-

patients that were transplanted from MUD have developed severe

dient facilitating donor stem cells engraftment in the bone marrow

or moderate chronic GvHD. The incidence of acute GVHD was, simi-

niche. This could explain the shorter engraftment times in our TMI

lar to chronic GVHD, lower in the TMI group as compared to the TBI

cohort, though the engraftment time was adequate in the TBI group.

group but not statistically significant. One hypothesis for the lower

Another factor that could affect the engraftment time is the radio-

incidence is that TMI, compared to standard TBI, reduces the extent

therapy dose rate. Increased dose rate has long been linked directly

of damage to intestinal epithelial cells, a potential trigger of allore-

In this study, the local dose rate, that is the instanta-

active T-cell reactions.47,48 This is important, since the early onset of

neous dose rate, was increased 30 times in TMI compared to TBI.

acute GvHD has been found to correlate with an increased risk of

The global dose rate, the fraction dose divided by the total treat-

extensive chronic GvHD and TRM.49,50

to cell kill.

ment delivery time, was on the other hand decreased. We suggest

Total marrow irradiation and TBI prior to HSCT have been stud-

the local, but not the global, dose rate to influence cell kill and thus

ied in randomised trials. Paix et al51 reviewed the current literature

toxicity, but this subject is partly uncharted in a clinical setting for

in 2018. They concluded that Phase I and II trials have demonstrated

TBI and TMI. In addition, there is a difference in dose coverage to

the feasibility and tolerance of TMI and that the dose to organs at risk

the bone marrow of the ribs, in the lung shielded area between the

could be reduced. High-dose TBI of up to 14 Gy has been compared to

two techniques. The effect is negligible when considering the total

standard regimen.38 The authors found that the reduced relapse risk

volume but may affect the cell kill from the radiotherapy treatment

with higher doses was hampered by increased non-relapse mortality

in that volume. Finally, differences and advances in care for HSCT

(NRM) and found no significant difference in OS. Dose escalation with

patients have improved38 and could contribute to the increased re-

TMI has been investigated from 12 Gy up to 15 Gy13 for patients with

covery. Which of these effects impacts the treatment, and to what

ALL. The authors concluded that dose escalation was feasible and that

extent, should be attributed to further studies.

the doses were well tolerated. The authors concluded that research

The large difference in the mean dose and probability of compli-

should focus on strategies to reduce TBI toxicity since radiotherapy

cation to kidneys as calculated by NTCP did not translate to a large

clearly benefits disease control. TMI irradiation has also been investi-

difference in renal dysfunction. Renal dysfunction after TBI and SCT

gated in patients with relapsed ALL33 with doses of up to 20 Gy and had

has previously been reported for children,

39,40

where 44.4% had im-

a relatively low occurrence of severe acute GVHD but many patients

paired renal function or elevated creatinine levels at follow-up, and

exhibited severe cGVHD, and with a 1-year OS of 55.5%. Further,

for adults41 where 5 out of 29 and 4 out of 64 adult patients in the

Stein et al33 concluded that TMI is feasible and was encouraged by the

respective study had elevated levels. Pulmonary toxicity has previ-

preliminary clinical response. Treatment and dose escalation with TMI

ously been found to correlate with radiotherapy, cyclophosphamide,

prior to HSCT has been studied for a number of diseases such as mul-

the addition of busulphan42 and dose rate 43,44 in total body irradi-

tiple myeloma and ALL11,12,14 where the key takeaway was that TMI

ation using similar radiotherapy fractionation as the current study.

was found feasible, and CR rate was found encouraging. Jensen et al14

The fractionation of 12 Gy TBI in 6 fractions was found to induce

reported outcome and toxicity and compared transplant-related tox-

an IPS incidence of 6%-7% with lung shielding, which correlates well

icity and mortality from other studies52-55 with FLU/MEL condition-

with this study. Since dose rate has been found to correlate with pul-

ing combined with TMI regimens and concluded that their patient's

monary toxicity, there was an a priori concern that a switch to TMI

outcome compared favourably to those reported with chemotherapy-

on TomoTherapy could increase the pulmonary toxicity. However,

based conditioning alone. The lower toxicity in our study strengthens

the occurrence of IPS was low in both study groups. Hence, no

the perception that dose escalation using TMI is feasible, and patients

correlation could be found caused by increased local dose rate. A

previously ineligible for full-dose treatment could be eligible for radio-

much larger cohort would be required to rule out any difference.

therapy thanks to organ-sparing radiotherapy.

The incidence of IPS that occurred was both in older patients, which

This study compared two similar cohorts from the same clinic

actualise questions of reducing the prescribed radiation dose to pa-

that received similar treatment in all regards except radiotherapy

tients past their forties, similar to what has been recommended pre-

and time of treatment. The same GvH prophylaxis was used for both

viously.45 For the TMI cohort, the follow-up time is yet too short to

cohorts. Despite the large similarities in treatment, changes in care

evaluate late toxicity. However, as early toxicity following radiother-

can to some extent influence the result of the comparison and we

apy is related to an increased risk of developing late toxicity, the low

interpret the result with caution.

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HARALDSSON et AL.

5 | C o n c l u s i o n Our early results indicate that organ-sparing radiotherapy with TMI

as part of the myeloablative conditioning translates to a low occurrence of toxicity, a robust and fast engraftment, and a low degree of GvHD. GRFS was significantly higher with TMI compared to condi-

tioning with TBI. The low number of adverse events for patients that received TMI prior to HSCT at our one-year follow-up shows promising results and that organ sparing TMI warrants further studies and

10.

further follow-up to assess long-term effects and survival. AC K N OW L E D G E M E N T

11.

The authors want to sincerely thank Dr Susann Ullén (Clinical Studies Sweden—Forum South, Skane University Hospital, Lund, Sweden) for input and discussion regarding the statistical methodology and presentation.

12.

C O N FL I C T O F I N T E R E S T Department of the corresponding author has an ongoing research agreement with Accuray Inc, which includes funding.

13.

DATA AVA I L A B I L I T Y S TAT E M E N T The data that support the findings of this study are available on request from the corresponding author.

14.

ORCID André Haraldsson

https://orcid.org/0000-0002-1694-3738

REFERENCES 1. Adkins DR, DiPersio JF, Adkins DR. Total body irradiation before an allogeneic stem cell transplantation: is there a magic dose? Curr Opin Hematol. 2008;15:555-560. https://doi.org/10.1097/MOH.0b013 e32831188f5 2. Hartman A-R, Williams SF, Dillon JJ. Survival, disease-free survival and adverse effects of conditioning for allogeneic bone marrow transplantation with busulfan/cyclophosphamide vs total body irradiation: a meta-analysis. Bone Marrow Transplant. 1998;22:439443. https://doi.org/10.1038/sj.bmt.1701334 3. Peters C, Dalle J-H, Locatelli F, et al. Total body irradiation or chemotherapy conditioning in childhood ALL: a multinational, randomized, noninferiority phase III study. J Clin Oncol. 2020;39:295-307. https://doi.org/10.1200/JCO.20.02529 4. Giralt SA, LeMaistre CF, Vriesendorp HM, et al. Etoposide, cyclophosphamide, total-body irradiation, and allogeneic bone marrow transplantation for hematologic malignancies. J Clin Oncol. 1994;12:1923-1930. https://doi.org/10.1200/JCO.1994.12.9.1923 5. Clift RA, Buckner CD, Appelbaum FR, et al. Allogeneic marrow transplantation in patients with chronic myeloid leukemia in the chronic phase: a randomized trial of two irradiation regimens. Blood. 1991;8:1660-1665. 6. Giebel S, Miszczyk L, Slosarek K, et al. Extreme heterogeneity of myeloablative total body irradiation techniques in clinical practice: a survey of the Acute Leukemia Working Party of the European Group for Blood and Marrow Transplantation. Cancer. 2014;120:2760-2765. https://doi.org/10.1002/cncr.28768 7. Hoeben BAW, Pazos M, Albert MH, et al. Towards homogenization of total body irradiation practices in pediatric patients across SIOPE affiliated centers a survey by the SIOPE radiation oncology

15.

16.

17.

18.

19.

20.

21.

22.

working group. Radiother Oncol. 2020;155:113-119. https://doi. org/10.1016/j.radonc.2020.10.032 Peñagarícano JA, Chao M, Rhee FV, Moros EG, Corry PM, Ratanatharathorn V. Clinical feasibility of TBI with helical tomotherapy. Bone Marrow Transplant. 2011;46:929-935. https://doi. org/10.1038/bmt.2010.237 Nalichowski A, Eagle DG, Burmeister J. Dosimetric evaluation of total marrow irradiation using 2 different planning systems. Med Dosim. 2016;41:230-235. https://doi.org/10.1016/j. meddos.2016.06.001 Shinde A, Yang D, Frankel P, et al. Radiation related toxicities using organ sparing total marrow irradiation transplant conditioning regimens. Int J Radiat Oncol Biol Phys. 2019;105(5):1025-1033. https:// doi.org/10.1016/j.ijrobp.2019.08.010 Somlo G, Spielberger R, Frankel P, et al. Total marrow irradiation: a new ablative regimen as part of tandem autologous stem cell transplantation for patients with multiple myeloma. Clin Cancer Res. 2011;17:174-182. https://doi.org/10.1158/1078- 0432. CCR-10-1912 Patel P, Oh AL, Saraf SL, et al. A phase 1 trial of autologous stem cell transplantation conditioned with melphalan 200 mg/m2 and total marrow irradiation (TMI) in patients with relapsed/refractory multiple myeloma. Leuk Lymphoma. 2018;59:1666-1671. https://doi. org/10.1080/10428194.2017.1390231 Wong JY, Forman S, Somlo G, et al. Dose escalation of total marrow irradiation with concurrent chemotherapy in patients with advanced acute leukemia undergoing allogeneic hematopoietic cell transplantation. Int J Radiat Oncol Biol Phys. 2013;85:148-156. https://doi.org/10.1016/j.ijrobp.2012.03.033 Jensen LG, Stiller T, Wong JYC, Palmer J, Stein A, Rosenthal J. Total marrow lymphoid irradiation/fludarabine/melphalan conditioning for allogeneic hematopoietic cell transplantation. Biol Blood Marrow Transplant. 2018;24:301-307. https://doi.org/10.1016/j. bbmt.2017.09.019 Haraldsson A, Engellau J, Lenhoff S, Engelholm S, Bäck S, Engström PE. Implementing safe and robust total marrow irradiation using helical tomotherap - A practical guide. Phys Med. 2019;60:162-167. https://doi.org/10.1016/j.ejmp.2019.03.032 Svahn-Tapper G, Nilsson P, Jönsson C, Alvegård TA. Calculation and measurements of absorbed dose in total body irradiation. Acta Oncol. 1990;29:627-633. https://doi.org/10.3109/0284186900 9090064 Holtan SG, DeFor TE, Lazaryan A, et al. Composite end point of graft-versus-host disease-free, relapse-free survival after allogeneic hematopoietic cell transplantation. Blood. 2015;125:13331338. https://doi.org/10.1182/blood-2014-10-609032 Bjork J, Grubb A, Sterner G, Nyman U. Revised equations for estimating glomerular filtration rate based on the Lund-Malmo Study cohort. Scand J Clin Lab Invest. 2011;71:232-239. https://doi. org/10.3109/00365513.2011.557086 Przepiorka D, Weisdorf D, Martin P, et al. 1994 consensus conference on acute GVHD grading. Bone Marrow Transplant. 1995;15:825-828. Harris AC, Young R, Devine S, et al. International, multicenter standardization of acute graft-versus-host disease clinical data collection: a report from the Mount Sinai Acute GVHD International Consortium. Biol Blood Marrow Transplant. 2016;22:4-10. https:// doi.org/10.1016/j.bbmt.2015.09.001 Filipovich AH, Weisdorf D, Pavletic S, et al. National Institutes of Health consensus development project on criteria for clinical trials in chronic graft-versus-host disease: I. Diagnosis and staging working group report. Biol Blood Marrow Transplant. 2005;11:945-956. https://doi.org/10.1016/j.bbmt.2005.09.004 Jagasia MH, Greinix HT, Arora M, et al. National Institutes of Health consensus development project on criteria for

181

23.

24.

25. 26.

27.

28.

29. 30. 31.

32.

33.

34.

35.

36.

37.

38.

39.

40.

182

clinical trials in chronic graft-versus-host disease: I. The 2014 Diagnosis and Staging Working Group Report. Biol Blood Marrow Transplant. 2015;21(3):389- 401.e1. https://doi.org/10.1016/j. bbmt.2014.12.001 Borg M, Hughes T, Horvath N, Rice M, Thomas AC. Renal toxicity after total body irradiation. Int J Radiat Oncol Biol Phy. 2002;54:11651173. https://doi.org/10.1016/S0360 -3016(02)03039- 0 Panoskaltsis-Mortari A, Griese M, Madtes DK, et al. An official American Thoracic Society research statement: noninfectious lung injury after hematopoietic stem cell transplantation: idiopathic pneumonia syndrome. Am J Respir Crit Care Med. 2011;183:12621279. https://doi.org/10.1164/rccm.2007- 413ST Lyman JT. Complication probability as assessed from dose-volume histograms. Radiat Res Suppl. 1985;8:S13-S19. Emami B, Lyman J, Brown A, et al. Tolerance of normal tissue to therapeutic irradiation. Int J Radiat Oncol Biol Phys. 1991;21:109122. https://doi.org/10.1016/0360-3016(91)90171-y Cox JD, Stetz J, Pajak TF. Toxicity criteria of the Radiation Therapy Oncology Group (RTOG) and the European Organization for Research and Treatment of Cancer (EORTC). Int J Radiat Oncol Biol Phys. 1995;31:1341-1346. https://doi. org/10.1016/0360-3016(95)00060 -c Fine JP, Gray RJ. A proportional hazards model for the subdistribution of a competing risk. J Am Stat Assoc. 1999;94:496-509. https:// doi.org/10.2307/2670170 Python Software Foundation. Python Language Reference, version 3.6. http://www.python.org. 2019. Team RC. R: A Language and Environment for Statistical Computing. 2020. Schoemans HM, Lee SJ, Ferrara JL, et al. EBMT−NIH−CIBMTR Task Force position statement on standardized terminology & guidance for graft-versus-host disease assessment. Bone Marrow Transplant. 2018;53:1401-1415. https://doi.org/10.1038/s41409- 018- 0204-7 Kim JH, Stein A, Tsai N, et al. Extramedullary relapse following total marrow and lymphoid irradiation in patients undergoing allogeneic hematopoietic cell transplantation. Int J Radiat Oncol. 2014;89:7581. https://doi.org/10.1016/j.ijrobp.2014.01.036 Stein A, Palmer J, Tsai NC, et al. Phase I trial of total marrow and lymphoid irradiation transplantation conditioning in patients with relapsed/refractory acute leukemia. Biol Blood Marrow Transplant. 2017;23:618-624. https://doi.org/10.1016/j.bbmt.2017.01.067 Kogut N, Tsai N-C, Thomas SH, et al. Extramedullary relapse following reduced intensity allogeneic hematopoietic cell transplant for adult acute myelogenous leukemia. Leuk Lymphoma. 2013;54:665668. https://doi.org/10.3109/10428194.2012.720375 Glass TJ, Hui SK, Blazar BR, Lund TC. Effect of radiation dose-rate on hematopoietic cell engraftment in adult zebrafish. PLoS ONE. 2013;8:e73745. https://doi.org/10.1371/journal.pone.0073745 Hui S, Takahashi Y, Holtan SG, et al. Early assessment of dosimetric and biological differences of total marrow irradiation versus total body irradiation in rodents. Radiother Oncol. 2017;124:468- 474. https://doi.org/10.1016/j.radonc.2017.07.018 Hall EJ, Brenner DJ. The dose-rate effect revisited: radiobiological considerations of importance in radiotherapy. Int J Radiat Oncol Biol Phys. 1991;21:1403-1414. Sabloff M, Chhabra S, Wang T, et al. Comparison of high doses of total body irradiation in myeloablative conditioning before hematopoietic cell transplantation. Biol Blood Marrow Transplant. 2019;25:2398-2407. https://doi.org/10.1016/j.bbmt.2019.08.012 Watanabe Nemoto M, Isobe K, Togasaki G, et al. Delayed renal dysfunction after total body irradiation in pediatric malignancies. J Radiat Res. 2014;55:996-1001. https://doi.org/10.1093/jrr/ rru041 Esiashvili N, Chiang KY, Hasselle MD, Bryant C, Riffenburgh RH, Paulino AC. Renal toxicity in children undergoing total

HARALDSSON et AL.

41.

42.

43.

44.

45.

46.

47.

48.

49.

50.

51.

52.

53.

54.

55.

body irradiation for bone marrow transplant. Radiother Oncol. 2009;90:242-246. https://doi.org/10.1016/j.radonc.2008.09.017 Kunkele A, Engelhard M, Hauffa BP, et al. Long-term follow-up of pediatric patients receiving total body irradiation before hematopoietic stem cell transplantation and post-transplant survival of >2 years. Pediatr Blood Cancer. 2013;60:1792-1797. https://doi. org/10.1002/pbc.24702 Sampath S, Schultheiss TE, Wong J. Dose response and factors related to interstitial pneumonitis after bone marrow transplant. Int J Radiat Oncol Biol Phys. 2005;63:S0360-S3016. Kim DY, Kim IH, Yoon SS, Kang HJ, Shin HY, Kang HC. Effect of dose rate on pulmonary toxicity in patients with hematolymphoid malignancies undergoing total body irradiation. Radiat Oncol. 2018;13:180. https://doi.org/10.1186/s13014- 018-1116-9 Abugideiri M, Nanda RH, Butker C, et al. Factors influencing pulmonary toxicity in children undergoing allogeneic hematopoietic stem cell transplantation in the setting of total body irradiationbased myeloablative conditioning. Int J Radiat Oncol Biol Phys. 2016;94:349-359. https://doi.org/10.1016/j.ijrobp.2015.10.054 Wong JYC, Filippi AR, Dabaja BS, Yahalom J, Specht L. Total body irradiation: guidelines from the International Lymphoma Radiation Oncology Group (ILROG). Int J Radiat Oncol Biol Phys. 2018;101:521529. https://doi.org/10.1016/j.ijrobp.2018.04.071 Corvò R, Zeverino M, Vagge S, et al. Helical tomotherapy targeting total bone marrow after total body irradiation for patients with relapsed acute leukemia undergoing an allogeneic stem cell transplant. Radiother Oncol. 2011;98:382-386. https://doi.org/10.1016/j. radonc.2011.01.016 Perkey E, Maillard I. New insights into graft-versus-host disease and graft rejection. Annu Rev Pathol. 2018;13:219-245. https://doi. org/10.1146/annurev-pathol- 020117- 043720 Nalle SC, Zuo L, Ong MLDM, et al. Graft-versus-host disease propagation depends on increased intestinal epithelial tight junction permeability. J Clin Investig. 2019;129:902-914. https://doi. org/10.1172/JCI98554 Ljungman P, Bregni M, Brune M, et al. Allogeneic and autologous transplantation for haematological diseases, solid tumours and immune disorders: current practice in Europe 2009. Bone Marrow Transplant. 2010;45:219-234. https://doi.org/10.1038/ bmt.2009.141 Ringden O, Labopin M, Sadeghi B, et al. What is the outcome in patients with acute leukaemia who survive severe acute graftversus-host disease? J Intern Med. 2018;283:166-177. https://doi. org/10.1111/joim.12695 Paix A, Antoni D, Waissi W, et al. Total body irradiation in allogeneic bone marrow transplantation conditioning regimens: a review. Crit Rev Oncol Hematol. 2018;123:138-148. https://doi.org/10.1016/j. critrevonc.2018.01.011 Giralt S, Thall PF, Khouri I, et al. Melphalan and purine analogcontaining preparative regimens: reduced-intensity conditioning for patients with hematologic malignancies undergoing allogeneic progenitor cell transplantation. Blood. 2001;97:631-637. https:// doi.org/10.1182/blood.v97.3.631 Giralt S, Aleman A, Anagnostopoulos A, et al. Fludarabine/melphalan conditioning for allogeneic transplantation in patients with multiple myeloma. Bone Marrow Transplant. 2002;30:367-373. https://doi.org/10.1038/sj.bmt.1703652 Ritchie DS, Morton J, Szer J, et al. Graft-versus-host disease, donor chimerism, and organ toxicity in stem cell transplantation after conditioning with fludarabine and melphalan. Biol Blood Marrow Transplant. 2003;9:435- 442. de Lima M, Anagnostopoulos A, Munsell M, et al. Nonablative versus reduced-intensity conditioning regimens in the treatment of acute myeloid leukemia and high-risk myelodysplastic syndrome: dose is relevant for long-term disease control after allogeneic

HARALDSSON et AL.

hematopoietic stem cell transplantation. Blood. 2004;104:865-872. https://doi.org/10.1182/blood-2003-11-3750 56. Kyle RA, Rajkumar SV. Criteria for diagnosis, staging, risk stratification and response assessment of multiple myeloma. Leukemia. 2009;23:3-9. https://doi.org/10.1038/leu.2008.291 57. Hochhaus A, Baccarani M, Silver RT, et al. European LeukemiaNet 2020 recommendations for treating chronic myeloid leukemia. Leukemia. 2020;34:966-984. https://doi.org/10.1038/s4137 5- 020- 0776-2

How to cite this article: Haraldsson A, Wichert S, Engström PE, et al. Organ sparing total marrow irradiation compared to total body irradiation prior to allogeneic stem cell transplantation. Eur J Haematol. 2021;00:1–15. https://doi. org/10.1111/ejh.13675

S U P P O R T I N G I N FO R M AT I O N Additional supporting information may be found online in the Supporting Information section.

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3D treatment planning on helical TomoTherapy

ARTICLE IN PRESS Medical Dosimetry ■■ (2018) ■■–■■

Medical Dosimetry j o u r n a l h o m e p a g e : w w w. m e d d o s . o r g

Dosimetry Contribution:

3D treatment planning on helical tomotherapy delivery system Cheng B. Saw, PhD,a Leah Katz, MD,b Carol Gillette, CMD,b and Lawrence Koutcher, MDb Northeast Radiation Oncology Centers (NROC), Dunmore, PA 18512; and bHudson Valley Radiation Oncology Associates, Cortlandt Manor, NY 10567

A R T I C L E

I N F O

Article history:

Received 18 February 2018 Accepted 19 February 2018 Keywords: Intensity-modulated radiation

therapy Radiosurgery Stereotactic body radiation therapy Stereotactic ablative radiation therapy Tomotherapy

A B S T R A C T

The helical tomotherapy is a technologically advanced radiation dose delivery system designed to perform intensity-modulated radiation therapy (IMRT). It is mechanistically unique, based on a small 6-MV linear accelerator mounted on a ring gantry that rotates around the patient while the patient moves through a bore, ultimately yielding a helical path of radiation dose delivery. The helical pattern of dose delivery differentiated tomotherapy from other contemporary radiation therapy systems at the time of its inception. The accompanying 3-dimensional (3D) treatment planning system has been developed to solely support this speciﬁc type of dose delivery system. The treatment planning system has 2 modules identiﬁed as TomoHelical and TomoDirect to perform IMRT and conformal radiation therapy, respectively. The focus of this work within the scope of this special issue on 3D treatment planning systems is to assess the use of planning tools to generate treatment plans for helical tomotherapy. Clinical examples are used throughout to demonstrate the quality and differences of various clinical scenarios planned with tomotherapy. © 2018 American Association of Medical Dosimetrists.

Introduction The helical tomotherapy system offers an integrated approach to radiation therapy, combining imaging and treatment delivery to precisely target a wide variety of pathology. 1 From the historical point of view, helical tomotherapy was conceived to optimally implement intensity-modulated radiation therapy (IMRT) treatment technique in the clinic.2 At that time, the concerns of the radiation oncology community were the ability to deliver a very

Reprint requests to Cheng B Saw, PhD, Northeast Radiation Oncology Centers, 1110 Meade Street, Dunmore, PA 18512. E-mail: cheng.saw@aol.com

targeted dose, maximally spare surrounding sensitive structures, concurrent veriﬁcation of beam shape and patient position, and of course, patient safety, which entail preventing patient collision with the dynamic therapy treatment unit. The solution to these priorities and concerns was the introduction of the commercial helical tomotherapy delivery system by Tomotherapy, Inc. (Madison, WI) in 2003.3 Although helical tomotherapy was initially designed with IMRT intent, it has evolved to include 3-dimensional (3D) conformal radiation therapy. The design of helical tomotherapy is unique compared with other contemporary radiation therapy machines, and its accompanying treatment planning system has been developed speciﬁcally to support and enhance the helical tomotherapy treatment delivery capabilities. The focus of this work within the scope of this special

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issue on 3D treatment planning is to assess the current use of the helical tomotherapy system, as well as explore the exciting future it holds.

Table 1 Helical tomotherapy nomenclature Delivery mode option

Parameters

TomoHelical

Methods and Materials The helical tomotherapy delivery system consists of a small 6-MV linear accelerator mounted on a ring gantry that rotates isocentrically around the patient. As the patient moves through the bore, a helical path of radiation dose delivery is produced, as seen in Fig. 1. Although it looks like a helical computed tomography (CT) scanner on the outside, the beam intensity is modulated using an internal binary collimator. The specially designed binary collimator has 2 banks, and each bank has 64 leaves with a beamlet size of 0.626 cm, giving a total field width of 40 cm. The binary collimator is computer controlled with the leaves sliding in and out of the slit aperture to provide temporal beam modulation. The jaw settings create a beam width of either 1.0, 2.5, or 5.0 cm. Helical tomotherapy now allows movable jaws to optimize treatment planning, which is a significant improvement from the older, fixed jaw model.4 The helical tomotherapy unit also encompasses megavoltage CT imaging to provide imageguided radiation therapy capability for accurate patient setup. As a technologically advanced dose delivery system, helical tomotherapy system has the network connectivity for the seamless transfer of electronic data. After the patient is immobilized and simulated, the CT image dataset on the patient is transferred to a contouring station. The initial stage of contouring typically involves image fusion with diagnostic imaging, and more commonly with positron emission tomography or magnetic resonance imaging for enhanced tumor visualization. After the image fusion, target volumes and organs at risk are delineated by the radiation oncologist, whereas pseudostructures, such as rings around the

Fig. 1. Helical tomotherapy unit. (Color version of ﬁgure is available online.)

Plan mode

IMRT/3DCRT

Field width

5.0 cm 2.5 cm

Jaw mode

1.0 cm Static/dynamic

Modulating factor Pitch Dose constraints and penalties TomoDirect Plan mode Field width

Jaw mode Gantry angles

IMRT/3DCRT 5.0 cm 2.5 cm 1.0 cm Static/dynamic 2-12

3DCRT, 3D conformal radiation therapy.

target volumes are drawn by the dosimetrist to aid in performing inverse planning. The CT image and structure dataset are exported to the TomoHD treatment planning system (version 5.1.1.6). Initially, the origin and the laser system are identified and placed on the CT image dataset, the CT couch is then replaced with the helical tomotherapy couch, and the prescribed dose is assigned to the target volume at a defined percent level with a set number of fractions. Lastly, constraints are placed on organs at risk and pseudostructures. At this juncture, the treatment planning system provides 2 delivery mode options to choose, the TomoHelical or the TomoDirect. TomoHelical treatment technique offers the helical mode of radiation dose delivery for the IMRT treatment method. The dose delivery involves multiple rotations as the patient translates or moves through the bore of the system and the continuous high dose rate allows for shorter treatment times. Besides the dose prescription, there are 3 important machine parameters that must be manually entered: field width, pitch, and the modulation factor. The field width options are 5.0, 2.5, and 1.0 cm, and the selected parameter depends on the length of the target volume, the shape of the target volume, and the anticipated treatment time. Generally, the larger field width is used for longer target volumes in the inferior to superior direction in the effort to reduce treatment time. The pitch refers to the relationship of the distance the couch travels per rotation to the field width. The modulation factor refers to the maximum leaf opening time to the average leaf opening time of all the nonzero leaf opening times. These various relationships must be matched for a prescribed dose to avoid regular intervals of hot spots that would otherwise be present, known as the “zebra” effect. The input parameters are listed in Table 1. Inverse-planning dose algorithm is used to generate the IMRT treatment plan. At this

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time, the dose constraints and their respective penalties are assigned to both the target volume and structure constraints. Treatment planning is then initiated, and the iterative process of optimization is performed. After a certain number of iterations, the penalties are adjusted interactively to “push” or modify the dose patterns. The interactive adjustment is made by first hitting the pause button to halt the dose algorithm calculation, adjusting the parameters, and then continue. The decision to make the change can be deduced from the isodose pattern, which is updated regularly on the screen. After a certain number of iterations, the isodose pattern plateaus, indicating that the dose algorithm calculation reaches a cost minimum or near a minimum. The process is repeated until an acceptable plan is obtained. The acceptability of the treatment plan is evaluated to ensure that the plan meets the target conformity requirements and normal tissue dose-volume constraints. TomoDirect treatment technique offers the discrete angle, nonrotational option for 3D conformal radiation therapy. TomoDirect permits the use of 2 to 12 user defined beam angles directed at the target, and the leaves of the multileaf collimation system extend or retract to enable the field to conform to the projected target volume. The delivery involves the movement of the leaves of the multileaf collimation system as the patient translates or moves into the radiation therapy machine. The delivery quality assurance is an essential component of the dose delivery systems. It involves the measurements of the patient treatment fluence directed at a phantom and compared against the dose distribution generated by the treatment planning. At our institution, this is performed on the Delta4 3D phantom for physical measurements.5 The dose planes can be exported to the vendor’s software for isodose distribution comparison with the measurements. In addition, an absolute point dose measurement in the “Cheese” or delivery quality assurance TomoPhantom can also be taken. Results Figure 2 shows an axial view of a TomoTherapy IMRT head and neck case. As pictured, isodose lines, targets, and organs at risk appear as they would within the helical tomotherapy treatment planning system. The major planes are typically used in this treatment planning system for evaluation, and the plane of interest can be rotated into the largest window to better examine the plan’s isodose pattern and volume conformality. As seen in Fig. 2, the axial view is displayed. The isodose levels can be displayed in isodose lines or dose color wash, as seen in Fig. 2A and B, respectively. The choice of isodose line display vs dose color wash depends on the radiation oncologist’s preference and the clinical site, as some anatomical sites and disease contexts lend themselves better

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to 1 display over another. The color wash display is particularly useful for head and neck plan evaluation, as there are often several dose levels used. Figure 3 shows the dosevolume histogram for this head and neck case, and the specific values can be directly obtained by placing the cursor over the organs at risk of interest line. The use of IMRT in general has become the standard of care for most head and neck patients, as the sparing of parotid structures and avoidance of xerostomia have been found to be superior. In that vein, the use of TomoTherapy for head and neck patients has allowed for dose intensification to gross tumor and areas at high risk of microscopic spread while sparing adjacent, normal tissue structures. The intrinsic complexity of head and neck anatomy and the relatively small areas over which sharp dose gradients are needed, lends itself very well to the dose modulating capabilities of TomoTherapy. Additionally, as many radiosensitive head and neck tumors recede, TomoTherapy’s integrated imaging system allows for radiation oncologists to know when they need to resimulate and replan, and be assured on a daily basis that the patient are setting up correctly. Although there is yet to be a prospective randomized control trial evaluating TomoTherapy vs other IMRT treatment planning systems, retrospective series have shown excellent local control rates and toxicity profiles with TomoTherapy. Modern day radiation oncologists regard TomoTherapy IMRT planning for complex head and neck plans as an excellent option. Figure 4 shows a prone breast treatment plan indicating that the bore hole is sufficiently large to accommodate this widely used type of treatment technique. Breast tangents are dosimetrically mimicked through the use of the TomoDirect treatment planning modality, which takes advantage of autoselection and adjustment of width and length based on the drawn target volume. Prone breast positioning allows for maximal lung sparing and in some women with specific anatomy, the heart and left anterior descending artery as well. TomoTherapy treatment planning is able to integrate this setup into its broad list of capabilities, and although it has been criticized in the past for spreading more low dose across a larger volume on normal tissue for prone positioning, its ability to maximally avoid heart and lungs still makes it an excellent modality for these women. By its operational principles, helical tomotherapy is well suited to perform focal radiation, either in the form of stereotactic radiosurgery (SRS) or stereotactic body radiation therapy (SBRT).6-8 Focal irradiation broadly refers to treatment technique where multiple beams are directed at a small, discrete target to deliver a very high dose with sharp dose fall off. Helical tomotherapy delivers radiation systematically from all directions, in complete rotations, satisfying the dosimetric criteria of focal irradiation. Because of the increased

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Fig. 2. (A) A bilateral neck treatment plan in which isodose lines are displayed for a head and neck patient using TomoHelical delivery mode. (B) Same plan as in A but in color wash display. (Color version of ﬁgure is available online.)

number of degrees of freedom offered by TomoTherapy, an extremely conformal isodose pattern is produced. TomoTherapy’s capabilities are very well suited to lung SBRT, which has been shown to have a far superior local control rate compared with the traditionally fractionated external beam radiation, and is an excellent option for medically

inoperable patients. As such, the use of SBRT has grown over the past decade and continues to be widely used. SBRT allows for excellent normal structure sparing, such as ribs, chest wall, esophagus, heart, skin, and spinal cord. The ability of TomoTherapy to avoid normal structures and spread out surface skin dose makes it an excellent modality

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Fig. 3. The DVH for the head and neck treatment plan in Fig. 2. DVH, dose-volume histogram. (Color version of ﬁgure is available online.)

to provide SBRT.9 Figure 5 illustrated a posterior pleural lesion targeted by SBRT using TomoTherapy IMRT treatment planning. Note the excellent dose optimization around the adjacent spinal cord. Lastly, SBRT for centrally located lung tumors have often been excluded, for fear of tracheal/ bronchial toxicity; however, through TomoTherapy, many of these lesions may be safely treated. In this way, TomoTherapy helps expand treatment options for many lung cancer

patients. To summarize, the innate conformal delivery exhibited by TomoTherapy IMRT, meticulous setup using TomoTherapy’s onboard megavoltage CT system, and evolving respiratory gating techniques will only continue to render TomoTherapy an excellent delivery system for lung SBRT. In addition to SBRT, SRS in the treatment of brain metastases has become increasingly popular. SRS offers patients an excellent treatment alternative to whole brain radiation,

Fig. 4. TomoDirect treatment plan for prone whole-breast irradiation. (Color version of ﬁgure is available online.)

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Fig. 5. A peripheral lung lesion is targeted by SBRT using TomoTherapy IMRT. Note the excellent spinal cord sparing with this treatment planning approach. (Color version of ﬁgure is available online.)

which results in signiﬁcant cognitive decline. In addition, it is far less invasive than surgical resection. TomoTherapy is compatible with SRS, as it is fast, achieves excellent conformity indices, spares normal brain tissue, is steady given the

ring gantry system, and requires no additional hardware. A typical treatment plan is shown in Fig. 6. The vast utility and capabilities of TomoTherapy include prostate cancer treatment, both for deﬁnitive prostate/

Fig. 6. Axial view of the SRS plan for the treatment of brain metastases. Note the excellent dose fall off for each treated lesion. (Color version of ﬁgure is available online.)

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Fig. 7. An axial view of a TomoTherapy treatment plan for the treatment of prostate cancer. (Color version of ﬁgure is available online.)

seminal vesicle treatment only, (see Fig. 7) as well as prostate/ seminal vesicle plus pelvic lymph node treatment for patients with more advanced disease (see Fig. 7). The treatment of pelvic lymph nodes and prostate illustrates one of the strengths of TomoTherapy, as the target volume is an extensive planning target volume (PTV) in the superior to inferior axis. Note the isodose pattern made concave contours sparing the bladder and rectum (Fig. 8). Additionally, TomoTherapy allows for the treatment of prostate bed status post radical prostatectomy. Given the intrinsic movement of the prostate caused by bladder and rectum filling, the ability to image the patient directly before each treatment assures that the desired target always remains within the treated PTV while avoiding unwanted dose to the bladder and rectum. Discussion Patients undergoing radiation therapy on the helical tomotherapy machine follows the procedures for the IMRT treatments: (1) immobilization and CT simulation, (2) treatment planning, (3) plan verification, (4) patient setup and target localization, and (5) dose delivery. This is the typical workflow of a modern radiation oncology facility. As a uniquely design dose delivery system on a ring gantry, the

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tight tolerances for IMRT are consistent with the requirements for focal irradiation.10,11 There is no additional hardware needed to perform SRS and SBRT using this dose delivery system. Also, the same image-guidance system is used for both focal irradiation and IMRT. The workflow of IMRT can be implemented for SRS and SBRT on the helical tomotherapy unlike being performed using medical linear accelerators or those done in the past, which require resources and quality assurance to ensure patient physical safety. It is also not a whole day event, which is typically associated with SRS procedure. Helical tomotherapy offers some unique benefits as a dose delivery system. This includes the ability to treat multiple lesions in a session, which accelerates the treatment compared with other treatment modalities.12 By its very nature of rotational and translational dose delivery, the system is highly efficient in the treatment of extended length, for example, in total body irradiation.13 With the numerous degrees of freedom (beam angles), the treatment plan can yield a highly conformal treatment plan, in particular to irregular targets as illustrated in these examples. TomoTherapy Radixact is the latest dose delivery system offered by Accuray, Inc. (Sunnyvale, CA)14 The machine output is higher, at 1000 MU per minute. The gantry rotation is also faster, at 10 revolutions per minute for imaging acquisition.

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Fig. 8. Axial view of a pelvic lymph node plus prostate treatment. Note the rectal and bladder sparing. (Color version of ﬁgure is available online.)

There is an available integrated data management system serving as a central management of data storage and processing for multiple dose delivery systems. The system allows for remote review and sign-off of reports and DICOM (Digital Imaging and Communications in Medicine) import/export and interfaces with other oncology information system. The treatment planning system, Accuray Precision, offers (1) the ability to plan for multiple Radixact dose delivery systems, (2) remote view and approval of plans, (3) autosegmentation, and (4) multimodality image support. It also has PreciseART adaptive radiation therapy and PreciseXRT option. Conclusions The helical tomotherapy system offers an integrated approach to radiation therapy, combining imaging and treatment delivery to precisely target a wide variety of cancers. The treatment planning system provides the option of 2 dose delivery modes, the TomoHelical and the TomoDirect. These 2 dose delivery modes enable TomoTherapy to treat a wide array of tumors, including advanced techniques such as SRS and SBRT. By its operational principles, helical tomotherapy is also effective in the treatment of extended ﬁelds, as with total body irradiation or in treating 2 PTVs far from each other.

References 1. Accuray Incorporated. Tomotherapy products. Available at: http:// www.tomotherapy.com/. Accessed March 18, 2018. 2. Mackie, T.R.; Holmes, T.; Swerdloff, S.; et al. Tomotherapy: A new concept for the delivery of dynamic conformal radiotherapy. Med. Phys. 20:1709–19; 1993. 3. Mackie, T.R. History of tomotherapy. Phys. Med. Biol. 51:R427–53; 2006. 4. Rudofsky, L.; Aynsley, E.; Beck, S.; et al. Lung and liver SBRT using helical tomotherapy—a dosimetric comparison of ﬁxed jaw and dynamic jaw delivery. J. Appl. Clin. Med. Phys. 15:114–21; 2014. 5. Scandidos. Delta4 family products. Available at: http:// delta4family.com/. Accessed March 18, 2018. 6. Saw, C.B.; Gillette, C.; Peters, C.A.; et al. Clinical implementation of radiosurgery using helical tomotherapy unit. Med. Dosim. 2018. in press. 7. Chi, A.; Jang, S.Y.; Welsh, J.S.; et al. Feasibility of helical tomotherapy in stereotactic body radiation therapy for centrally located early stage non-small-cell lung cancer or lung metastases. Int. J. Radiat. Oncol. Biol. Phys. 81:856–62; 2011. 8. Sterzing, F.; Hauswald, H.; Uhl, M.; et al. Spinal cord sparing reirradiation with helical tomotherapy. Cancer 116:3961–8; 2010. 9. Hoppe, B.S.; Laser, B.; Kowalski, A.V.; et al. Acute skin toxicity following stereotactic body radiation therapy for stage I non-smallcell lung cancer. Who’s at risk? Int. J. Radiat. Oncol. Biol. Phys. 72:1283–6; 2008. 10. Langen, K.M.; Papanikolaou, N.; Balog, J.; et al. QA for helical tomotherapy: Report of the AAPM Task Group 148. Med. Phys. 37:4817–53; 2010.

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11. Benedict, S.H.; Yenice, K.M.; Followill, D.; et al. Stereotactic body radiation therapy: The report of AAPM Task Group 101. Med. Phys. 37:4078–101; 2010. 12. Saw, C.B.; Battin, F.; McKeague, J.; et al. Dose planning management of patients undergoing salvage whole brain radiation therapy after radiosurgery. Med. Dosim. 41:277–80; 2016.

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13. Gruen, A.; Ebell, W.; Wlodarczyk, W.; et al. Total body irradiation (TBI) using helical tomotherapy in children and young adults undergoing stem cell transplantation. Radiat. Oncol. 8:92; 2013. 14. Accuray Incorporated. Radixact products. Available at: http:// www.accuray.com/product/radixact. Accessed March 18, 2018.

Delivered dose can be a better predictor of rectal toxicity than planned dose in prostate radiotherapy Radiotherapy and Oncology xxx (2017) xxx–xxx

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Original article

Delivered dose can be a better predictor of rectal toxicity than planned dose in prostate radiotherapy L.E.A. Shelley a,b,c,⇑, J.E. Scaife a,d, M. Romanchikova a,b, K. Harrison a,f, J.R. Forman a,e, A.M. Bates a,d, D.J. Noble a,d, R. Jena a,d, M.A. Parker a,f, M.P.F. Sutcliffe a,c, S.J. Thomas a,b, N.G. Burnet a,d a Cambridge University Hospitals NHS Foundation Trust, Department of Oncology; b Department of Medical Physics and Clinical Engineering, Cambridge University Hospitals NHS Foundation Trust; c Department of Engineering, University of Cambridge; d Department of Oncology, University of Cambridge; e Cambridge Clinical Trials Unit, Cambridge University Hospitals NHS Foundation Trust; and f Cavendish Laboratory, University of Cambridge, United Kingdom

a r t i c l e

i n f o

Article history: Received 13 December 2016 Received in revised form 3 April 2017 Accepted 5 April 2017 Available online xxxx Keywords: Rectal toxicity VoxTox Dose–surface maps Delivered dose Prostate radiotherapy

a b s t r a c t Background and purpose: For the first time, delivered dose to the rectum has been calculated and accumulated throughout the course of prostate radiotherapy using megavoltage computed tomography (MVCT) image guidance scans. Dosimetric parameters were linked with toxicity to test the hypothesis that delivered dose is a stronger predictor of toxicity than planned dose. Material and methods: Dose–surface maps (DSMs) of the rectal wall were automatically generated from daily MVCT scans for 109 patients within the VoxTox research programme. Accumulated-DSMs, representing total delivered dose, and planned-DSMs, from planning CT data, were parametrised using Equivalent Uniform Dose (EUD) and ‘DSM dose-width’, the lateral dimension of an ellipse fitted to a discrete isodose cluster. Associations with 6 toxicity endpoints were assessed using receiver operator characteristic curve analysis. Results: For rectal bleeding, the area under the curve (AUC) was greater for accumulated dose than planned dose for DSM dose-widths up to 70 Gy. Accumulated 65 Gy DSM dose-width produced the strongest spatial correlation (AUC 0.664), while accumulated EUD generated the largest AUC overall (0.682). For proctitis, accumulated EUD was the only reportable predictor (AUC 0.673). Accumulated EUD was systematically lower than planned EUD. Conclusions: Dosimetric parameters extracted from accumulated DSMs have demonstrated stronger correlations with rectal bleeding and proctitis, than planned DSMs. 2017 The Authors. Published by Elsevier Ireland Ltd. Radiotherapy and Oncology xxx (2017) xxx–xxx This is an open access article under the CC BY license (http://creativecommons.org/licenses/by/4.0/).

In prostate radiotherapy, the correlation between dose to rectum and toxicity has been the focus of many research studies [1– 7]. The rectum is one of the dose-limiting organs when planning intensity-modulated radiotherapy (IMRT) to the prostate due to the risk of radiation-induced adverse effects. Modern systems for inverse IMRT treatment planning iteratively seek to achieve an optimal plan, delivering maximal dose to the tumour volume and minimal dose to healthy organs. Current normal tissue complication probability (NTCP) models and conventional treatment planning constraints are based upon dose–volume histogram (DVH) data to minimise the risk of toxicity. With ever improving disease control [8,9] and survival rates [10], post-treatment quality of life becomes an increasingly significant consideration during treatment planning, alongside target coverage. ⇑ Corresponding author at: Cancer Research UK VoxTox Research Group, Cambridge University Hospitals NHS Foundation Trust, Department of Oncology, Addenbrooke’s Hospital, Cambridge CB2 0QQ, United Kingdom. E-mail address: ls698@cam.ac.uk (L.E.A. Shelley).

The DVH-based approach to radiotherapy treatment planning has been criticised for lacking in spatial dose consideration [2]. Consequently, accumulation of DVHs is not dosimetrically representative and results in false overestimations of dose. A review by Landoni et al. [11] emphasises the need to assess associations between spatial dose patterns and late toxicity [12], particularly as results may reveal inhomogeneous intra-organ radiosensitivities. Several groups have explored alternative approaches for parametrisation of dose distributions in order to establish links with toxicity. Methods have included dose–surface histograms [1,5,13,14], dose–surface maps [1,5,15], dose–line histograms [14], principal component-based pattern analysis [16], and voxelbased approaches for identifying rectal subregions [2,6,7]. These studies have been limited in their analysis by the availability of planned dose data only, based on a single anatomical snapshot in time. A common recommendation in the literature has been the need to establish dose-toxicity models based on delivered dose [17]. However, this has proven technically challenging to date due to

http://dx.doi.org/10.1016/j.radonc.2017.04.008 0167-8140/ 2017 The Authors. Published by Elsevier Ireland Ltd. This is an open access article under the CC BY license (http://creativecommons.org/licenses/by/4.0/).

Please cite this article in press as: Shelley LEA et al. Delivered dose can be a better predictor of rectal toxicity than planned dose in prostate radiotherapy. Radiother Oncol (2017), http://dx.doi.org/10.1016/j.radonc.2017.04.008

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hardware and software limitations. These challenges have been addressed within the VoxTox Research Programme [18] where contours generated from on-treatment megavoltage computed tomography (MVCT) image guidance scans are used to calculate daily delivered dose. This approach has made it possible to account for the effect of interfractional anatomical variation. Total delivered dose can be estimated by accumulating daily delivered dose throughout the course of radiotherapy. Studies by the VoxTox group have demonstrated that the rectum moves more than previously predicted based on estimates from prostate motion [19], and that planned dose is not equal to delivered dose [20]. The dose–surface map (DSM) approach has been implemented within this study as a solution enabling meaningful accumulation and conservation of geometric information, an advantage over the DVH methodology. The concept of accumulating DSMs to estimate total delivered dose has been applied previously for the bladder [13]. By extracting spatial parameters from DSMs of delivered dose, and linking with the archive of patient follow-up data available within VoxTox, it was hypothesised that stronger correlations could be established with late toxicity than previously achievable using planned dose alone. Ultimately, improved dose-toxicity modelling based on delivered dose could facilitate real-time in silico prediction of NTCP within the clinical pathway. Material and methods VoxTox study design & patient information The VoxTox research programme is an observational study linking radiation dose to toxicity outcomes [18,20]. It received approval from the National Research Ethics Service (NRES) Committee East of England (13/EE/0008) in February 2013 and is part of the UK Clinical Research Network Study Portfolio (UK CRN ID 13716). One hundred and nine prostate cancer patients were selected from the discovery cohort of the VoxTox research programme [18]. This cohort (Table 1) comprised patients treated prior to the formal collection of baseline data, but for whom prospective follow-up data of at least 2 years were available (median 4 years). Early VoxTox patients were selected based on expected benefit from IMRT rather than conventional 3D conformal radiotherapy. Patients in this study were included on the basis of availability of pre-existing toxicity status from clinical notes, or no reported toxicity, and was limited to those prescribed IMRT to a dose of 74 Gy in 37 fractions, the standard of care in the UK at the time [21]. VoxTox patients are treated with TomoTherapy (Accuray, Sunnyvale, CA). Manual contouring of the anatomy on the kilovoltage computed tomography (kVCT) planning scan was performed according to local procedures [19], adapted from clinical trials. Daily MVCT image guidance scans were acquired immediately prior to treatment delivery for the purposes of online target localisation [22]. Following our department protocol, scans were inspected for rectal dilation and if deemed excessive, remedial action was taken prior to delivery of radiation therapy [23]. Dose–surface map construction & dose accumulation Within the VoxTox research programme, MVCT scans are multifunctional; primarily for the purpose of routine image guidance, they also provide a platform for calculation of delivered dose. The rectum was identified on each MVCT image series using an in-house autocontouring system based on a customised ChanVese segmentation algorithm [24]. Delivered dose was independently calculated using a locally implemented ray-tracing algorithm [25,26] and the rectal contour-of-the-day, accounting for inter-fraction motion. Automation and integration of dose calcula-

Table 1 Baseline characteristics for the 109 VoxTox participants. Prescribed dose to the prostate was 74 Gy in 37 fractions over 7.5 weeks. All patients were treated with androgen deprivation therapy. IBD = inflammatory bowel disease, IQR = interquartile range, PSA = prostate-specific antigen, SD = standard deviation. Clinical data for VoxTox patients (n = 109) Age, years Median (IQR) Range

68 (64–71) 51–80

T stage, n (%) T1A/T1B/T1C/T1X T2A/T2B/T2C/T2X T3A/T3B/T3X T4 Not known

24 (22%) 34 (31%) 45 (41%) 0 6 (6%)

Gleason score, n (%) 66 7 P8 Not known

23 (21%) 44 (40%) 39 (36%) 3 (3%)

PSA (ng/ml) Median (IQR) Mean (SD) Not known

11 (7–20) 20 (30) 3 (3%)

Clinical history Diabetes Hypertension IBD or diverticular disease Previous pelvic surgery Haemorrhoids past 12 months Any previous TURP Not known

10 (9%) 35 (32%) 7 (6%) 7 (6%) 3 (3%) 9 (8%) 9 (8%)

tion and contouring systems were essential for large-scale processing of the 4142 scans in this study. Planned and daily DSMs were generated based on algorithms described by Buettner et al. [1] and Murray et al. [15]. The rectal wall was considered the structure of interest, and was treated as a tubular surface rather than a volume. Contours were virtually ‘cut’ along the superior–inferior axis and ‘unfolded’ to a twodimensional plane. The ‘cutting point’ was identified as the point on the contour surface directly posterior to the centre of mass of the rectal outline, on each CT slice [20]. The height of the planned-DSM was defined by the number of slices of the manually contoured rectum on the kV planning scan (slice thickness 3 mm). The circumference of the rectal contour on each slice was normalised such that the unfolded width of the planned-DSM was equal to the height. Daily delivered DSMs calculated from the image-guidance MVCT scans (slice thickness 6 mm) were normalised to the same width as the planned-DSM but were restricted in height by the field of view (FOV), resulting in a shorter DSM, as shown in Fig. 1. Rectal DSMs were calculated for each treatment fraction, and corrected for daily couch shifts. For the purposes of dose accumulation, any ‘missing’ dose data cropped by the restricted FOV superiorly or inferiorly were substituted from the planned-DSM [20] in order to maintain common dimensions between final accumulated-DSM and planned-DSM. The final accumulated-DSM was resampled to match the 3 mm resolution of the plannedDSM, producing an easily comparable and interpretable spatial representation of total delivered dose to the rectal wall throughout the course of prostate radiotherapy [25] (illustrated in Fig. 1). The use of planned-DSM data as a surrogate beyond the boundaries of the MVCT FOV was considered an acceptable estimate under the assumption that the relative anatomical motion of the rectum becomes more confined by surrounding musculature as the distance from the prostate increases [20]. However, this could have reduced potential differences between planned and accumulated dose, and was a limitation of the analysis.

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Fig. 1. Generation of planned, daily and accumulated dose surface maps.

Dose parameters & clinical endpoints Dose was parametrised from DSMs using two methods implemented in MATLAB (MathWorks , Natick, MA): 1. Calculation of Equivalent Uniform Dose (EUD) 2. Fitting of DSM ‘dose-widths’ to discrete isodose clusters EUD reduces the dose information extracted from the DSMs to a single generalised value which allows comparison between inhomogeneous dose distributions [27]. An ‘a’ value of 11.11 was used in the EUD calculation [28]. Spatial dose information was generated by reproducing Buettner’s ellipse-fitting method [1], reporting the most significant dose quantifier, the lateral extent, termed here the ‘DSM dose-width’. For a given isodose level, a binary image was created from the DSM by assigning a pixel value of 1 to doses greater than or equal to the nominated isodose, with lower doses assigned a value of 0. An ellipse was then fitted to the largest central cluster. The maximum lateral extent of the ellipse was projected onto the DSM axis, accounting for any rotation with respect to the DSM coordinate system. The resulting DSM dose-width, expressed as a the percentage of total normalised DSM width, allowed parametrisation of the geometrical dose distribution which would have been masked using a DVH approach. For each patient, EUD and DSM dose-widths for isodose levels of 30, 40, 50, 60, 65, and 70 Gy were calculated from planned-DSM and accumulated-DSM. Doses less than 30 Gy were not included as DSM dose-width results became dominated by extrapolated values greater than 100%, indicating that the entire rectal circumference was receiving less than or equal to the selected isodose level. This was identified as a limitation of the ellipse fitting method when seeking to analyse low dose toxicity correlations. Doses greater than 70 Gy were also excluded from toxicity analyses due to the increasing frequency of 0% DSM dose-widths, indicating that doses greater than or equal to the selected isodose level were not received by the rectal wall. Only 49/109 patients recorded a non-zero result from accumulated DSM at 74 Gy, reducing to 10/109 at 75 Gy, compared with 106/109 and 64/109 respectively from planned-DSM. It was identified that a 0% DSM result could conceal information leading to misinterpretation of data when performing AUC calculations so results at these isodose levels were not reported. Despite these restriction, the dose levels included within this study incorporate the 39–61 Gy range at which Buettner [1] determined significant correlations between lateral extent and toxicity.

Study specific clinical reporting forms were developed for robust collection of toxicity data, and raw data were used to populate recognised systems, including: Common Terminology Criteria for Adverse Events (CTCAE) v4.03 [29], Late Effects of Normal Tissues/Subjective, Objective, Management, Analytic (LENT SOMA) scores [30]; Radiation Therapy Oncology Group (RTOG) grading system [31]; University of California, Los Angeles, Prostate Cancer Index (UCLA-PCI) questionnaire [32]. Receiver Operator Characteristic (ROC) curves (Fig. 2) were generated using SPSS (IBM 23.0.0.2) to evaluate the link between dosimetric parameters extracted from planned and accumulated DSMs, and the six most prevalent clinical endpoints, listed in Table 2. The mean area under the curve (AUC), with associated upper and lower 95% confidence intervals (CIs), was calculated for each ROC curve as a measure of the level of association between dosimetric parameter and toxicity. An ideal correlation would have an AUC of 1. Results were reported for dosimetric parameters with AUC P 0.6 and lower 95% CI P 0.5, considered statistically significant by Gulliford et al. [33]. Results Rectal bleeding Twenty-eight patients reported rectal bleeding CTCAE PGrade 1, which was equivalent to PGrade 2 (LENT SOMA). The AUC was greater for all accumulated DSM dose-widths than planned DSM dose-widths up to 70 Gy (Table 3). At 30, 40 and 60 Gy, the lower 95% CI boundaries for the planned DSM dose-widths extended below 0.5, but remained above this threshold for the corresponding accumulated DSM dose-widths (Fig. 3a). The strongest spatial predictor of rectal bleeding was accumulated 65 Gy DSM dose-width (AUC 0.664), and the largest difference between planned and accumulated DSM dose widths was at 60 Gy (AUC difference 0.035). Overall, for both planned and accumulated DSMs, the AUC was greater for EUD than from respective DSM dose-widths, with the strongest predictor of rectal bleeding being accumulated-EUD (AUC 0.682). Proctitis The RTOG definition of proctitis considers urgency and frequency of bowel movements, as well as the presence of rectal mucous/blood. Eighteen patients reported RTOG proctitis PGrade

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Correlating delivered dose with toxicity Table 2 Clinical endpoints, scoring systems and incidence rates of the 6 most frequently reported toxicities within the patient sample (*Data were missing for 4 patients so sample size was reduced accordingly). Clinical Endpoint

Scoring System

Incidence % (n)

Rectal Bleeding PGrade 1 (Rectal Bleeding PGrade 2) Proctitis PGrade 2

CTCAE [29] (LENT SOMA [30]) RTOG [31]/ Gulliford [35] LENT SOMA [30] CTCAE [29]/ LENT SOMA [30] UCLA-PCI [32] UCLA-PCI [32]

25.7 (28/109)

Sphincter Control PGrade 1 Rectal Pain PGrade 1 Bowel bother PGrade 1 Bowel bother PGrade 2

16.5 (18/109) 10.1 (11/109) 15.6 (17/109) 30.7 (32/105*) 11.5 (12/105*)

Table 3 Mean Area Under the Curve (AUC) for planned and accumulated DSM dose-widths and EUD corresponding to rectal bleeding PGrade 2 (LENT SOMA) and PGrade 1 (CTCAE), n = 28/109. The greater AUC of each parameter has been presented in bold. Dose Level (Gy)

Mean AUC (Planned)

Mean AUC (Accumulated)

30 40 50 60 65 70

0.606 0.603 0.627 0.608 0.635 0.659

0.629 0.621 0.635 0.643 0.664 0.642

EUD

0.673

0.682

at 50, 60, 65 and 70 Gy, and were equivalent at 40 Gy. At 30 Gy, the AUC of planned DSM dose-width was slightly higher than the accumulated AUC (0.004 difference). Remaining clinical endpoints For the remaining clinical endpoints (LENT SOMA sphincter control PGrade 1; CTCAE/LENT SOMA subjective rectal pain PGrade 1; UCLA-PCI ‘‘Overall, how big a problem have your bowel habits been for you during the last 4 weeks?”, bowel bother PGrade 1 and PGrade 2), EUD and DSM dose-widths had little discriminatory power from planned-DSM or accumulated-DSM. No dosimetric parameter was found to have AUC P 0.6 and lower 95% CI P 0.5. Results have been included as supplementary data. Equivalent uniform dose EUD produced the greatest AUCs for rectal bleeding and proctitis, indicating a stronger association than the spatial parameters investigated. In both cases, accumulated-EUD generated a higher AUC than planned-EUD. For all patients, EUD of accumulatedDSM was lower than that of planned-DSM (mean difference 2.2 Gy, standard error 0.3 Gy, range [ 0.3, 7.1] Gy). Discussion

Fig. 2. Receiver operator characteristic curves for (a) rectal bleeding with 65 Gy DSM dose-widths, (b) rectal bleeding with EUD, and (c) proctitis with EUD.

2. Accumulated-EUD (AUC 0.673) was the only dosimetric parameter with AUC P 0.6 and lower 95% CI P 0.5 (Fig. 3b). Accumulated DSM dose-widths had greater AUC than planned DSM dose-widths

Radiation dose received by the rectal wall during prostate radiotherapy was calculated and accumulated using DSMs. Geometric aspects of dose distribution - information not distinguishable from DVHs – were parametrised using DSM dose-widths. EUD was calculated to compare planned and accumulated DSMs using a single metric. Extracted dosimetric parameters were evaluated against six clinical endpoints reported by patients within the VoxTox research programme. Previous dose-toxicity investigations in the literature have been limited to planned dose only. This study has demonstrated, for the first time, that delivered dose can

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Fig. 3. High-low plots of mean AUC and 95% confidence intervals for (a) Rectal Bleeding and (b) Proctitis, where results were considered significant if mean AUC P0.6 and lower 95% CI P0.5.

be a stronger predictor of toxicity in the case of rectal bleeding and proctitis in prostate radiotherapy. Toxicity rates reported in the literature have been variable. The rate of bowel toxicity PGrade 2 (CTCAE), 5 year cumulative incidence, amongst VoxTox prostate patients was 17%. This falls within the bowel toxicity PGrade 2 (RTOG) range of 13.7–24.9% for IMRT over the same timeframe, reported by Dearnaley et al. [9] and Wortel et al. [34], respectively. The rates of incidence indicate that toxicity remains an important clinical issue.

Many associations were found between DSM dose-widths with rectal bleeding. Accumulated DSMs generated greater AUCs than planned DSMs for 5 DSM dose-width levels up to 70 Gy. The strongest correlation between rectal bleeding and any spatial parameter was the 65 Gy DSM dose-width from accumulated dose (AUC 0.664). At 30, 40 and 60 Gy, accumulated DSM dose-widths produced AUC P 0.6 and lower 95% CI P 0.5, where corresponding planned DSM dose-widths did not. These thresholds were considered indicative of significance following the methods of Gulliford et al. [33]. The greatest difference between planned and accumulated AUCs was observed at the 60 Gy DSM dose-width. Overall, the results compared well with the findings of Buettner et al. [1] who reported the most significant correlation with rectal bleeding to be the 61 Gy lateral extent (AUC 0.66), derived from planned dose data. Accumulated EUD was found to have the strongest correlation overall with rectal bleeding (AUC 0.682), and was the only predictor of proctitis (AUC 0.673). For all patients, accumulated-EUD was systematically lower than planned-EUD. A contributory factor was possibly the inherent blurring of high dose regions during accumulation. Upon visual inspection of daily DSMs, the differences in size, shape and position of the high dose region due to anatomical variation was clearly visible (for example, shown in deep red in Fig. 1). During accumulation, high doses were superimposed in overlap regions, but reduced where isodose edges differed, due to averaging over the full course of radiotherapy. This affected the maximum dose of the accumulated-DSM, on which EUD calculation was heavily weighted. The dose-blurring effect could also have been responsible for the increased frequency of 0% DSM dose-width results at high dose levels from accumulated-DSMs with respect to plannedDSMs. At 70 Gy, 4/109 patients recorded a 0% accumulated DSM dose-width (including 1 patient experiencing toxicity), whereas all corresponding planned DSM dose-widths had non-zero results. Furthermore, dose levels could not be considered independent variables, as a low 70 Gy DSM dose-width was likely to be associated with a low 65 Gy DSM dose-width, and a cooler plan overall. These issues were not accounted for within the scope of this study. The generally lower reported values for EUD and DSM dosewidths from accumulated dose compared with planned dose should not be interpreted as delivered treatment erring on the ’safe side’ in terms of dose to rectum. Where current NTCP models are based on planned dose, the presented results suggest that the same magnitude of risk would be associated with a systematically lower delivered dose. The findings show that the difference in dose between patients with and without rectal toxicity is greater from delivered dose than planned dose. This indicates that dosimetric parameters from accumulated-DSMs could provide new information to improve understanding of the relationship between dose and toxicity. The single parameter EUD was a superior predictor of rectal bleeding and proctitis than spatial dose quantifiers. However, DSM-dose widths produced several strong correlations with rectal bleeding, and for 5/6 dose levels, accumulated dose generated AUC values greater than planned dose. The ability to preserve and accumulate spatial dose information throughout treatment is a novel process requiring careful consideration of data interpretation and parametrisation. Future work may involve exploring alternative methods for geometrical quantification of spatial dose distributions in order to determine stronger correlations with toxicity. Analysis of delivered dose to the rectal wall could facilitate the identification of inhomogeneous intraorgan radiosensitivities, allowing shape-based dose constraints to be derived. Spatial considerations could complement current DVH-based approaches to treatment planning.

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Through novel characterisation of delivered dose, beyond the limitations of the static planned DVH, the aim is to determine those parameters strongly associated with rectal toxicity which could be incorporated into multivariate NTCP models. Emerging dose quantifiers could be integrated into planning constraints, as well as being prospectively monitored throughout treatment. Delivered dose can be accumulated in ’real-time’ and analysed with each fraction, allowing on-treatment toxicity risk assessment. Towards the end of the course of treatment, if toxicity prediction was found to be lower than planned, the decision could be made to increase the total delivered dose to the target. The potential scope for further individualisation and adaptation of treatment could ultimately reduce rates of toxicity incidence and improve clinical outcomes. Conclusion Parametrisation of delivered dose to the rectal wall during prostate radiotherapy has revealed stronger correlations with rectal bleeding and proctitis than achievable from planned dose. New information from accumulated delivered dose could lead to improved dose-toxicity modelling in the future, with the aim of reducing post-treatment toxicity. Conflict of interest The authors declare no conflicts of interest. Acknowledgements The authors would like to thank the patients who participated in the study, the referring physicians, and VoxTox Research Facilitator, Michael Simmons. LEAS is supported by the University of Cambridge W D Armstrong Trust Fund; AMB, MRR and KH are supported by the VoxTox Programme Grant, which is funded by Cancer Research UK (CRUK); JES was supported by a CRUK Clinical Research Fellowship; DJN is supported by a CRUK Clinical Research Fellowship; NGB is Principle Investigator of the CRUK VoxTox Programme and is supported by the NIHR Cambridge Biomedical Research Centre. Appendix A. Supplementary data Supplementary data associated with this article can be found, in the online version, at http://dx.doi.org/10.1016/j.radonc.2017.04. 008. References [1] Buettner F, Gulliford SL, Webb S, Sydes MR, Dearnaley DP, Partridge M. Assessing correlations between the spatial distribution of the dose to the rectal wall and late rectal toxicity after prostate radiotherapy: an analysis of data from the MRC RT01 trial (ISRCTN 47772397). Phys Med Biol 2009;54:6535–48. [2] Acosta O, Dréan G, Ospina JD, et al. Voxel-based population analysis for correlating local dose and rectal toxicity in prostate cancer radiotherapy. Phys Med Biol 2013;58:2581–95. [3] Wortel RC, Witte MG, van der Heide UA, et al. Dose–surface maps identifying local dose-effects for acute gastrointestinal toxicity after radiotherapy for prostate cancer. Radiother Oncol 2015;117:515–20. [4] Coloigner J, Fargeas A, Kachenoura A, et al. A novel classification method for prediction of rectal bleeding in prostate cancer radiotherapy based on a seminonnegative ICA of 3D planned dose distributions. IEEE J Biomed Health Informat 2015;19:1168–77. [5] Buettner F, Gulliford SL, Webb S, Partridge M. Modeling late rectal toxicities based on a parameterized representation of the 3D dose distribution. Phys Med Biol 2011;56:2103–18. [6] Dréan G, Acosta O, Ospina JD, et al. Identification of a rectal subregion highly predictive of rectal bleeding in prostate cancer IMRT. Radiother Oncol 2016;119:388–97.

[7] Gael Dréan G, Acosta O, Lafond C, Simon A, de Crevoisier R, Haigron P. Interindividual registration and dose mapping for voxelwise population analysis of rectal toxicity in prostate cancer radiotherapy. Med Phys 2016;43:2721–30. [8] Dearnaley DP, Jovic G, Syndikus I, et al. Escalated-dose versus control-dose conformal radiotherapy for prostate cancer: long-term results from the MRC RT01 randomised controlled trial. Lancet Oncol 2014;15:464–73. [9] Dearnaley D, Syndikus I, Mossop H, et al. Conventional versus hypofractionated high-dose intensity-modulated radiotherapy for prostate cancer: 5-year outcomes of the randomised, non-inferiority, phase 3 CHHiP trial. Lancet Oncol 2016;17:1047–60. [10] Cancer Research UK. Prostate cancer survival statistics. http:// www.cancerresearchuk.org/health-professional/cancer-statistics/statisticsby-cancer-type/prostate-cancer/survival#ref-2. Accessed: November 2016 [11] Landoni V, Fiorino C, Cozzarini C, Sanguineti G, Valdagni R, Rancati T. Predicting toxicity in radiotherapy for prostate cancer. Phys Med 2016;32:521–32. [12] Cox JD, Stetz J, Pajak TF. Toxicity criteria of the Radiation Therapy Oncology Group (RTOG) and the European organization for research and treatment of cancer (EORTC). Int J Radiat Oncol Biol Phys 1995;31:1341–6. [13] Palorini F, Botti A, Carillo V, et al. Bladder dose–surface maps and urinary toxicity: Robustness with respect to motion in assessing local dose effects. Physica Med. 2016;32:506–11. [14] Hamlett LJ, McPartlin AJ, Maile EJ, et al. Parametrized rectal dose and associations with late toxicity in prostate cancer radiotherapy. Br J Radiol 2015;88:20150110. [15] Murray J, McQuaid D, Dunlop A, et al. Su-e-j-14: a novel approach to evaluate the dosimetric effect of rectal variation during image guided prostate radiotherapy. Med Phys 2014;41:157. [16] Söhn M, Alber M, Yan D. Principal component analysis-based pattern analysis of dose–volume histograms and influence on rectal toxicity. Int J Radiat Oncol Biol Phys 2007;69:230–9. [17] Jaffray DA, Lindsay PE, Brock KK, Deasy JO, Tomé W. Accurate accumulation of dose for improved understanding of radiation effects in normal tissue. Int J Radiat Oncol Biol Phys 2010;76:S135–9. [18] CompRT VoxTox. Linking radiation dose at the voxel level with toxicity. http:// www.comprt.org/research/voxtox. Accessed: August 2016 [19] Scaife JE, Harrison K, Romanchikova M, et al. Random variation in rectal position during radiotherapy for prostate cancer is two to three times greater than that predicted from prostate motion. Br J Radiol 2014;87:20140343. [20] Scaife JE, Thomas SJ, Harrison K, et al. Accumulated dose to the rectum, measured using dose-volume histograms and dose-surface maps, is different from planned dose in all patients treated with radiotherapy for prostate cancer. Br J Radiol 2015;88:20150243. [21] National Institute for Health and Care Excellence (NICE). Prostate cancer: diagnosis and treatment (CG175). http://www.nice.org.uk/guidance/cg175. Accessed: November 2016 (2014) [22] Burnet NG, Adams EJ, Fairfoul J, et al. Practical aspects of implementation of helical tomotherapy for intensity-modulated and image-guided radiotherapy. Clin Oncol 2010;22:294–312. [23] Thomas SJ, Ashburner M, Tudor GSJ, et al. Intra-fraction motion of the prostate during treatment with helical tomotherapy. Radiother Oncol 2013;109:482–6. [24] Sutcliffe MP, Harrison K, Scaife JE, Parker MA, Romanchikova M. Autocontouring of the rectum on megavoltage computed tomography images. Cambridge University Engineering Department Technical Report 2015;CUED/ C-MICROMECH/TR. 100. [25] Thomas SJ, Romanchikova M, Harrison K, et al. Recalculation of dose for each fraction of treatment on TomoTherapy. Br J Radiol 2016;89:20150770. [26] Thomas SJ, Eyre KR, Tudor GSJ, Fairfoul J. Dose calculation software for helical tomotherapy, utilizing patient ct data to calculate an independent threedimensional dose cube. Med Phys 2012;39:160–7. [27] Niemierko A. Reporting and analyzing dose distributions: a concept of equivalent uniform dose. Med Phys 1997;24:103–10. [28] Michalski JM, Gay H, Jackson A, Tucker SL, Deasy JO. Radiation dose-volume effects in radiation-induced rectal injury. Int J Radiat Oncol Biol Phys 2010;76:123–9. [29] U.S. department of health and human services NIoH. National Cancer Institute. Common Terminology Criteria for Adverse Events (CTCAE) Version 4.0 2010. Accessed: July 2016. URL: http://evs.nci.nih.gov/ftp1/CTCAE/CTCAE4.03201006-14QuickReference5x7.pdf. [30] LENT SOMA tables table of contents. Radiother Oncol 1995;35:17–60. [31] Pilepich M, Asbell S, Krall J, et al. Correlation of radiotherapeutic parameters and treatment related morbidity—analysis of RTOG study 77–06. Int J Radiat Oncol Biol Phys 1987;13:1007–12. [32] Litwin MS, Hays RD, Fink A, Ganz PA, Leake B, Brook RH. The UCLA prostate cancer index: development, reliability, and validity of a health-related quality of life measure. Med Care 1998;36:1002–12. [33] Gulliford SL, Partridge M, Sydes MR, Andreyev J, Dearnaley DP. A comparison of dose–volume constraints derived using peak and longitudinal definitions of late rectal toxicity. Radiother Oncol 2010;94:241–7. [34] Wortel RC, Incrocci L, Pos FJ, et al. Late side effects after image guided intensity modulated radiation therapy compared to 3D-conformal radiation therapy for prostate cancer: results from 2 prospective cohorts. Int J Radiat Oncol Biol Phys 2016;95:680–9. [35] Gulliford SL, Foo K, Morgan RC, et al. Dose–volume constraints to reduce rectal side effects from prostate radiotherapy: Evidence from MRC RT01 trial ISRCTN 47772397. Int J Radiat Oncol Biol Phys 2010;76:747–54.

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Helical tomotherapy for prostate cancer radiation

Original Article

therapy: An audit of early toxicity and quality of life

Helical tomotherapy for prostate cancer radiation therapy: An audit of early toxicity and quality of life ABSTRACT Background: Radiation plays a major role in the management of localized prostate cancer (CaP). There are limited studies reporting the quality of life (QOL) and toxicity with CaP tomotherapy. Materials and Methods: This is a single‑institutional prospective observational study evaluating the acute toxicity and QOL of patients with CaP receiving tomotherapy from May 2018 to October 2019. Toxicity assessed using radiation therapy oncology group toxicity grading. QOL assessed using International Prostate Symptom Score (IPSS) and QOL score. Results: A total number of 74 patients received radiation therapy (RT), of which 25 had postoperative RT and 49 had radical RT. The median age was 71 years. During RT, 8 (10.8%) had Grade 2 gastrointestinal (GI) and 4 (5.4%) had Grade 2 genito urinary (GU) toxicities. At 3 months, 1 (1.4%) had Grade 2 GI, 1 (1.4%) had Grade 2 GU, and 1 (1.4%) had Grade 3 GU toxicities. At 6 months, 1 patient had Grade 2 GU and no Grade 2 GI toxicity noted. In postoperative RT Group, 2 (8%) Grade 2 GI and 1 (1.4%) Grade 2 genitourinary toxicity reported during radiation. At 3 months, 1 (1.4%) Grade 2 GI, 1 (1.4%) G2 GU, and 1 (1.4%) G3 GU toxicities noted. At 6 months, no ≥ Grade 2 noted. In radical RT group, during radiation 6 (12.2%) Grade 2 GI and 3 (6.1%) Grade 2 GU recorded. At 3 and 6 months, no ≥ Grade 2 GI/GU toxicity was recorded. No Grade 3/Grade 4 observed in radical RT group. One patient in radical RT and one in postoperative RT had severe IPSS symptom score. Results are comparable to reported studies. Conclusion: Our initial clinical experience with helical tomotherapy in CaP confirms lower rate of toxicities and no significant worsening of QOL with RT. KEY WORDS: Helical tomotherapy, image guided radiotherapy, prostate cancer, quality of life, toxicity

INTRODUCTION Tomotherapy is an intensity‑modulated rotational radiation therapy (RT) technique using photon fan beam designed for image guided radiotherapy (IGRT).[1‑5] In helical tomotherapy, the couch and gantry are in continuous motion and described as a helical trajectory. Thus, it permits high tailored dose distributions with excellent coverage and integrates the image guidance for patients setup verification. [6,7] The additional benefit of helical tomotherapy is incorporated with adaptive planning software which determines the changes in external or internal anatomy and can modify the radiation treatment plans if necessary. Prostate cancer (CaP) RT plays a major role in the management of localized CaP. In our center, IGRT for CaP is delivered either using volumetric arc therapy or helical tomotherapy. Majority of prostate cases

are treated with helical tomotherapy. There are limited study reporting the quality of life (QOL) and toxicity pattern with different RT techniques and studies pertaining to tomotherapy are even less.

Beena Kunheri, J. S. Lakshmi, Greeshma C. Ravindran1, Haridas, Vishal Marwaha2 Departments of Radiation Oncology, 1 Biostatistics and 2 Amrita School of Medicine, AIMS, Amrita Vishwa Vidyapeetham, Kochi, India For correspondence: Prof. Beena Kunheri, Department of Radiation Oncology, Amrita School of Medicine, AIMS, Amrita Vishwa Vidyapeetham, Kochi ‑ 682 041, Kerala, India. E‑mail: beenakunheri@yahoo. co.in

In the present study, we prospectively evaluated the acute, early delayed toxicity and QOL of patient undergoing postoperative RT (RP + RT) or radical RT for localized CaP using helical tomotherapy. MATERIALS AND METHODS This is a single institutional study evaluating the acute, early late toxicities and QOL of patient

Submitted: 08‑Sep‑2020 Revised: 20‑Dec‑2020 Accepted: 03‑Jan‑2021 Published: 11‑Jun‑2021 Access this article online

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Cite this article as: Kunheri B, Lakshmi JS, Ravindran GC, Haridas, Marwaha V. Helical tomotherapy for prostate cancer radiation therapy: An audit of early toxicity and quality of life. J Can Res Ther 2021;17:366‑71.

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receiving RT for localized CaP using helical tomotherapy from May 2018 to October 2019. Patients with age ≤85 years, with histologically confirmed nonmetastatic CaP were included in this study. Intermediate and high Risk patients received hormonal treatment as per institutional protocol. Informed consent was taken and those willing to participate in this study were given QOL questionnaires. Simulation and planning All patients underwent computed tomography (CT) simulation with bladder and rectal protocol (moderately filled bladder and empty rectum) in supine position with appropriate immobilization devices (head rest, knee rest, etc.,) and were treated with helical tomotherapy according to the standard institutional protocol. Radiation dose Postoperative radiation dose was 60–66 Gy/30–33 fractions and in patients with gross residual disease or local relapse dose escalation was done up to 70 Gy. In radical RT intermediate risk, patients received 60 Gy in 20 fractions to prostate alone. High risk patients were treated with 70 Gy in 28 fractions to primary and pelvic nodal region received 50.4 Gy/28 fractions (SIB‑simultaneous integrated boost). Toxicity and quality of life assessment Toxicity assessed weekly during RT and then at 3 and 6 months following RT using RT Oncology Group toxicity grading.[8] QOL assessed pre‑RT, on the last day of treatment and at 3 and 6 months following RT. QoL assessment done using International Prostate Symptom Score (IPSS) and QOL score.[9] All patients will be followed up long term for any new toxicity and will be recorded. Compliance assessed based on treatment breaks and completion of proposed treatment. After completion, patients were reviewed every 3 months for 1st year and then every 4 months for next 1 year and thereafter every 6 months for subsequent 3 years and then annually after 5th year. This is an interim report, analyzing acute and early delayed toxicity as well as QOL. Acute toxicity is during radiation and within 3 months of treatment, early delayed toxicity is from 3 months to 6 months of treatment. Late toxicity is the toxicity after 6 months and late toxicity was not analyzed for this report. Ethical issues Informed consent was obtained from all patients participating in this study. This study was approved by the Institutional Review Board. Statistical details Statistical analysis was done using IBM SPSS 20.0 (SPSS Inc., Chicago, USA). For all continuous variables, results shown as mean ± standard deviation, and for categorical variables as percentage. To test the statistical significance of difference

between the two groups Chi‑square test was applied. To test the statistical significance of difference in mean QOL score between the two groups, Student’s t‑test was applied. P < 0.05 was considered as statistically significant. RESULTS The data of 74 patients were analyzed. Patient characteristics The median age was 71 years (range 51–82 years). Based on D’Amico risk stratification; 2 (2.7%) patients were low risk, 10 (13.5%) were intermediate and 62 (83.8%) were high risk. Patient characteristics are shown in Table 1. Toxicity pattern During RT, majority of the toxicity was reported at week 3 of RT. Thirty (40.5%) had Grade 1 and 8 (10.8%) had Grade 2 gastrointestinal (GI) toxicities. Regarding genitourinary (GU) toxicities 43 (58.1%) had Grade 1 and 4 (5.4%) had grade 2. At first follow‑up (3 months), 1 (1.4%) had Grade 1, 1 (1.4%) had Grade 2 GI toxicity and none had Grade —. Regarding GU toxicity 11 (14.9%) had Grade 1 and each 1 (1.4%) patient had Grade 2/3. At 6 months, only 2 (2.7%) had Grade 1 GI, 4 (5.4%) had Grade 1 GU and 1 (1.4%) had Grade 3 GU toxicities. Overall no Grade 3 or 4 GI toxicity and no grade 4 GU toxicity were observed. Figure 1 shows the overall toxicity pattern in my cohort. Of the 74 patient, 25 (33.8%) patients received postoperative RT and 49 (66.2%) received Radical RT. On subgroup analysis Table 1: Patients characteristics Characteristics

n (%)

RP+RT group Radical RT group Age (years) Range Median age

25 (33.8) 49 (66.2)

Characteristics Stage I II A II B II C III A III B III C IV A Risk stratification Low Intermediate High Adjuvant RT Salvage RT Radiation dose EQD2: ≤66 EQD2: >66 Hypofractionation

RP+RT group, n (%)

Radical group, n (%)

0 (0.0) 0 (0.0) 0 (0.0) 4 (16) 0 (0.0) 11 (44) 3 (12) 7 (28)

1 (2) 1 (2) 9 (18.4) 6 (12.2) 11 (22.4) 7 (14.3) 2 (4.9) 12 (24.5)

0 (0.0) 3 (12) 22 (88) 14 (56) 11 (44)

2 (4.1) 7 (14.3) 40 (81.6) NA NA

13 (52) 12 (48) NA

NA NA 49 (100)

RP=Radical prostatectomy, RT=Radiation therapy, NA=Not available, EQD2: equivalent dose in 2Gy

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with regards to postoperative RT patients, 12 (48%) had Grade 1 and 2 (8%) had Grade 2 GI toxicities. Regarding GU toxicity 19 (76%) had Grade 1 and 1 (4%) had Grade 2. At 3 months, 1 (4.5%) patient had Grade 2 GI and each 1 (4.5%) had Grade 2/3 had GU toxicity. At 6 months, no Grade 2 toxicity was recorded. Figure 2 shows the toxicity pattern in adjuvant/ salvage RT patients. With regards to radical RT, during RT 18 patients (36.7%) had Grade 1 and 6 (12.2%) had Grade 2 GI toxicity. With regards to GU toxicity 24 (49%) had Grade 1 and 3 (6.1%) patients had Grade 2. At 3 months and 6 months, no Grade 2 GI toxicity was recorded. Overall, no grade 3 or 4 GI and GU toxicity were observed. Figure 3 shows the toxicity pattern in radical RT patients.

modalities of treatment are combined. After the advent of modern RT techniques (IGRT) and following advancement in surgical techniques, there is a significant reduction in the toxicities compared to conventional methods. Beck et al.[10] in 2017, analyzed the toxicity pattern of 69 patients receiving adjuvant/salvage RT using Tomotherapy technique, reported 10.1%(n = 7) GU and 5.8% (n = 4) GI acute toxicities. Similarly, Linsay et al.[11] in 2017, evaluated the toxicity pattern of 313 patients receiving adjuvant RT using helical tomotherapy

Quality of life QOL assessment done at baseline (before starting RT), at RT completion, at 3 months and at 6 months. IPSS symptom score and IPSS QOL scale were used for assessment. For analysis, IPSS QOL scale categorization done as good and average to severe. “Good” includes delighted, pleased, and mostly satisfied. “Average” includes mixed and “Poor” includes mostly dissatisfied, unhappy, and terrible. International Prostate Symptom Score symptom score No severe symptoms were noted at baseline. One (1.4%) patient had severe symptom score at the time of RT completion and 3 months. No severe symptoms noted at 6 months. On subgroup analysis, in postoperative patients, one patient had severe symptom at RT completion and at 3 months whereas in radical RT patients no severe symptom score noted at RT completion, at 3 months and at 6 months.

Figure 1: Overall toxicity pattern in prostate patients in helical tomotherapy

International Prostate Symptom Score quality of life score One patient in the radical RT arm had poor QOL at RT completion. No poor QOL score noted at 3 months and at 6 months. IPSS symptom and QOL score is shown in Tables 2 and 3. DISCUSSION Helical tomotherapy is an advanced form of IGRT delivery system with onboard imaging and capability of adaptive planning.[6,7] Our clinical experience with moderate hypofractionation in carcinoma prostate patients using helical tomotherapy show low rate of toxicity with no marked deterioration in QOL. With the benefit of image guidance and adaptive planning software in tomotherapy, lower and acceptable rate of toxicities were achievable which translates into better QOL. This study reports the acute toxicity and QOL. Late toxicity will be reported later after adequate follow‑up. Acute toxicity As mentioned in the literature, the most common toxicities are GI and GU in CaP patients. Patients receiving postoperative RT are expected to have more toxicities as two radical 368

Figure 2: Toxicity pattern in postoperative radiation therapy patients in helical tomotherapy

Figure 3: Toxicity pattern in radical radiation therapy patients in helical tomotherapy

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Table 2: Overall international prostate symptom score symptom score and quality of life score IPSS symptom score No Mild Moderate Severe IPSS QOL score Good Average Poor

Pre-RT (%)

RT completion (%)

3 months (%)

6 months (%)

10 (13.5) 31 (41.9) 27 (36.5) 6 (8.1)

10 (13.5) 50 (67.6) 13 (17.6) 1 (1.4)

17 (23) 53 (71.6) 0 (0.0) 1 (1.4)

22 (29.7) 48 (64.9) 1 (1.4) 0 (0.0)

31 (41.9) 35 (47.3) 8 (10.8)

48 (64.9) 25 (33.8) 1 (1.4)

61 (82.4) 10 (13.5) 0 (0.0)

64 (86.5) 7 (9.5) 0 (0.0)

IPSS=International prostate symptom score, QOL=Quality of life, RT=Radiation therapy

Table 3: International prostate symptom score symptom score and quality of life score of postoperative radiation therapy and radical radiation therapy patients Pre-RT (%)

RT completion (%)

3 months (%)

6 months (%)

Postoperative RT group IPSS symptom score No Mild Moderate Severe IPSS QOL score Good Average Poor Radical RT group IPSS symptom score No Mild Moderate Severe IPSS QOL score Good Average Poor

5 (20) 16 (64) 4 (16) 0 (0.0)

4 (16) 17 (68) 3 (12) 1 (4)

8 (36.4) 13 (59.1) 0 (0.0) 1 (4.5)

10 (45.5) 11 (50) 1 (4.5) 0 (0.0)

17 (68) 7 (28) 1 (4)

20 (80) 5 (20) 0 (0.0)

20 (90.9) 2 (9.1) 0 (0.0)

5 (10.2) 15 (30.6) 23 (46.9) 6 (12.2)

6 (12.2) 33 (67.3) 10 (20.4) 0 (0.0)

9 (18.4) 40 (81.6) 0 (0.0) 0 (0.0)

12 (24.5) 37 (75.5) 0 (0.0) 0 (0.0)

14 (28.6) 28 (57.1) 7 (14.3)

28 (57.1) 20 (40.8) 1 (2)

41 (83.7) 8 (16.3) 0 (0.0)

44 (89.8) 5 (10.2) 0 (0.0)

IPSS=International prostate symptom score, QOL=Quality of life, RT=Radiation therapy

reported 25% (n = 77) Grade 2 GU and 33% (n = 103) Grade 2/1% (n = 1) Grade 3 GI acute toxicities. The literature on hypofractionated postoperative helical tomotherapy in CaP by Cuccia et al.[12‑15] report the various helical tomotherapy fractionation schemes. Acute GI and GU toxicities were reported. These include: For GU Grade 1 in 46% (n = 35) and Grade 2 in 4% (n = 3). For GI toxicities, Grade 1 in 36% (n = 75) and Grade 2 in 18% (n = 14). In the present study, we observed low rate of acute and early delayed toxicity. During RT, 8% patients had Grade 2 GI and 4% had Grade 2 GU toxicity. At 3 months, 4.5% had Grade 3 GI and 4.5% grade 2 GU and 4.5% had Grade 3 GU toxicities. At 6 months, no Grade 2, 3, or 4 toxicities were recorded. Low rates of toxicities observed in the present study could be due to advanced techniques such as Helical Tomotherapy and minimally invasive surgery, robotic‑assisted radical prostatectomy. We also used a tighter margin of 0.5 cm from CTV to PTV, which is considered minimum recommended when daily online image guidance adopted.[16] Table 4 shows the CaP studies and related toxicity pattern following image‑guided RT. Due to the increasing workload and logistic issues in a country like India, it becomes important to reduce treatment time

whenever possible. CaP with low α/β value is one tumor that can be treated using hypofractionation. Long‑term follow‑up results of hypofractionated studies such as conventional versus hypofractionated high‑dose intensity‑modulated radiotherapy for CaP ‑CHHIP (60 Gy in 20 fractions)[19] and Cleveland clinic[20] dose schedules (70 Gy in 28 fractions) did show improved control rates with acceptable toxicity. CHHIP trial used IMRT to compare conventional versus hypofractionation in 3162 men. They reported 38% Grade 2 or more GI and 49% Grade 2 or more GU acute toxicities. At 18 weeks, they noted decreasing trend; 3% GI and 5%GU toxicities were reported. Cleveland clinic data on hypofractionation ((70 Gy in 28 fractions) with IGRT reported 40% Grade 1 and 9% Grade 2 GI toxicity. GU toxicities were 48% Grade 1, 18% Grade 2, and 1% Grade 3. Barra et al.[21] in 2014, reported 36% Grade 1, 13% Grade 2, 4% Grade 3 GU toxicities and 6% Grade 1, 4% Grade 2 GI toxicities using helical tomotherapy in CaP patients receiving radical radiotherapy. In this study, we observed 12.2% Grade 2 GI and 6.1% Grade 2 GU toxicity. At 3 months and 6 months, no Grade 2 or more GI/GU toxicity was recorded. The low rates of toxicity could be attributed to the high conformality achieved in our plans thereby limiting the dose to the organs at risk (OARs). We need further follow‑up and larger cohort to confirm the absolute benefit and outcome.

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Table 4: Prostate studies reporting acute and late toxicities Technique Postoperative RT study Beck et al.[10] Jensen et al.[11]

Tomotherapy Tomotherapy

Cuccia et al.[12]

Tomotherapy

Berlin et al.[17]

IMRT

Goenka et al.[18]

IMRT

Current study

Tomotherapy

Radical RT study CHHIP[19] Cleaveland clinic[20]

IMRT IMRT

GI toxicities

GU toxicities

Acute

Late

Acute

Late

5.8% G2: 33% G3: 1% G1: 36% G2: 18% G2: 16% G3: 0% G2: 8% G3: 0% G2: 8% G3: 0%

No G2 or higher G2: 16% G3: 2% G2: 6.6%

10.1% G2: 25% G3: 0% G1: 46% G2: 4% G2: 19% G3: 0% G2: 13%

G2: 2.9% G2: 37% G3: 10% ≥G2: 5.3%

G2: 4% G3: 0%

≥G2: 38% G2: 9%

≥G2: 49% G2: 18% G3: 1%

≥G2: 11.7% G2: 5.1% G3: 0.1%

G2: 13% G3: 4% G2: 6.1%

G2: 4%

G2: 12% G3: 0% G2: 2% G3: 1.4% NR

Barra et al.[21]

Tomotherapy

G2: 4%

≥G2: 11.9% G2: 3.1% G3: 1.3% G4: 0.1% No G2 or higher

Current study

Tomotherapy

G2: 12.2%

G2: 13% G3: 0% G2: 17%

GI=Gastro-intestinal, GU=Genito-urinary, RT=Radiation therapy, IMRT=Intensity Modulated Radiation Therapy, NR: Not reported

Quality of life assessment QOL is an important hallmark in CaP management, especially considering that men are likely to survive for a considerable number of years after treatment. The CaP Outcomes Study on QOL[22] examined 1,655 men in 1994–1995 and who underwent either radical prostatectomy (1,164 men) or radiotherapy (491 men). The study found that those undergoing surgery were significantly more likely to have urinary incontinence and erectile dysfunction (ED) at 2 and 5 years. However, bowel urgency at 2 and 5 years were significantly more in those undergoing radiotherapy. Notably, when the follow‑up duration was extended to 15 years, the burden of urinary incontinence, ED, and bowel urgency were comparable between the treatment modalities. A systematic review and meta‑analysis by Chen et al.[23] reported a pooled analysis of total 6 studies containing 4423 patients. They analyzed the QOL between RP and RT patients and concluded that RP was associated with worse urinary and sexual domain score than EBRT. In contrast, EBRT group had lower bowel domain score than RP group. Pervez et al.[24] reported the QOL outcome of CaP patients treated with tomotherapy in 2012. The study found that bowel functions were affected maximum than urinary symptoms. Bowel symptoms scores declined at 1 and 6 months compared to baseline whereas overall urinary scores at baseline with those at 1 month and 6 months showed improvement. In the present study, we observed improvement in both IPSS symptom score and QOL score on completion of RT, at 3 months and at 6 months compared to baseline in the radical RT group. On subgroup analysis, radical RT patients had better QOL as compared to postoperative RT patients on follow‑up. In the postoperative RT group, one patient had severe IPSS score during RT whereas no patient had severe score in the radical RT arm. The improvement in QOL noticed for radical RT patients compared to base line could be due to 370

the bulky local disease responding to treatment. The subjective nature of questionnaires and attitude of the patients toward their QOL and the timing does affect the response to the questionnaire. Limitation This is a short‑term study analyzing acute toxicity and health‑related QOL issues. Longer follow‑up is needed to evaluate the late effects, outcome, and long‑term bearing on QOL. CONCLUSION Our clinical experience with helical tomotherapy in CaP RT confirms lower rate of toxicities and no deterioration in QOL as compared with studies in literature.[13‑15,25,26] The use of IGRT and highly conformal treatment lowers the toxicity rates in both radical RT and postoperative RT as it allows more uniform coverage of target, while minimizing OARs doses improving the therapeutic ratio. Acknowledgment We would like to thank all the staff of the Department of Radiation oncology, Medical Oncology, Uro‑oncology. Financial support and sponsorship Nil. Conflicts of interest There are no conflicts of interest. REFERENCES 1.

Mackie TR, Holmes T, Swerdloff S, Reckwerdt P, Deasy JO, Yang J, et al. Tomotherapy: A new concept for the delivery of dynamic conformal

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2. 3. 4. 5. 6. 7. 8.

10.

11.

12.

13.

14.

15.

radiotherapy. Med Phys 1993;20:1709‑19. Mackie TR, Holmes TW, Reckwerdt PJ, Yang J. Tomotherapy: Optimized planning and delivery of radiation therapy. International Journal of Imaging Systems and Technology 1995;6:43‑55. Yang JN, MackieTR, Reckwerdt PJ, Deasy JO, Thomadsen BR. An investigation of tomotherapy beam delivery. Med Phys 1997;24:425‑36. Mackie TR, Balog J, Ruchala K, Shepard D, Aldridge S, Fitchard E, et al. Tomotherapy. InSeminars in Radiation Oncology 1999;9:108‑17. Olivera GH, Shepard DM, Ruckala K, Jennifer SA, John PB, Guang YF, et al. Tomotherapy. In: Van Dyk J, editor. Modern Technology of Radiation Oncology. Madison: Medical Physics Publishing; 1999. Ruchala KJ. Megavoltage Computed Tomography for Tomotherapy Verification. Madison: Dept. of Medical Physics, University of Wisconsin; 1999. Ruchala KJ, Olivera GH, Kapatoes JM, Schloesser EA, Reckwerdt PJ, Mackie TR. Megavoltage CT image reconstruction during tomotherapy treatments. Phys Med Biol 2000;45:3545‑62. Cox JD, Stetz J, Pajak TF. Toxicity criteria of the Radiation Therapy Oncology Group (RTOG) and the European Organization for Research and Treatment of Cancer (EORTC) Int J Radiat Oncol Biol Phys 1995;31:1341‑6. Lukacs B, Grange JC, Comet D. One‑year follow‑up of 2829 patients with moderate to severe lower urinary tract symptoms treated with alfuzosin in general practice according to IPSS and a health‑related quality‑of‑life questionnaire. BPM Group in General Practice. Urology 2000;55:540‑6. Beck M, Wust P, Barelkowski T, Kaul D, Thieme AH, Wecker S, et al. Risk adapted dose‑intensified postoperative radiation therapy in prostate cancer patients using a simultaneous integrated boost technique applied with helical Tomotherapy. Radiat Oncol 2017;12:125. Jensen L, Yuh B, Wong JYC, Schultheiss T, Cheng J, Ruel N, et al. Outcomes and toxicity of 313 prostate cancer patients receiving helical tomotherapy after radical prostatectomy. Adv Radiat Oncol 2017;2:597‑607. Cuccia F, Mortellaro G, Serretta V, Valenti V, Tripoli A, Gueci M, et al. Hypofractionated postoperative helical tomotherapy in prostate cancer: A mono‑institutional report of toxicity and clinical outcomes. Cancer Manag Res 2018;10:5053‑60. Cuccia F, Mazzola R, Arcangeli S, Mortellaro G, Figlia V, Caminiti G, et al. Moderate hypofractionated helical tomotherapy for localized prostate cancer: Preliminary report of an observational prospective study. Tumori 2019;105:516‑23. Cuccia F, Mortellaro G, Trapani G, Valenti V, Ognibene L, De Gregorio G, et al. Acute and late toxicity and preliminary outcomes report of moderately hypofractionated helical tomotherapy for localized prostate cancer: A mono‑institutional analysis. Radiol Med 2020;125:220‑7. Cuccia F, Fiorentino A, Corrao S, Mortellaro G, Valenti V, Tripoli A,

16.

17.

18.

19.

20.

21.

22. 23.

24.

25.

26.

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et al. Moderate hypofractionated helical tomotherapy for prostate cancer in a cohort of older patients: A mono‑institutional report of toxicity and clinical outcomes. Aging Clin Exp Res 2020;32:747‑53. Poortmans P, Bossi A, Vandeputte K, Bosset M, Miralbell R, Maingon P, et al. Guidelines for target volume definition in post‑operative radiotherapy for prostate cancer, on behalf of the EORTC Radiation Oncology Group. Radiother Oncol 2007;84:121‑7. Berlin A, Cho E, Kong V, Howell KJ, Lao B, Craig T, et al. Phase 2 trial of guideline‑based postoperative image guided intensity modulated radiation therapy for prostate cancer: Toxicity, biochemical, and patient‑reported health‑related quality‑of‑life outcomes. Pract Radiat Oncol 2015;5:e473‑82. Goenka A, Magsanoc JM, Pei X, Schechter M, Kollmeier M, Cox B, et al. Improved toxicity profile following high‑dose postprostatectomy salvage radiation therapy with intensity‑modulated radiation therapy. Eur Urol 2011;60:1142‑8. Dearnaley D, Syndikus I, Mossop H, Khoo V, Birtle A, Bloomfield D, et al. Conventional versus hypofractionated high‑dose intensity‑modulated radiotherapy for prostate cancer: 5‑year outcomes of the randomised, non‑inferiority, phase 3 CHHiP trial. Lancet Oncol 2016;17:1047‑60. Kupelian PA, Willoughby TR, Reddy CA, Klein EA, Mahadevan A. Hypofractionated intensity‑modulated radiotherapy (70 Gy at 2.5 Gy per fraction) for localized prostate cancer: Cleveland Clinic experience. Int J Radiat Oncol Biol Phys 2007;68:1424‑30. Barra S, Vagge S, Marcenaro M, Blandino G, Timon G, Vidano G, et al. Image guided hypofractionated radiotherapy by helical tomotherapy for prostate carcinoma: Toxicity and impact on Nadir PSA. BioMed Res Int 2014;2014: 541847. Resnick MJ, Koyama T, Fan KH, Albertsen PC, Goodman M, Hamilton AS, et al. Long‑term functional outcomes after treatment for localized prostate cancer. N Engl J Med 2013;368:436‑45. Chen C, Chen Z, Wang K, Hu L, Xu R, He X. Comparisons of health‑related quality of life among surgery and radiotherapy for localized prostate cancer: A systematic review and meta‑analysis. Oncotarget 2017;8:99057. Pervez N, Krauze AV, Yee D, Parliament M, Mihai A, Ghosh S, et al. Quality‑of‑life outcomes in high‑risk prostate cancer patients treated with helical tomotherapy in a hypofractionated radiation schedule with long‑term androgen suppression. Curr Oncol 2012;19:e201‑10. Schiller K, Geier M, Duma MN, Nieder C, Molls M, Combs SE, et al. Definitive, intensity modulated tomotherapy with a simultaneous integrated boost for prostate cancer patients–Long term data on toxicity and biochemical control. Rep Pract Oncol Radiother 2019;24:315‑21. Takakusagi Y, Kawamura H, Okamoto M, Kaminuma T, Kubo N, Mizukami T, et al. Long‑term outcome of hypofractionated intensity‑modulated radiotherapy using TomoTherapy for localized prostate cancer: A retrospective study. PLoS One 2019;14:e0211370.

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Influence of optimizing protocol choice on the integral dose value in prostate radiotherapy planning by reports of practical oncology and radiotherapy 2 2 ( 2 0 1 7 ) 415–419 dynamic techniques Available online at www.sciencedirect.com

ScienceDirect journal homepage: http://www.elsevier.com/locate/rpor

Technical note

Inﬂuence of optimizing protocol choice on the integral dose value in prostate radiotherapy planning by dynamic techniques – Pilot study Anna Zaleska a,b,∗ , Krzysztof Bogaczyk c , Tomasz Piotrowski a,d a

Department of Medical Physics, Greater Poland Cancer Centre, Poznan, Poland Faculty of Physics, University of Warsaw, Warsaw, Poland c Fryderic Chopin State Clinical Hospital, Rzeszow, Poland d Department of Electroradiology, University of Medical Sciences, Poznan, Poland b

a r t i c l e

i n f o

a b s t r a c t

Article history:

Aim: The purpose of this study was to compare the values of integral dose, calculated for

Received 17 September 2016

treatment plans of dynamic radiotherapy techniques prepared with two different optimiza-

Received in revised form

tion protocols.

27 December 2016

Background: Delivering radiation by IMRT, VMAT and also HT techniques has an inﬂuence on

Accepted 19 April 2017

the low dose deposition of large areas of the patient body. Delivery of low dose can induce

Available online 17 August 2017

injury of healthy cells. In this situation, a good solution would be to reduce the area, which receives a low dose, but with appropriate dose level for the target volume.

Keywords:

Materials and methods: To calculate integral dose values of plans structures, we used 90

Integral dose

external beam radiotherapy plans prepared for three techniques (intensity modulated

Prostate

radiotherapy, volumetric modulated arc therapy and helical tomotherapy). One technique

IMRT

includes three different geometry combinations. 45 plans were prepared with classic opti-

VMAT

mization protocol and 45 with rings optimization protocol which should reduce the low

doses in the normal tissue. Results: Differences in values of the integral dose depend on the geometry and technique of irradiation, as well as optimization protocol used in preparing treatment plans. The application of the rings optimization caused the value of normal tissue integral dose (NTID) to decrease. Conclusion: It is possible to limit the area of low dose irradiation and reduce NTID in dynamic techniques with the same clinical constraints for OAR and PTV volumes by using an optimization protocol other than the classic one. © 2017 Greater Poland Cancer Centre. Published by Elsevier Sp. z o.o. All rights reserved.

Introduction

In recent years, techniques using beam intensity modulation, Corresponding author. Tel.: +48 785 617 141. both intensity modulated radiotherapy (IMRT), volumetric E-mail address: anna.zaleska@o2.pl (A. Zaleska). http://dx.doi.org/10.1016/j.rpor.2017.04.003 1507-1367/© 2017 Greater Poland Cancer Centre. Published by Elsevier Sp. z o.o. All rights reserved. ∗

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modulated arc therapy (VMAT) and helical tomotherapy (HT), have become frequently used in clinical practice. One can say that in some locations, on account of dose distribution conformality to the target area, better dose reduction in organs at risk or shorter therapy sessions, IMRT techniques substitute conventional three dimensional conformal radiotherapy (3DCRT).1–3 Despite signiﬁcant advantages, there is a problem associated with the use of both IMRT, VMAT and HT as they have the dose bath effect.4 Dose bath effect or low radiation dose in normal tissue area is clearly observable when low isodose on CT scans are compared between the 3DCRT and IMRT techniques as is dose reduction in the organ at risk (OAR) volume for IMRT techniques plans towards 3DCRT. Integral dose (ID) is deﬁned as a product of mean dose and tissue volume for contemplated organs or structure (1).5 ID = Dmean of structure × Vstructure

(1)

In the case of normal tissue, the term normal tissue integral dose (NTID) is used, deﬁned as a difference between ID deposited in the body (in healthy tissue) and ID deposited in the clinical target volume (CTV) (2). NTID = IDnormal tissue − IDCTV

(2)

In prostate location, both the bladder and the rectal wall are in close proximity or they have a common part with the planning target volume. It is very important in the case of prostate cancer therapy, on account of patients’ quality of life and side effects, to reduce high dose to the bladder and rectal wall,6,7 but integral dose reduction in these organs would also be beneﬁcial. According to As Low As Reasonably Achievable rule, it would also be ideal to reduce as much as possible dose delivered to healthy tissue. Value of Integral Dose for given organs depends on many factors, including the beam energy, density of surrounding tissue, dose calculating algorithm, margin size,5,8–10 but, primarily, on the choice of radiation technique. In prostate cancer therapy, in dynamic techniques, ID and low isodose location may be different depending on the number of beams for IMRT, number of arcs for VMAT, and the pitch factor for HT. Another factor, determining the value of ID may be the choice of an optimization process. In this pilot study, we report the use of two optimization processes for planning of the same patient to explore their inﬂuence over the value of the integral dose in the volume of healthy tissue and OAR.

Materials and methods

To prepare plans, ﬁve prostate cancer patients were selected. The patients had been previously treated with external beam radiotherapy. CTV was deﬁned between 28 and 51 cm3 (entire prostate – without nodes and seminal vesicles). CTV with 1 cm margin (unsymmetrical to the rectum site 0.7 cm) creating PTV extent 120–160 cm3 . Common part PTV and rectum did not exceed 15% of the volume of the rectum and the common part

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of the PTV and bladder did not exceed 25% of the volume of the bladder. The criterion for patients selection, besides PTV and CTV volumes, was organs at risk volume. Bladder filling was defined between 150 and 250 cm3 , rectum volume between 65 and 90 cm3 , femoral heads between 60 and 80 cm3 . Organs at risk and CTV contouring was performed by the same doctor. To determine normal tissue volume, which ranged from 17 to 25 l, two limits were used: the upper one – between third and fourth lumbar vertebrae, and the lower one – three CT scans below the biggest ring. To optimize data collection, five auxiliary structures were created: body ID volume (normal tissue volume defined earlier), a sphere with a margin of 1 mm around the PTV, created to make a high dose gradient between the target and healthy tissue volumes during the optimization process (used in IMRT and VMAT) and three rings. First ring of 2 cm around PTV, second of 2 cm around the first one and third of 2 cm around the second one. Ring structures were used to plan optimization by reducing the dose to healthy tissue. IMRT plan was made with the following geometry: 5 beams (0, 60, 110, 250, 300 deg), 7 beams (0, 50, 100, 150, 210, 260, 310 deg), 9 beams (0, 40, 70, 110, 150, 210, 250, 290, 320 deg). VMAT plans have been prepared with 1 arc (160–200 deg), 2 arcs (170–190 and 160–200 deg) and 3 arcs (181–179 deg and two previous combinations) geometry. Tomotherapy plans were prepared using three pitch factors: 0.215; 0.287 and 0.430. Parameters used in HT plans were the Modulation Factor (MF) = 2.6; Field Width (FW) = 1.0 cm and pitch factors defined earlier. For all 5 patients, unified optimization protocols were used for planning. Structures weight during the optimization were identical for IMRT and VMAT, and different for HT, because another treatment planning system was used for HT. Criteria of clinical constraints for OARs and PTV in all techniques were the same. For one patient, 18 plans were prepared (6 IMRT, 6 VMAT, 6 HT plans) – 9 with normal optimization (only one auxiliary structure – 1 mm around PTV for IMRT and VMAT and without this structure for HT) and 9 with rings optimization. Dose calculation algorithm in IMRT and VMAT optimization was AAA version 10.0.28 in the Eclipse treatment planning system by Varian, in Tomtherapy CCC version 4.3 in TomoTherapy Planning System by Accuracy. 6 MV X-ray beam was used in all prepared plans, and for IMRT and VMAT FF beam with Millennium 120 Leaf MLC. To calculate integral dose values for each patient, Aoyama formula was used, and the difference between normal tissue and CTV integral dose to calculate NTID.

Results

Differences in values of integral dose between techniques are not great, but we can point to lower ID in some of these groups and to some trends (Fig. 1). In the bladder, integral doses are similar for IMRT and HT techniques. For VMAT technique in this structure, they are slightly higher.

reports of practical oncology and radiotherapy 2 2 ( 2 0 1 7 ) 415–419

417

Fig. 1 – Mean integral dose values (point) with standard error (frame) of organs at risk and normal tissue (NTID) for all ﬁve patients. 5, 7, 9 = numbers of beams; 1, 2, 3 = numbers of arcs; 0.215, 0.287, 0.430 = pitch factor; Ropt = rings optimization.

Rectum integral doses are the lowest for IMRT techniques and the highest for VMAT and HT. Lowest integral doses for the femoral heads are for HT, then for VMAT and for IMRT. Only in 7-beam IMRT plans, values are similar to HT and VMAT techniques, in 5- and 9-beam plans, values of integral dose are higher.

NTIDs in VMAT, HT and 9-beam IMRT plans are similar, but higher in VMAT and 9-beam IMRT than HT in context of the value. Quite a high value of NTID can be seen in 5-beam IMRT plans, and a little bit lower in 7-beam plans. A trend to decrease ID value can be observed in the rectum with the number of beams and arcs increasing in IMRT and

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Table 1 – Mean ID values of normal and rings (Ropt) optimization, for all 5 patients. Technique and geometry

IMRT

VMAT

5/5 Ropt 7/7 Ropt 9/9 Ropt 1/1 Ropt 2/2 Ropt 3/3 Ropt 0.215/0.215 Ropt 0.287/0.287 Ropt 0.430/0.430 Ropt

Mean [Gy × l] Rectum

Bladder

Left femoral heads

Right femoral heads

2.76/2.60 2.72/2.63 2.66/2.56 2.93/2.92 2.84/2.80 2.73/2.72 2.94/3.00 3.02/3.05 3.08/3.02

4.78/4.73 4.72/4.64 4.58/4.55 5.16/4.93 4.83/4.79 5.02/4.88 4.40/4.44 4.49/4.51 4.62/4.45

1.23/1.16 0.89/0.84 1.20/1.22 0.91/0.88 0.95/0.93 1.04/1.00 0.79/0.77 0.78/0.75 0.79/0.74

1.36/1.30 1.04/0.98 1.27/1.26 0.90/0.88 1.05/0.97 1.13/1.09 0.83/0.80 0.82/0.78 0.83/0.76

VMAT techniques. The same can be seen in the bladder. In HT we have a poorly visible rising trend of integral doses with the increasing of the pitch factor value. In the femoral heads, a trend can be observed for the ID value to grow with the increasing number of arches in the VMAT technique, but in HT they are at the same level. The drop of ID value in 7-beam IMRT plans is strongly dependent on the plans geometry in the IMRT techniques. If the femoral heads are not directly in the axis of the beam, the ID value will be lower. A noticeable decrease in the value of the integral dose always occurs after rings optimization for every structure (Table 1). The differences between the mean values of the integral dose before and after rings optimization is well noticeable in the case of NTID, except for 0.215 and 0.430 pitch factor optimization of HT. Isolated cases of ring structures properly worked are also found in the OARs, for the bladder in the 0.430 pitch plans and for the rectum in 5- and 9-beam plans. The greater differences in the context of one technique are visible in the IMRT, particularly in the femoral heads and normal tissue dose value, but they are not observed in VMAT and HT. All analyses were prepared in Statistica 12 by StatSoft.

Discussion

Value of integral dose is closely linked with the volume which was calculated. To compare doses in a given location, we should know the volume of analyzed organs and the presented group should be uniform by volume. Other inﬂuencing factors are clinical constraints, priorities and weights used during the optimization process. They may affect the organs at risk, integral dose values and, indirectly, also the normal tissue integral dose value (NTID). Compared with Ślosarek et al. paper, in our patient group differences between the planning techniques used in the NTID value are not so large, with the smallest one for HT. In our pilot study, we observed a decrease in the dose to OARs and normal tissue in the dose volume histograms and in the isodose distribution of the CT scans, but we did not observe statistical signiﬁcance for all test volumes, techniques, geometries and factors. All we can say is that there are clear trends.

208

133.5/126.3 119.5/112.0 124.8/119.6 122.2/116.2 122.9/115.7 123.4/117.8 118.0/114.7 118.6/113.6 118.0/112.0

One of possible reasons for the lack of statistical signiﬁcance is the size of the patient group, which is small at the moment. In the future, the authors plan to increase patients group. As D’Suoza and Aoyama showed, the total energy deposited in the patient during radiation is dependent on the treatment planning parameters. Our study showed that planning parameters include not only the choice of planning geometry and planning technique, but also the choice of an optimization process, especially in the context of normal tissues. In view of our and previous results, it is clear that the choice of a planning geometry and optimization process has an impact on the values of integral doses in organs at risk and NTID values. The most extreme example of this is the comparison of the values of ID for the femoral heads in IMRT plans, another may be the rectum ID values (when more beams or arcs are used in this area, the dose can be distributed more sparingly). Probably due to the different algorithms used in the treatment planning systems in IMRT and VMAT, integral dose in all types of structures was smaller after rings optimization, and in HT it was not always smaller.

5. 4.

Normal tissue (NTID)

Conclusion

A general tendency can be observed for integral dose value to decrease in all structures after rings optimization. Better effect of rings optimization is noticeable in the IMRT and VMAT techniques. It is possible to satisfactorily reduce NTID without detriment to the PTV and OARs by the use of rings optimization.

Conﬂict of interest None declared.

Financial disclosure The study was funded by Greater Poland Cancer Centre, research task number 10/2015(102).

reports of practical oncology and radiotherapy 2 2 ( 2 0 1 7 ) 415–419

references

1. Ost P, Speleers B, De Meerleer G, et al. Volumetric Arc Therapy and Intensity-Modulated radiotherapy for primary prostate radiotherapy with simultaneous integrated boost to intraprostatic lesion with 6 and 18 MV: a planning comparison study. Int J Radiat Oncol Biol Phys 2011;79(3):920–6. 2. Marnitz S, Wlodarczyk W, Neumann O, et al. Which technique for radiation is most beneﬁcial for patients with locally advanced cervical cancer? Intensity modulated proton therapy versus intensity modulated photon treatment, helical tomotherapy and volumetric arc therapy for primary radiation – an intraindividual comparison. Radiat Oncol 2015;10:91. 3. Skórska M, Piotrowski T. Empirical estimation of beam-on time for prostate cancer patients treated on Tomotherapy. Rep Pract Oncol Radiother 2013;18(4):201–8. 4. Davidson MT, Blake SJ, Batchelar DL, Cheung P, Mah K. Assessing the role of volumetric modulated arc therapy (VMAT) relative to IMRT and helical tomotherapy in the management of localized, locally advanced, and post-operative prostate cancer. Int J Radiat Oncol Biol Phys 2011;80(5):1550–8.

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5. Aoyama H, Westerly DC, Mackie TR, et al. Integral radiation dose to normal structures with conformal external beam radiation. Int J Radiat Oncol Biol Phys 2006;64(3):962–7. 6. Fuentes-Raspall R, Inoriza JM, Rosello-Serrano A, Auñón-Sanz C, Garcia-Martin P, Oliu-Isern G. Late rectal and bladder toxicity following radiation therapy for prostate cancer: predictive factors and treatment results. Rep Pract Oncol Radiother 2013;18(5):298–303. 7. Polkinghorn WR, Zelefsky MJ. Improving outcomes in high-risk prostate cancer with radiotherapy. Rep Pract Oncol Radiother 2013;18(6):333–7. 8. D’Souza WD, Rosen II. Nontumor integral dose variation in conventional radiotherapy treatment planning. Med Phys 2003;30(8):2065–71. 9. D’Arienzo M, Masciullo SG, de Sanctis V, Osti MF, Chiacchiararelli L, Enrici RM. Integral dose and radiation-induced secondary malignancies: comparison between stereotactic body radiation therapy and three-dimensional conformal radiotherapy. Int J Environ Res Public Health 2012;9(11):4223–40. ˛ 10. Ślosarek K, Osewski W, Grzadziel A, et al. Integral dose: comparison between four techniques for prostate radiotherapy. Rep Pract Oncol Radiother 2014;20(2): 99–103.

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A novel approach to total skin irradiation using helical TomoTherapy

Practical Radiation Oncology (2013) xx, xxx–xxx

www.practicalradonc.org

Original Report

A novel approach to total skin irradiation using helical TomoTherapy Arman Sarfehnia PhD a,⁎, Emily Poon PhD a , Stephen D. Davis PhD a , Adam Fleming MD b , David Mitchell MD b , Carolyn R. Freeman MD c a

Department of Medical Physics, McGill University Health Centre, Montreal, Quebec, Canada Department of Hematology/Oncology, McGill University Health Centre, Montreal, Quebec, Canada c Department of Radiation Oncology, McGill University Health Centre, Montreal, Quebec, Canada b

Received 21 August 2013; revised 7 October 2013; accepted 9 October 2013

Abstract Purpose: To describe our experience with a novel technique for total skin irradiation using helical TomoTherapy (Accuray, Sunnyvale, CA). Methods and materials: An infant with refractory acute myelogenous leukemia with extensive cutaneous involvement was given total skin irradiation using inverse-planned helical tomotherapy. Quality assurance tests to determine the deliverability of the technique and the accuracy of dose estimation at the superficial skin level were devised and performed. Daily megavoltage imaging, tomotherapy plan adaptive evaluation, in vivo skin dose measurements, and cumulative dose summation were tools employed to assess the quality of treatment and positioning reproducibility on a daily basis. Results: The quality assurance checks showed that tomotherapy can indeed be used for total skin irradiation in cases where conventional electron treatment delivery is not possible. However, the overestimation of absorbed dose near surface by the treatment planning software must be quantified and taken into account using in-phantom and in vivo dosimetry techniques with appropriate detectors. Daily imaging allows for superior positioning, while daily plan adaptive and dose summations based on the plan adaptive calculations allow for evaluation of the treatment delivery. Conclusions: An infant has been treated successfully using helical TomoTherapy for total skin irradiation prior to allogeneic stem cell transplant. The course of treatment was uncomplicated and the patient is doing well more than 15 months following therapy. Crown Copyright © 2013 Published by Elsevier Inc. on behalf of American Society for Radiation Oncology. All rights reserved.

Introduction Conflicts of interest: None. ⁎ Corresponding author. McGill University Health Centre, Department of Radiation, Oncology, Rm L5-112, 1650 Cedar Ave, Montreal, Canada, QC H3G 1A4. E-mail address: asarfehnia@medphys.mcgill.ca (A. Sarfehnia).

Total skin irradiation is normally performed at our institution using a rotational technique with the patient standing on a rotating platform at an extended source-tosurface distance. 1-3 A high-dose-rate 6 MeV electron beam is used with a custom-built flattening filter to ensure

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a degraded beam that is relatively uniform in the central 80% of the large patient field size. Our requirement for uniformity is ± 10%, although our most recent in-air measurements have shown ± 3% uniformity. The decision to use total skin irradiation as part of the preparatory regimen for a stem cell transplant for an infant with refractory acute myelogenous leukemia (AML) with extensive cutaneous involvement therefore posed a challenge. Our solution was to develop a technique using intensity modulated image guided radiation therapy using 6 MV photons on a helical TomoTherapy (Accuray, Sunnyvale, CA) unit. To the best of our knowledge, such an approach has not been previously described in the literature.

Methods and materials Our patient The patient presented to hospital at 10 months of age with fever, respiratory congestion, and an extensive nodular skin rash. He was found to be mildly anemic, with severe neutropenia. He had no previous medical history except for recurrent upper respiratory tract infections. His skin surface was extensively covered with a variety of lesions, from superficial scaly patches to thicker erythematous nodules, with relative sparing of the scalp. On physical examination and imaging, there was no evidence of lymphadenopathy or organomegaly. Biopsy of a nodular skin lesion was positive for a leukemic infiltrate and a bone marrow biopsy showed acute myeloid leukemia (French-American-British [FAB] classification M5, acute monocytic leukemia). His cerebrospinal fluid showed many mononuclear cells and it was not possible to rule out central nervous system involvement by leukemia. He was admitted and treated with intensive chemotherapy as per the current Children’s Oncology Group protocol (AAML1031) with cytarabine, daunorubicin, etoposide, mitoxantrone, and bortezomib. Based on an excellent marrow response at the end of induction cycle 1, he was stratified as low-risk and received a total of 4 chemotherapy cycles as per protocol. His skin lesions markedly improved and disappeared during the treatment phase. However, skin nodules reappeared within 2 weeks of completing his treatment and a skin biopsy performed approximately 1 month after chemotherapy was positive for leukemia cells. Bone marrow biopsy showed 6% blast cells. His cerebrospinal fluid was negative. He was admitted for reinduction chemotherapy (“FLAG”; fludarabine, cytarabine, and filgrastim). 4 The skin lesions continued to progress over the following month, covering his entire body surface. The decision was made to treat him with stem cell transplantation using his brother’s stored umbilical cord blood as a stem cell source. Due to the refractory skin disease, it was decided to use a conditioning regimen that

Practical Radiation Oncology: Month 2013

included radiation therapy, to be given in 3 phases: first, total skin irradiation with a total dose of 14 Gy given in 7 daily fractions (2 Gy per fraction), then craniospinal radiation therapy with a single dose of 1.8 Gy, and then finally total body irradiation (TBI), with a total dose of 10 Gy given in 5 fractions (a single fraction on the first day of treatment and then twice daily on each of the following 2 days).

Total skin irradiation technique Planning The patient underwent computed tomography (CT) simulation under anesthesia in the supine position immobilized in a full body Vac-Lok cushion (Civco, Kalona, IA) along with a thermoplastic head mask. The whole skin surface was contoured and the planning target volume (PTV) was defined as a 3 mm rim of skin and subcutaneous tissue. Due to technical difficulties with accurate and reproducible placement of bolus, we chose not to use any bolus for treatment. Instead, we relied on in vivo film dosimetry for accurate surface dose measurement. Optimization was performed using TomoTherapy, version 4.0.4 software. A field width of 5.0 cm, a pitch of 0.287, and modulation factor of 2.5 were used. Four concentric rings of 5-mm width each were drawn inside the larger PTV ring. These acted as optimizing structures and were used to force the dose to drop at an acceptable rate (Fig 1). The maximum doses for the rings were set at 17.9, 17.0, 16.7, and 16.0 Gy. Complete blocks at the center of the brain, abdominal, and thoracic cavity were also used to further minimize beams traversing through the patient and force the TomoTherapy to deliver tangential beams along the outer contour for the most optimal solution. Delivery TomoTherapy-based total skin therapy relies heavily on appropriate positioning of the patient as well as motion management. Accuracy in positioning was accomplished through the use of the couch-indexed Vac-Lok cushion and head mask. Daily full body megavoltage imaging using MVCT scans were performed to ensure appropriate positioning and monitor any weight changes or deviations of the body contour from the original kVCT.

Verification techniques Prior to patient treatment To evaluate the accuracy of surface dose estimation by the treatment planning system (TPS), a planned dose of 2 Gy was delivered along the 3-mm rim of a cylindrical phantom. Several pieces of radiochromic film (GafChromic EBT3; Ashland, Inc, Covington, KY) film were taped onto the phantom during the delivery. The measured dose

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Practical Radiation Oncology: Month 2013

Total skin irradiation using helical TomoTherapy

Figure 1 (A) The planning target volume (PTV; red) and consecutive rings of optimizing structure to reduce the dose from surface toward the center. (B) The final dose–volume histogram achieved for the PTV and the consecutive rings. (For color version, see online at www.practicalradonc.org).

at these points was compared against the TPS-calculated dose. Two delivery quality assurance tests were done with solid water phantoms to verify treatment deliverability and accuracy. The proposed treatment was first delivered onto a slab phantom in which a piece of radiochromic film and an ionization chamber were inserted. As such, we ensured deliverability of the proposed plan, as well as the accuracy of the dose distribution along a coronal plane and the reference dose at a single point.

modulated treatment plan was created that enabled delivery of prescription dose to the body surface with relatively sharp drop off of dose at depth. Figure 2 shows the calculated dose distribution by the TomoTherapy treatment planning software in the 3 orthogonal planes.

During patient treatment TomoTherapy planned adaptive was performed daily for the entire duration of the treatment to determine accuracy of delivery and differences between delivered and intended dose distributions. Dose summation based on the plan adaptive distributions allowed for an evaluation of the total delivered dose following the completion of treatment delivery. Skin dose measurements using radiochromic films were performed on days 1, 2, 3, and 7. The films were distributed over the patient’s body, with several film pieces (1 cm 2 in size) placed below the mask and between the patient’s skin and Vac-Lok cushion or underneath the anesthesia tubing. These were to determine if there were hot or cold spots in regions where high density equipment was in contact with the skin.

Results Total skin irradiation technique Based on the technique described in the previous section and shown in Fig 1, an inverse planned intensity

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Figure 2 The dose distribution in the transverse (top), coronal (middle), and sagittal (bottom) planes.

A. Sarfehnia et al

Figure 3

Practical Radiation Oncology: Month 2013

Dose–volume histogram for some major organs at risk. (PTV, planning target volume.)

Figure 3 shows the standard cumulative dose–volume histogram (DVH) for the major organs at risk, and Table 1 gives the maximum, minimum, and average doses received by these structures. Figure 3 shows the overall dose distribution in 3 planes. All constraints were well within limits. Under anesthesia, patient motion was minimized and dominated by patient breathing. We evaluated this motion and deemed it acceptable for the level of required uniformity (ie, an allowed ± 10% variation in dose around the prescription dose). The patient tolerated radiation therapy well with only mild erythema over most of the skin surface and a more pronounced reaction around the mouth, genitals,

and buttocks, with mild dry desquamation. He went on to complete the transplant conditioning regimen with chemotherapy as planned. His course following stem cell rescue was relatively uncomplicated and he has no evidence of leukemia or graft versus host disease now 15 months post transplant. He has moderate to severe eczema, confirmed by multiple skin biopsies that have ruled out leukemia and graft versus host disease. Of note, the patient’s stem cell donor (his sibling) has suffered from moderate eczema since early infancy. The patient also has clinical skin findings consistent with Gianotti-Crosti syndrome (infantile papular acrodermatitis). These rashes have been successfully managed with antihistamines and steroid or emollient topical treatments.

Table 1 Maximum, minimum, and average doses for selected organs. Dose values shown in Gy

Verification techniques

Organ

Maximum dose

Minimum dose

Average dose

PTV Spinal cord Brainstem Optic nerve (L) Globe (L) Globe (R) Liver Trachea Heart Lung (L) Lung (R)

16.2 1.6 1.4 2.8 15.2 14.5 12.7 8.3 6.9 9.6 9.2

9.6 0.9 0.6 0.9 2.5 2.3 0.7 0.9 0.8 0.8 0.8

14.7 1.1 0.8 1.4 7.0 6.9 2.2 2.6 0.7 1.6 1.6

Dose profiles along a coronal plane as measured by the radiochromic film agreed with the TPS calculation. The ionization chamber measurement in a medium dose, low dose gradient region was found to be 5.9% higher than expected. Dose–volume averaging effect of the ionization chamber may have played a part in the slightly larger than expected discrepancy. The radiochromic film measurement showed that the TPS overestimated the skin dose by up to a maximum of 25%. From our previous experience with TomoTherapy and based on literature, 5 the overestimation of the surface dose by the TPS did not come as a surprise and was simply taken into consideration in the dose prescription.

L, left; PTV, planning target volume; R, right.

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Practical Radiation Oncology: Month 2013

Total skin irradiation using helical TomoTherapy

Figure 4 Differences in dose–volume histogram (DVH) and isodose lines between delivered (dashed) and calculated (solid) plans. All organs at risk agree well to within uncertainty. The planning target volume coverage is compromised partially due to difficulty with patient positioning. (A, anterior; L, left; P, posterior; R, right; ROI, regions of interest.)

In general, the in vivo film dosimetry confirmed our delivery quality assurance measurements. Our results showed that the TomoTherapy planning station overestimates the skin dose. Overall, we measured about 20 cGy lower for a calculated 200 cGy dose deposited close to the skin (ie, a 10% overestimation of the dose by the treatment planning software). Neither the thermoplastic mask nor the anesthesia tubing affected the skin dose distribution significantly and we did not observe any hot spots. Agreement between measurement and calculation in these regions was within 5%. Figure 4 shows the dose distribution and the DVH for a slice through the abdomen for summed daily delivered doses. This was performed following completion of the entire treatment, and compared with the planned distribution and DVH (ie, initial intent).

Discussion Using the TomoTherapy unit for total skin irradiation was an elegant solution to a difficult clinical problem. We were able to achieve good coverage of the PTV and good sparing of organs at risk including and most especially the lungs and kidneys. We accounted for the relatively higher dose at depth in the arms by omitting the arms from the PTV for the last 2 days of treatment. We accounted for the total body contribution (~ 2 Gy, including the dose from daily MVCT verification imaging) by reducing the TBI dose from our standard 12 Gy in 6 twice-daily fractions to 10 Gy in 5 fractions and then compensated for the lower

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TBI dose by adding a single fraction of 2 Gy to the craniospinal axis. Problems encountered included reproducibility between CT images and the treatment MVCT, and day-today setup during the 7 days of treatment, with, for example, changes in the abdominal girth that is not surprising in such a young child. One and sometimes 2 full body scans (0.25 cGy per scan) were necessary each day for positioning purposes. Although the DVHs of most organs at risk looked similar to those predicted by the TPS, summation of daily plan adaptives showed that the PTV coverage was not as conformal. Instead of 95% coverage of the target volume by the 14 Gy isodose as intended, the final distribution displays 95% coverage by the 13 Gy isodose line. Finally, a maximum underdosage of 13% to the skin surface was observed. However, for most areas we measured 3%-5% underdosage which we judged acceptable. Given the degree of difficulty in measurements and accurate positioning of the child, as well as in the spatial registration of the measured and TPS calculated dose, the agreement between the dose delivery and TPS calculated dose distribution was also deemed acceptable, and in practice was not associated with unacceptable toxicity.

References 1. Podgorsak EB, Pla C, Pla M, Lefebvre PY, Heese R. Physics aspects of a rotational total skin electron irradiation. Med Phys. 1983;10: 159-168.

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2. Freeman CR, Suissa S, Shenouda G, et al. Clinical experience with a single field rotational total skin electron irradiation technique for cutaneous T-cell lymphoma. Radiother Oncol. 1992;24:155-162. 3. Reynard EP, Evans MD, Devic S, et al. Rotational total skin electron irradiation (RTWEI) with a linear accelerator. J Appl Clin Med Phys. 2008;9:123-134.

Practical Radiation Oncology: Month 2013 4. McCarthy AJ, Pitcher LA, Hann IM, Oakhill A. FLAG (fludarabine, high dose cytarabine, and G-CSF) for refractory and high risk relapsed acute leukemia in children. Med Pediatr Oncol. 1999;32:411-415. 5. Ramsey CR, Seibert RM, Robison B, Mitchell M. Helical tomotherapy superficial dose measurements. Med Phys. 2007;34: 3286-3293.

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Strahlenther Onkol https://doi.org/10.1007/s00066-020-01743-4

COVID-19 pneumonia treated with ultra-low doses of radiotherapy (Ultra-COVID study): a single institution report of two cases.

ORIGINAL ARTICLE

COVID-19 pneumonia treated with ultra-low doses of radiotherapy (ULTRA-COVID study): a single institution report of two cases Elena Moreno-Olmedo1 · Vladimir Suárez-Gironzini1 · Manuel Pérez2 · Teresa Filigheddu2 · Cristina Mínguez3 · Alba Sanjuan-Sanjuan4 · José A. González5 · Daniel Rivas6 · Luis Gorospe7 · Luis Larrea8 · Escarlata López1 Received: 22 July 2020 / Accepted: 31 December 2020 © Springer-Verlag GmbH, DE part of Springer Nature 2021

Abstract Introduction Since the outbreak of coronavirus disease 2019 (COVID-19) pandemic, healthcare systems have focused their efforts into finding a treatment to avoid the fatal outcomes of severe acute respiratory syndrome due to coronavirus-2 (SARS-CoV-2). Benefits and risks of systemic treatments remain unclear, with multiple clinical trials still ongoing. Radiotherapy could play a role in reducing the inflammatory response in the lungs and relieve life-threatening symptoms. Methods We designed a prospective study of Ultra-Low Doses of Therapy with Radiation Applied to COVID-19 (ULTRA-COVID) for patients who suffer pneumonia, are not candidates for invasive mechanical ventilation and show no improvement with medical therapy. Results We present the preliminary results of two patients diagnosed with COVID-19 pneumonia treated with ULTRA-COVID. After one radiotherapy session, significant clinical response and a good radiological response was observed in both cases, resulting in both patients being discharged from hospital in less than 2 weeks after radiation treatment. Conclusion Preliminary clinical and radiological results suggest a potential benefit of treating COVID-19 pneumonia with ULTRA-COVID. ClinicalTrials.gov Identifier: NCT04394182

Keywords COVID-19 pneumonitis · SARS-CoV-2 · Radiation · Cytokine storm · Inflamatory response

Introduction Elena Moreno-Olmedo, M.D.

escarlata.lopez@genesiscare.es 1

Department of Radiation Oncology, La Milagrosa Hospital, GenesisCare, Madrid, Spain

Department of Internal Medicine, La Milagrosa Hospital, Madrid, Spain

Department of Radiophysics, La Milagrosa Hospital, GenesisCare, Madrid, Spain

Oral and Maxillofacial Surgeon, Universtiy Hospital Reina Sofía, Córdoba, Spain

Department of Radiation Oncology, GenesisCare, Seville, Spain

Department of Radiation Oncology, GenesisCare, Málaga, Spain

Department of Radiodiagnosis, La Milagrosa Hospital, Madrid, Spain

Department of Radiation Oncology, Vithas Valencia Consuelo Hospital, Valencia, Spain

The onslaught of coronavirus disease 2019 (COVID-19) has challenged healthcare infrastructures worldwide. In this evolving situation and with still many unanswered questions about the optimal therapeutic approach, healthcare systems worldwide have struggled with a rise of critically ill patients [1]. Although the majority of COVID-19 patients are asymptomatic, complications such as severe pneumonia, respiratory failure, or acute respiratory distress syndrome (ARDS) can occur, often leading to fatal outcomes for patients. Most of the time, these cases require intensive care unit (ICU) admission and invasive mechanical ventilator (IMV) support [2]. In the case of these critically ill patients, the host response against the virus appears to be mediated by a ‘cytokine storm or release syndrome (CRS)’, leading to a macrophage-mediated inflammatory mechanism (inflammatory M1-phenotype) [3] and ARDS, in the form of