Dental ceramics seminar/ dental implant courses by Indian dental academy by indiandentalacademy

DENTAL CERAMICS

Seminar by

Dr. M. SHANMUGARAJ Postgraduate Student

DEPARTMENT OF CONSERVATIVE DENTISTRY & ENDODONTICS SRI RAMACHANDRA DENTAL COLLEGE AND HOSPITALS CHENNAI

CONTENTS INTRODUCTION

STRUCTURE

HISTORY

TERMINOLOGIES

CLASSIFICATION

COMPOSITION

PROPERTIES

STRENGTHENING OF DENTAL PORCELAIN

CONDENSATION OF DENTAL PORCELAIN

FIRING PROCEDURE

STAGES OF MATURITY

ALL CERAMICS

CLASSIFICATION

CONVENTIONAL POWDER SLURRY CERAMIC HICERAM – ALUMINA REINFORCED PORCELAIN OPTEC HSP – LEUCITE REINFORCED PORCELAIN

54 56

DUCERAM LFC - HYDROTHERMAL LOW FUSING CERAMIC 60 PRESSABLE CERAMIC IPS EMPRESS

OPTEC PRESSABLE CERAMIC INFILTRATED CERAMIC INCERAM

CASTABLE CERAMIC DICOR CERA PEARL

73 79

MECHINABLE CERAMIC CEREC VITBLOCS MARK I AND II

CELAY BLOCKS

132

REFERENCES

136

INTRODUCTION

Man has been obsessed with duplicating, restoring and replacing various lost body parts like the limbs, ear, nose and eyes with artificial prosthesis and teeth being no exception. Restoration of teeth is not recent but ancient, dating back to 1st century Roman B.C. Many materials have been used to restore and replace a lost teeth or a part of it, of these ivory was popular but not without its disadvantages.

The quest for an artificial prosthesis similar to the nature tooth, both in function and esthetics, in the oral environment still remains as a foremost concern to the dentist, which has led to the use of CERAMICS in dentistry.

CERAMICS

Ceramics are defined as man-made solid objects formed by nonmetallic and inorganic raw materials that are baked at high temperatures. Stoneware and pottery are still made from impure clays, sand and feldspar minerals, and are baked in kiln,s First pulvering the raw materials into a fine powder and then adding water to obtain a working consistency for shaping and molding makes these objects. The unbaked

objects dried and placed in a kiln and heating to sufficiently high temperatures to make the individual particles coalesce into a solid mass.

Ceramics are nonmetallic, inorganic materials that contain metal oxides whose structure is crystalline, displaying a regular periodic arrangement of the component atoms and may exhibit ionic or covalent bonding. Also a low-fusing glass matrix filled with high-fusing filler. It is heated above the fusing temperature of the low-fusing glass but well below the temperature needed to fuse the high-fusing filler. The filler, as in composite resins, improves strength and esthetics.

Glasses are described as supercooled liquids, not structureless or truly amorphous like a gas. In liquids, structural units or arrangements of atoms exist as they do in crystalline solids, but these units are not arranged in a regular manner. Glasses and liquids differ in one respect â&#x20AC;&#x201C; in a glass, each atom has permanent neighbours at a farily definite distance while in a liquid the neighbours about any atom are continually changing. Glass is an inorganic product of fusion, which has cooled to a rigid condition without crystallization. Common glass is made of silica sand, sodium oxide and potassium oxide, and by adding aluminium oxide a plate glass is made. If silica is heated to 1000 oC and then gradually increased in temperature to 1500oC over the course of hours it changes

into cristobalite. Tridymatie is an impurity of cristobalite and is formed when the quartz is heated between 870-1470 oC. Enamels are closely connected to the glass industry as they may be compared to fusible glass made opaque by adding opacifiers.

Porcelain is a type of ceramic. All porcelains are ceramics but all ceramic are not porcelains. The traditional porcelain is composed of three naturally occurring minerals: pure white clay (kaolin), silica (quartz), and feldspar. After baking it is known as whiteware because of its color from the clay. The basic components of dental porcelain are silica and feldspar. Additional components are aluminium oxide as well as pigments and opacifying agents, depending on the application.

Ceramics, industrial porcelains and dental porcelains are fabricated from the same compounds, it is merely the concentrations of the various components that differentiate them.

STRUCTURE  0   0  Si  0 

 0   0  Si  0  0 

HISTORY OF CERAMIC

Aesthetics and durability of material in the oral environment has always been a foremost concern to the dentist and is still a foremost concern to the dentist.

The desire for a durable and aesthetic material is ancient although dental technology existed in Etrutia as early as 700 B.C. and during the Roman 1st Century BC.

Little progress took place in dental art from the beginning of the Christian era to about 1500 AD. This was described as the dark ages of physical activities, a probably there was much activity, creative though and invention, but records were either not kept or later destroyed.

Artificial teeth were made from 1. Animal products such as ivory teeth or bone These were unsatisfactory because they tend to deteriorate and disintegrate in the mouth and absorb stains and odour.

AMBROISE PARE (1562) is credited for having prepared artificial teeth from bone and ivory.

JACQUES GUILLENMEAU was a pupil of PARE, who prepared a substance by fusing certain waxes, gums, ground mastic, powdered pearl and white coral. This may have been the forerunner, in principle of esthetic fused porcelains, which appeared many years later.

2. Teeth taken from the mouth of dead persons The disadvantage were, • Expensive • Scared people • Developed a natural repugnance to put a corpse’s teeth into their mouth. • Repeated failures • Risk of transmitting diseases like syphilis

3. Bamboo The disadvantages of bamboo are esthetically poor and functionally not durable in the oral environment.

4. Mineral tooth or Porcelain tooth CERAMICS originally referred to the art of fabricating of pottery.

The term ceramic is derived from the Greek term “KERAMOS”, which means “A POTTER OR POTTERY”.

It is believed that this word is realized to a Sanksrit term meaning “BURNED EARTH”, since the basic components were clays from the earth, which were heated to form pottery (FRIEDMANN 1991).

Ceramic is a non-metallic, inorganic material.

The term

“CERAMIC” applies to a wide variety of materials, including metal oxides, borides, carbides, nitrides and complex mixture of these materials.

Ceramic objects have been constructed for thousands of years. The earliest techniques used were crude. It consisted of shaping the item in clay/soil and then baking it to fuse the particles together, which resulted in coarse and porous products such as goblets and other forms of potter. 21,000 BC; earliest man-made ceramic artifacts were dated. 5000 BC: clay pots were discovered.

Later development led to detailed stoneware items 100 BC: colored, glazed vessel made (Han Dynasty) 600 BC: translucent porcelain made (Tang Dynasty)

Egyptian faieces are the first to enamel a substructure with a ceramic venner. Their typical blue green hues resulted form metal oxides created during the firing process.

More recently the Chinese ceramist developed porcelain. Vitrification, translucency, hardness and impermeability characterized it.

In the 17th century, the Europeans attempted to develop porcelain of similar quality that of the Chines. By 1720â&#x20AC;&#x2122;s the Europeans mastered the art of manufacturing fine translucent porcelain. This lead to the

promulgation of information regarding the fundamental components of porcelain: KAOLIN and FELDSPAR.

In 1723, enameling of metal denture bases was described by PIERRE FAUCHARD, which initiated research in porcelain that imitates color of the teethand gingival tissue.

By 1774, a Parisian apothecary ALEXIS DUCHATEAU with the assistance of a Parisian dentist NICHOLAS DUBOIS de CHEMENT made the first successful porcelain dentures at the GUERCHAND PORCELAIN FACTORY, replacing the stained and malodours ivory processes.

NICHOLAS DUBOIS worked diligently at perfecting the invention (a very difficult achievement because the one-piece denture had to resist distortion during firing).

In course of his experiments, DUBOIS continuously improved his porcelain formulation and was awarded both French and English patent.

He termed them â&#x20AC;&#x153;UNCORRUPTIBLE TEETHâ&#x20AC;? that gained wide currency and for many years was synonymous with porcelain teeth.

In 1817, a French immigrant dentist, ANTOINE PLANTON introduced individual porcelain teeth in America. In 1837, CLAUDIUS ASH produced fine porcelain teeth and later went on to introduce “TUBE TEETH” which could be inserted over a post on a denture. It became widely accepted for use in bridges as well as in full dentures.

In 1851, JOHN ALLEN of Cincinnati patented “CONTINUOUS GUM TEETH” prosthesis consisting of two to three porcelain teeth fused to a small block of porcelain colored like gingiva.

The search for suitable tooth colored filling material continued and was led by the prominent artist-dentist ADELBERT.J.VOLCK who brought about somewhat unsatisfactory products as early as 1857.

The modern synthetic porcelain or silicate cements-porcelain inlays fashioned to fit prepared cavities precisely were marketed first in 1880.

In 1882, glass inlays (not porcelain) was introduced by HERLRST.

In 1885 LOGAN fused porcelain to platinum post thus resolving the retention problem. He termed them as “RICHMOND CROWN”. These crowns represent the first innovative use of metal ceramic system.

The first ceramic crowns and inlays were made by C.H.LAND in 1886. He fused feldspathic porcelain to burnished platinum foil (used as a substructure) with high controlled heat of a gas furnace.

Improvement in translucency and color of dental porcelains were realized through developments that ranged from the formulation of ELIAS WILDMENA in 1838 to introduction of vacuum firing in 1949.

The popularity of ceramic restoration declined with the introduction of acrylic resin into dentistry till 1940’s after which its popularity increased as the disadvantage of acrylic resin were realized.

Vacuum firing of ceramics resulted in denser and more translucent restorations than the air fired restorations.

In 1950’s and early 1960’s dental porcelains were developed with high coefficient of thermal expansion, which allowed compatibility with

dental casting alloys. This enabled the fabrication of porcelain fused to metal restorations.

Refinements in the mental ceramics systems dominated dental ceramic research during the past 35 years that resulted in improved alloys, porcelain metal bonding and porcelains.

All porcelain crown systems, despite its aesthetic advantage failed to gain widespread popularity because the chief disadvantage of early restorations was their low strength. This resulted in the usage of ceramic restorations in low stress situations such as anterior teeth.

But still

fractures of restorations were very common, which resulted in the development of higher strength materials.

The development of high strength ceramics followed 2 paths. The first approach was to use 2 ceramic materials to fabricate the restoration. A high strength but non-aesthetic core material is veneered with a lower strength aesthetic material. This approach is similar to the metal ceramic system, but its advantage over the metal ceramic system is that the ceramic core can be more easily masked than the metal substructure. The second approach is to develop a ceramic that combines good aesthetic with high strength. This technique has the additional advantage of not

needing the additional thickness of material to make a high strength core. However at present the strongest ceramics are non-aesthetic ceramics.

The popularity of all ceramic systems increased after the introduction of alumina reinforced dental porcelain.

Mc.LEAN and

HUGHES in 1965 were the first to introduce high strength porcelain into dentistry. They advocated the introduction of glass-alumina composites.

McLEAN used a relatively opaque inner core of high alumina content for maximum strength. This was surrounded by combination of body and enamel powder with respectively 15% and 5% alumina resulting in restoration that were 40% stronger than traditional feldspathic porcelain.

The technique was further developed by improving the fabrication technique of alumina core. Here the porous alumina was fused with a specially formulated glass by a process called slip casting. This material was called INCERAM (1988) whose strength is about 3 to 4 times greater than earlier alumina core material. Thus these materials have been used in high stress FPDâ&#x20AC;&#x2122;s.

Different oxides have been used to strengthen ceramics like magnesium and zirconium. The ceramics, which used MgO, were called INCERAM SPINELL, whose strength is less than INCERAM but its translucency is better. So used for anterior crowns. Zirconium oxides were the latest to be used to strengthen ceramics, which can be used in the case of posterior bridges.

High strength aesthetic ceramics have been developed again using glass-ceramic composite microstructure for improving strength. In one system molten porcelain is cast into a refractory mold formed by traditional loss wax technique. These are Castable ceramics and are called DICOR porcelain. These are transparent after casting and must be subjected to a carefully controlled 11 hours firing sequence to promote the mica crystal growth that gives the restoration its strength. This was introduced in 1972.

‘Shrink free’ all ceramic crown systems were introduced in 1980’s Eg.CERESTORE (1983: Cerestore injection-molded core by Sozio and Riley).

Manufacturers have introduced high strength ceramics using leucite [potassium aluminum silicate] crystals dispersed in glassy matrix.

Leucite is precipitated from feldspar is incorporated in metal-ceramic porcelain formulation to increase the coefficient of thermal expansion of ceramics to match that of the metal substructure E.g. OPTEC HSP, CERIMATE and IPS EMPRESS.

In 1989 Alceram a replacement for Cerestore was introduced. CAD/CAM [COMUTER AIDED DESIGNING / COMPUTER AIDED MANUFACTURING] has been introduced into dentistry as early as 1970 which has now revolutionized the designing and processing of all ceramic crowns and bridges by cutting down the time for impression making and processing of the ceramic crowns and bridges. E.g. CEREC 2, CEREC 3, CELAY, PROCERA (1993).

TERMINOLOGY

ALUMINA : The oxide of aluminum (A1O3)

ALUMINA CORE : A ceramic containing sufficient crystalline alumina to achieve adequate strength and opacity when used for the production of a core for ceramic jacket crowns.

ALUMINOUS PORCELAIN : Glass strengthened by the addition of alumina.

AMORPHOUS : Without definite form or shape; formless; without real or apparent crystalline form; uncrystallized.

CAD-CAM: Computer-aided design combined with computer-aided machining. In dentistry, laser mapping of a cavity preparation can be fed to a computer-controlled milling machine.

CERAMIC : Any of various heat resistant and corrosion resistant materials made by shaping then firing a nonmetallic metal, such as clay, at a high temperature; a compound of metallic and nonmetallic elements.

CERAMIC, DENTAL: A compound of metals (aluminum, calcium, lithium, magnesium, potassium, sodium, tin, titanium and zirconium) and nonmetals (silicon, boron, fluorine and oxygen) that may be used as a single structural

component as one of the several layers that are used in the fabrication of a ceramic-based restoration.

CERAMIC JACKET CROWN : An all-ceramic crown without a supporting metal substrate that is made a ceramic with a substantial crystal content (>50 vol%) from which its higher strength and / or toughness is derived; distinguished from porcelain jacket crowns which are made with a lower strength core material, usually aluminous porcelain or feldspathic porcelain.

CLAY : A

native

hydrated

aluminum

silicate,

produced

the

decomposition of rocks due to weathered (A1203, SiO2. H2O); insoluble in water and organic solvents but absorbs water to form a plastic, moldable mass, water serving as a lubricant between the colloidal particles; a widely distributed colloidal lusterless earthy substance, plastic when moist but permanently hard when fired, that is composed primarily of decomposed igneous and metamorphic rocks rich in the mineral feldspar in the form of crystalline grains <0.002mm in diameter, whose essential constituents are kaolinite and other hydrous aluminous minerals.

DISPERSION STRENGTHENING : A mechanism by which a crystalline phase of high strength and high modulus of elasticity is dispersed in an amorphous glassy matrix to produce a high strength composition. FELDSPAR : Any of a group of abundant rock-forming minerals occuring principally in igneous, plutonic and some metamorphic rocks and consisting of silicates of aluminum with potassium, sodium, calcium and rarely barium; X20, A12O3.SiO2 where X is either Na or K.

FELDSPATHIC PORCELAIN : A ceramic composed of a glass matrix phase and one or more crystalline phase one of which is leucite (K 20,A12O3, 4SiO2) which is used to create high-expansion porcelain that is thermally compatible with metal allow core substructures; a more technically correct name for this is leucite porcelain because feldspar is not present in the final processed porcelain nor is it necessary as a raw material to produce leucite crystals.

FLUX : (Latin fluere â&#x20AC;&#x201C; to flow) a substance used to promote fusion especially of metals or minerals; a substance (as rosin or borax) applied to surface to be joined by soldering, brazing or welding just prior to or

during the operation to clean and free them from oxide and promote their union; a substance (as borax) added in glassmaking for promoting vitrification.

FRIT : Materials of which glass is made after having been calcified or partly fused in a furnace but before vitrification; glass variously compounded that is quenched and ground as a basis for glazes or enamels; powdered glass; ceramic melt in which a glass is formed.

GLASS : Any of a large class of materials with highly variable mechanical and optical properties that solidify from the molten state without crystallization, that are typically based on silicon dioxide, boric dioxide, aluminum oxide or phosphorous pent oxide, that are generally transparent or translucent and that are regarded physically as super-cooled liquids rather than true solids. An amorphous inorganic usually transparent or translucent substance consisting typically of a mixture of silicates or borates or phosphates formed by fusion of sand or some other form of silica or by fusion of oxides of boron or phosphorous with a flux (soda, potash) and a stabilizer (lime, alumina) and sometimes metallic oxides for coloring; a non-crystalline brittle solid.

GLASS-CERAMIC : A solid consisting of a glassy matrix and one or more crystal phases produced by the controlled nucleation and growth of crystals in the glass.

GLASS-INFILTRATED DENTAL CERAMIC : A minimally sintered A1203 or MgA12O4 core with a void network that has been sealed by the capillary flow of molten glass; In-CERAM (A12O3) and IN-CERAM Spinell (MgA12O4) core.

INJECTION â&#x20AC;&#x201C;MOLDED CERAMIC : A glass or other ceramic material that is used to form the ceramic core by heating and compressing a heating ceramic into a mold under pressure; IPS Empress.

KAOLIN : Fine clay used in ceramics and refractories and as a filter or coating for paper and textiles.

KAOLINITE : A mineral, the principle constituent of kaolin, A12O3, 2SiO2.2H2O.

LEUCITE : White or gray mineral, KA1Si2O6, consisting of potassium aluminum silicate occuring in igneous rocks with a glassy fracture.

MICA : Any of a group of chemically and physically related mineral silicate, common in igneous and metamorphic rock each containing hydroxyl, alkali and aluminum silicate groups.

OPACIFIER : A white or pale cream-colored oxide, which is used to decrease translucency and act as a masking agent, often, tin oxide or titanium dioxide.

PORCELAIN : A hard, white, translucent ceramic made by firing a pure clay and then glazing with variously colored fusible materials; china; a white,

ceramic-containing glass with a glazed surface; ceramic containing minerals held together with glass.

PORCELAIN JACKET CROWN : One of the first all-ceramic crowns, made from a low strength aluminous core material and veneering porcelain usually utilizes a thin platinum foil substructure.

POTASH : K2CO3 [potassium carbonate]; K2 (OH) [potassium hydroxide]; any of several compounds containing potassium,

especially soluble

compounds, such as K20 [potassium oxide], KC1 [potassium chloride] and various potassium sulfates.

POTASH FELDSPAR : Orthoclase.

QUARTZ : A mineral, SiO2 consisting of a silicon dioxide that next to feldspar is the commonest mineral.

REFRACTORY : Capable of enduring or resisting high temperatures.

SAND : Consisting mostly of quartz commonly used for making mortar and glass.

SILICA : Chemically resistant dioxide, SiO2, of silicon that occurs naturally in the 3 crystalline modifications of quartz, tridymite and cristobalite, in amorphous and hydrated forms (as opal) and in less pure forms (sand, diatomite, tripoli) and combined in silicates that can be prepared artificially as a fine powder water glass or other soluble silicates and also in colloidal form, and that is used primarily in making glass, ceramics and refractories, in producing elemental silicon, its alloys and compounds.

SILICATE :

Any of numerous insoluble often complex metal salts containing silicon and oxygen in the anion, that constitute the largest group of minerals and with quartz make up the greater part of the earthâ&#x20AC;&#x2122;s crust.

SINTER : To cause to become a coherent mass by heating without melting: although there is not a fusion of the porcelain powder particles, they join together by flow on contact as a result of surface energy; densification by partial fusion. SLIP-CAST SLURRY : A fine particle ceramic dispersed in an aqueous liquid medium is poured into a porous mould, which rapidly extracts the liquid causing the formation of a close-packed but weak ceramic particle structure.

SODA : Any of various forms of sodium carbonate; chemically combined sodium.

SPINEL : Any of several hard, white, orange, red, green, blue, or black minerals with composition MgA12O4.

SWAGE : Shape to the form of a model, cast or die by compressive strength (porcelain teeth soldered to gold plates swaged to fit the mouth).

VITRIFICATION : (Latin vitrum â&#x20AC;&#x201C;glass) to change into glass or a glassy substance by heat and fusion.

CLASSIFICATION

ACCORDING TO TYPE 1. Feldspathic porcelain 2. Aluminous porcelain 3. Glass infiltrated aluminous 4. Glass infiltrated spinell 5. Glass ceramics

ACCORDING TO USE 1. Ceramic for artificial teeth 2. Jacket crown, inlay and onlay ceramic 3. Metal ceramic

4. Anterior bridge ceramic

ACCORDING TO PROCESSING TECHNIQUE 1. Sintered porcelain 2. Castable porcelain 3. Machined porcelain 4. Infiltrated porcelain 5. Pressed porcelain

ACCORDING TO FIRING TECHNIQUE 1. Air fired (at atmospheric pressure) 2. Vacuum fired (at reduced pressure) 3. Diffusible gas firing

ACCORDING TO FIRING TEMPERATURE 1. High fusing

- >1300 C

2. Medium fusing

- 1101 t0 1300C

3. Low fusing

- 850-1101C

4. Ultra low fusing

- <850C

ACCORDING TO SUBSTRATE MATERIAL 1. Cast metal 2. Sintered metal 3. Swaged metal 4. Glass ionomer 5. CAD/CAM.

COMPOSITION

Dental porcelains, to a large extent, are glassy materials. Glasses are super-cooled liquids / non-crystalline solids with only a short-range order in their atomic arrangement.

During cooling, molten glass

solidifies with a liquid structure instead of a crystalline structure. Such a structure is called vitreous and the process of forming it is known as vitrification. The principal anion present in all glasses is O 2 ion, which forms very stable bonds with small multivalent cations such as silicon, boron, phosphorous etc. (e.g.,. in silicon glasses, SiO4 tetrahedra are formed which are responsible for the random network of glass). These

ions are termed as glass formers. For dental applications, only two glass forming oxides â&#x20AC;&#x201C; silicon oxide and boron oxide are used to develop the principal network. Additional properties like low fusion temperature, high viscosity, color and resistance to devitrification is obtained by the addition of other oxides like potassium, sodium, calcium, boron or aluminum oxides to the glass forming lattice, SiO4.

HIGH FUSING PORCELAINS FELDSPAR Traditionally, the basic ingredients of these types of porcelains are feldspar kaolin (clay) and quartz. Feldspar is the primary constituent, and all porcelains based on feldspar are referred to as feldspathic porcelains. Natural feldspars can be either sodium feldspar (albite) or potassium feldspar (orthoclase / microline) which are minerals composed of potash (K2O), Soda (Na2O) Alumina (Al2O3) and silica (SiO2).

For dental purposes, light potassium based feldspar is

generally selected because of its increased resistance to pryoplastic flow and an increased viscosity.

The pyroplastic flow of dental

porcelain should be low in order to prevent rounding of margins, loss of tooth from and obliteration of surface markings. Feldspars are present in concentrations of 75 to 85% and undergo incongruent melting at temperatures between 1150째C and 1530째C. Incongruent melting is the process by which one material melts to form a liquid plus a different crystalline material. Hence a glassy phase is formed and suspended inside it are crystalline potassium alumino silicate crystals known as leucite.

KAOLIN / CLAY

Kaolin / clay (Al2O3, 2SiO2, 2H2O) serves as a binder. When mixed with water, it forms a sticky mass, which allows the unfired porcelain to be easily worked and molded. On heating, it reacts limitedly with feldspar (known as pyrochemical reaction) and thereby provides rigidly. It also adheres to the framework of quartz particles and shrinks considerably during firing. Unfortunately, pure kaolin is white in color and reduces the translucency of porcelain. Consequently, it is included only in small concentrations of 4 to 5%.

PURE QUARTZ Pure quartz is used porcelain as a strengthener. The main function of quartz (silica) is to impart more strength and firmness, and a greater translucency. Silica remains uncharged at the usual firing temperatures and hence contributes stability to the mass during heating by providing a framework for other constituents. It is present in concentrations of 13 to 14%. Traces of iron may be present as impurities in the quartz and must be removed to prevent discoloration of porcelain.

MEDIUM, LOW AN ULTRA LOW FUSING PORCELAINS The low and medium fusing porcelain powders are glass which have been ground from blocks of matured porcelain. For this, the raw ingredients are mixed and fused, and the fused mass is the quenched in

water. The rapid cooling induces stresses in the glass to the extent that considerable cracks and fractures occur. This process is referred to as fritting and the product so obtained is called a frit. The brittle material is then ground to a fine powder of almost colloidal dimensions. During subsequent firing, little or no pyrochemical reaction occurs, but the glass phase softens and flows slightly.

This softening allows the powder

particles to coalesce together (sintering) and form a dense solid. However, the temperature must be controlled to minimize the pyroplastic flow.

The raw ingredients for the low and medium fusing porcelains are basically the same as for the high fusing porcelain powders but in addition contain balancing oxides / fluxes.

These additions tend to

modify the properties by interrupting the glass network and hence are also known as glass modifiers.

GLASS MODIFIERS These acts as fluxes and help in reducing the softening temperature of glass by decreasing the amount of cross-linking between the oxygen and the glass forming elements like silica i.e., they disrupt the continuity of the SiO4 network. E.g., if Na2O is added, the sodium ions break the bridging Si-O-Si bond leaving behind two non-bridging oxygenâ&#x20AC;&#x2122;s. The

modifier concentration should not be too high, because if too many tetrahedra are disrupted, there may occur crystallization during the porcelain firing operations. The most commonly used glass modifiers are potassium, sodium and calcium oxides.

These are introduced as

carbonates that revert to oxides on heating. Other oxides added may be lithium oxide, magnesium oxide, phosphorous pentoxide etc.   0 0    0  Si  0  Si  0 + Na2O   0 0    0   0  Si  • •   0 

 0  Si  0 + 2Na+  0 

Diagram showing interruption of silica tetrahedral by sodium oxide.

INTERMEDIATE OXIDES The addition of glass modifiers not only lowers the softening temperature but also reduces the viscosity of the glass. A less viscous porcelain would have a lower resistance to slump or pyroplastic flow and

it is therefore necessary to produce glasses with low firing temperatures and a high viscosity. This can be achieved by using intermediate oxides lie aluminum oxide (Al2O3), which cannot actually form a glass but can take part in the glass network.

BORIC OXIDE Boric oxide (B2O3) serves as a glass modifier as well as a glass former.

The amorphous matrix of B2O3 is formed by the three

dimensional arrangement of BO3 triangles. Because the bonds extend in only three directions compared to four in SiO 4 the stability of boric oxide is weaker i.e., glass formed of boric oxide has a comparatively lower melting point, less viscosity and a higher expansion. When B2O3 is added to silica glass, the amorphous network consists of a continuous arrangement of SiO4 tetrahedra and BO3 triangles.

Inspite of the

continuous lattice arrangement, the softening point of glass is lowered because of the interruption of the more rigid and stable SiO 4 network by the BO3 lattice.

A typical low fusing porcelain can be shown to have the following composition.

Composition of typical low fusing porcelain Low fusing porcelain Glass Formers Glass Modifiers Intermediate oxides

Oxide SiO2 B2O3 CaO K2O NaO Al2O3

Weight percent 69.36 7.53 1.85 8.33 4.81 8.11

OPACIFYING AND COLORING DENTAL PORCELAIN The translucency of dental porcelain depends on whether a singlephase glass or mixture of glasses is used. If a single-phase glass frit is employed in which all of the constituents are completely taken into solution, the resultant product is highly transparent. In case of fluxed feldspathic porcelains, the degree of fusion and pyro-chemical reactions are limited to an extent such that some crystalline feldspar remains undissolved in the glassy matrix. This difference in refractory indices of the crystal and glass produces porcelain with opalescent or grayish blue translucency.

Another method of developing translucent gray or

opalescent characteristics in porcelain is the use of a mixture of two or more single phase glass frits of slightly different refractive indices.

The translucency of porcelain can be further decreased by using an opacifying agent. An opacifying agent is generally a metal oxide-ground to a very fine particle size of <5Âľm.

Zircomium oxide is the most

common opacifier employed and is usually incorporated into the concentrated color frit to be later added to the unfired porcelain. The difference between the refractive indices of the glass and the opacifier is the basic mechanism behind opalescence. Different wavelength of visible light are scattered differently by the opacifying particles. This effect depends upon the size as well as the volume distribution of the particles. Particles in the size range 0.4 to 0.8 Âľm generate a blue tinge in reflecting light and turn yellowish red in transmitted light. Preferably, the size of the particle should be nearly the same as the wavelength of visible light. Dentin porcelains are more opaque compared to enamel porcelains.

COLOURING AGENTS Pigmenting or coloring oxides are added to obtain various shades needed to simulate natural teeth. These pigments, generally metal oxides, are added to the glass used for porcelain manufacture and then subjected to the fritting process. The frit so obtained is highly color concentrated. These colored glasses are then finely ground and blended with the unpigmented porcelain powder to obtain the proper hue and chroma. The different colouring pigments used in dental porcelain are given in the table below.

Different coloring pigments used in dental porcelain Ferric oxide (black), platinum gray Chromium oxide, Copper oxide Cobalt Salts Ferrous oxide, Nickel oxide Titanium oxide Manganese oxide Chromium-tin, Chromium-alumina Indium

Gray Green Blue Brown Yellowish brown Lavender Pink Yellow / Ivory

STAINS AND COLOR MODIFIERS Stains are generally low fusing colored porcelains used to imitate markings like enamel check lines, calcification spots, fluoresced areas etc. Stains in finely powdered form are mixed with water or glycerine and water or any other special liquid. The wet mix is applied with a brush either on to the surface of porcelain before glazing, or built into the porcelain (internal staining). Internal staining is preferable as it gives more life like results and also prevents direct damage to the stains by the surrounding chemical environment. Color modifiers on the other hand are less concentrated than stains and are used to obtain gingival effects or highlight body colours, and are best used at the same temperature as the dental porcelain.

GLAZES AND ADD-ON PORCELAIN Glazing is done so as to produce enamel like luster after occlusal and morphologic corrections have been made in a porcelain restoration.

It also seals pores on the surface of a fired porcelain. The removal or reduction in the size and number of these surface flaws after glazing markedly increases the strength of porcelain by preventing crack propagation. It has been seen that if the glaze is removed by grinding, transverse strength may be only half that of glazed porcelain.

Glazing can be of two types: self glazing (autoglazing) and add-on glazing. In the self-glazing procedure, an external glaze layer is not applied but the completed restoration itself is subjected to glazing. Whereas in the add-on glazing, an external glaze layer is applied on the surface. Add-on glazes are uncolored glasses whose fusing temperature have been lowered by the addition of glass modifiers.

The thermal

expansion of an add-on glaze is also fractionally lower than the ceramic body to which it is applied.

This places the glazed layer under

compression and hence crazing or peeling of the surface is avoided. Disadvantages of add-on glazes are its low chemical durability, difficult to apply evenly and almost impossible to attain a detailed surface characterization.

Too high temperatures or prolonged glazing could result in increased pyroplastic flow of the material and hence roundening off of the line angles and loss of surface characteristics. Also, an over glazed

surface appears glassy and takes on the greenish hue of a natural glass thereby defying the natural enamel look. Add-on porcelains are generally similar to glaze porcelains except for the addition of opacifiers and color pigments.

Add-on porcelains should exclusively be used for simple

corrections of tooth contour or contact points.

PROPERTIES

Compressive strength

50,000 psi

Tensile strength

5,000 psi

Shear strength

16,000 psi

Elastic modulus

10X106 psi

Linear coefficient of thermal expansion

12X10-6 / 째C

Specific gravity

2.2 to 2.3

Liner shrinkage

Refractive index

High fusing -

11.5%

Low fusing -

14.0%

1.52 to 1.54

1. The compressive strength is quite high compare to tensile or shear strength.

2. The tensile strength is low because of the unavoidable surface defects. 3. The shear strength is low because of lack of ductility in the material. 4. Voids and blebs greatly reduce the strength of porcelain. 5. Blebs are internal voids tend to reduce the specific gravity of porcelain. 6. Porcelains extremely hard materials and because of this property offer considerable resistance to abrasion.

This could be a

disadvantage in that it causes excessive wear of the opposing natural tooth structure or the restorative material. 7. The brittleness â&#x2020;&#x2019; 0.1% deformation is sufficient to fracture porcelain before fracture. 8. Uranium oxide / cerium oxide is added to match the fluorescence of porcelain to that of the natural tooth. 9. Porcelain: a. Relatively inert. b. Chemically stable. c. Corrosion resistant. d. Highly biocompatible. e. Conducive to gingival health â&#x20AC;&#x201C; as it prevents plaque addition.

f. Solubility is less.

TWO FACTORS AFFECTING THE PROPERTIES 1. Manner and degree of condensation / compaction of power. 2. Degree of firing and procedure followed to fuse mass.

STRENGTHENING DENTAL PORCELAIN METHODS 1. Development of residual compressive stresses 2. Interruption of crack propagation

DEVELOPMENT OF RESIDUAL COMPRESSIVE STRESSES: The propagation of cracks from surface flaws is responsible for the poor mechanical behaviour of ceramics in tention, although it is also possible that flaws within the interior of the material can also cause fracture initiation under certain conditions. One widely used method of strengthening glasses and ceramics is the introduction of residual compressive stresses within the surface of the object. Strengthening is gained by virtue of the face that these residual stresses must first be negated by developing tensile stresses before any net tensile stress develops. For example, if the net compressive stress within a surface of

ceramic is 60 Mpa, it would take a total induced tensile stress of + 100 Mpa in this region to cause a fracture of the material.

Consider two strips of ceramic A, one that was subjected to a treatment that introduced a residual compressive stress of â&#x20AC;&#x201C; 100 Mpa into its surface and the other that was not treated. As the two strips are flexed equal amounts, the untreated strip develops tensile in its convex surface, whereas the treated strip merely experiences a decrease in the residual compressive stress. When the tensile stress in the untreated strip reaches + 60 Mpa, for example, the untreated strip fracture but the treated strip has a residual compressive stress of â&#x20AC;&#x201C; 49 Mpa remaining within its surface.

If the untreated strip breaks at 60 Mpa, the treated strip

subjected to the same force will still have â&#x20AC;&#x201C; 40 Mpa of residual compressive stress remaining. It would take an additional applied tensile stress of + 10 Mpa to bring the surface tensile of the treated strip to +60 Mpa.

This increase in applied tensile stress from 60 to 160 Mpa

represents a 200% increase in strength over the untreated strip. There are several techniques for introducing these residuals compressive stresses into the surfaces of ceramic articles. discussed below.

Ion Exchange:

Three of these methods are

The technique of ion exchange sometimes called chemical temperaturing, is one of the more sophisticated and effective methods of introducing residual compressive stresses into the surfaces of ceramics. This process involves the exchange of larger potassium ions for the smaller sodium ions, a common constituent of a variety of glasses. If a sodium-containing glass article is placed in a bath of molten potassium nitrate, potassium ions in the bath exchange places with some of the sodium ions in the surface of the glass article. The potassium ion is about 35% larger than the sodium ion. The squeezing of the potassium ion into the place formerly occupied by the sodium ion creates large residual compressive stresses (roughly 700 Mpa 100,000 psi) in the surfaces of glasses subjected to this treatment. These residual compressive stresses produce a pronounced strengthening effect. However, this process is best used on the internal surface of a crown, veneer, or inlay because this surface is protected from grinding and exposure to acids. One study has shown that grinding of only 100 Âľm from an external surface reduces the strength of the treated structure to its original value. Furthermore, contact with acidulated phosphate fluoride over a cumulative time of 3 hours removes most of the ion-exchanged layer as well. Not all ceramics are amenable to ion exchange. For example, alumina core materials, DICOR glass-ceramic core material, and some conventional feldspathic porcelains that are highly enriched with potash feldspar (K 2O,

Al2O3.6SiO2) cannot be sufficiently ion exchanged with potassium to warrant this treatment.

Thermal Tempering: Perhaps the most common method for strengthening glass is by thermal tempering.

Thermal tempering creates residual surface

compressive stress by rapidly cooling (quenching) the surface of the object while it is hot and in the softened (molten) state. This rapid cooling produces a skin of rigid glass surrounding a soft (molten) core. As the molten core solidifies, it tends to shrink, but the outer skin remains rigid. The pull of the solidifying molten core, as it shrinks, creates residual tensile stresses in the core and residual compressive stresses within the outer surface.

For dental applications, it is more effective to quench hot glassphase ceramics in silicone oil or other special liquids rather than using air jets that may not uniformly cool the surface.

Thermal Compatibility : Most metals expand linearly with temperature up to the melting range. Thus, a metal expands approximately the same amount when heated from 50oC to 60oC as it does from 200oC to 210oC.

Dental

porcelains behave differently; they have different values in different temperatures ranges, and, as a result, the thermal expansion or contraction of the porcelain cannot be precisely matched to that of the allow. Instead, the thermal behaviour of the metal and porcelain must be adjusted by the manufacturer in such a way that during the cool-down and properly directed so that the porcelain is not subject to immediate or delayed failure. Ideally, the porcelain should be under slight compression in the final restoration. This objective is accomplished by selecting an alloy that contracts slightly more than the porcelain on cooling to room temperature.

Consider three layers of porcelain: the outer two of the same composition and thermal contraction coefficient and the middle layer of a different composition and a higher thermal contraction coefficient. Suppose that the layers are bonded together and the bonded structure is allowed to cool to room temperature.

The inner layer has a higher

coefficient of thermal contraction and thus contracts more as it cools. Hence, an cooling to room temperature, the inner layer produces compressive stresses in the outer layers as previously described for thermal tempering.

This three-layer laminate technique is used by

Corning Glass Works to manufacture their dinnerware.

A similar rationale applies to porcelains and alloys for metalceramic restorations. The metal and porcelain should be selected with a slight mismatch in their thermal contraction coefficients (the metal thermal contraction coefficient is slightly larger), so that the metal contracts slightly more than the porcelain on cooling from the firing temperature to room temperature. This mismatch leaves the porcelain in residual compression and provides additional strength for the restoration. Disruption of Crack Propagation : A further, yet fundamentally different, method of strengthening glasses and ceramics is to reinforce them with a dispersed phase of a different material that is capable to hindering a crack from propagating through the material. There are two different types of dispersions used to interrupt crack propagation. One type relies on the toughness of the particle to absorb energy from the crack and deplete its driving force for propagation. The other relies on a crystal structural change under stress to absorb energy from the crack. These methods of strengthening are described later.

Dispersion of a Crystalline Phase : When a tough, crystalline material such as alumina (Al2O3) in particulate form is added to a glass, the glass is toughened and strengthened because the crack cannot penetrate the alumina particles as

easily as it can the glass.

The technique has found application in

dentistry in the development of aluminous porcelains (A12O3 particles in a glassy porcelain matrix) for PJCs. Another ceramic dental material that uses reinforcement of a glass by a dispersed crystalline substance is Dicor glass-ceramic. The cast glass crown is subjected to a heat treatment that causes micron-sized mica crystals to grow in the glass. When glassceramic restorations are subjected to high tensile stresses, these microscopic crystals will disrupt crack propagation, thereby strengthening the crown. In most instances, the use of a dispersed crystalline phase to disrupt crack propagation requires a close match between the thermal contraction coefficients of the crystalline material and the surrounding glass matrix.

Transformation Toughening : A new technique for strengthening glasses involves the incorporation of a crystalline material that is capable of undergoing a change in crystal structure when placed under stress. The crystalline material usually used is termed partially stabilized zirconia (PSZ). The energy required for the transformation of PSZ is taken from the energy that allows the crack to propagate. Experimental work has shown that transformation toughening may be a viable method for strengthening dental porcelains. One drawback of PSZ is that its index of refraction is

much higher than that of surrounding glass matrix. As a result, the particles of PSZ scatter light as it passes through the bulk of the porcelain, and this scattering produces an opacifying effect that may not be aesthetic in most dental restorations.

CONDENSATION OF DENTAL PORCELAIN

Porcelain powder is mixed with a liquid binder so that the particles are held together, and the thick creamy paste can be worked and built to the desired shape. The process of bringing the particles closer and of removing the liquid binder is known as condensation. Distilled water is the liquid binder used most commonly. However, glycerine, propylene glycol or alcohol has also been tried. The liquid because of its surface tension property serves as the binder. During subsequent firing it is eliminated, and the porcelain particles fill the space formerly occupied by the binder thereby resulting in shrinkage.

The aim of consideration is to pack the particles as close as possible in order to reduce the amount of porosity and shrinkage during firing.

Two important factors, which determine the effectiveness of

condensation, are the size and shape of the powder particles. If only onesize particles are used, even the greatest condensation is expected to leave a void space of 45 percent between the particles.

With two sized

particles, the void space is reduced to2 5 percent, and with three or more sized particles, the void space comes down to 22 percent. System that uses three sizes of powder is known as the gap grading system. In addition, the shape of the powder particles also governs the packing density. Round particles produce better packing compared with angular particles. The most important factor in condensation is the effect of surface tension. As the liquid is withdrawn, surface tension causes the powder particles to pack closely together. However, sufficient amount of liquid should be present so as to wet all the powder particles.

Several methods of condensation are employed (1) in the vibration method; the paste is applied on to the platinum matrix and vibrated slowly. This brings the excess water on to the surface, which is then drawn away with a linen or clean tissue. Excessive vibration should be avoided as it can cause slumping of the mass (2). In the spatulation method, a small spatula is used to apply and smooth the wet porcelain. The smoothening action disturbs the particles bringing them closer and also the water rises to the surface, which is removed as described earlier (3) Dry brush technique involves placement of dry powder onto the wet

surface. The excess water moves from mixture to the dry powder by capillary action and the wet particles are pulled together (4) In the whipping method, a large soft brush is moved in a light dusting action over the wet porcelain. This brings excess water to the surface, and the same brush can be used to remove any course surface particles along with the excess water. A combination of the vibration and the whipping methods can also be used. The mix is first vibrated and then whipped with a brush.

FIRING PROCEDURE Most of the thermochemical reactions in porcelain are completed during the manufacturing process. The role of firing is simply to sinter the particles of porcelain powder together to form a dense restoration. Some chemical reaction may however occur during prolonged firing or multiple firings, like the formation of leucite crystals in porcelain. During firing, the following changes are seen in the porcelain. The first change involves the loss of water, which was added to the powder to form a workable mass. The excess water is partially removed by slightly warming the mix before it is placed in the preheated furnace.

This

prevents the sudden production of steam that could result in voids or fractures. After the mass is placed in a furnace, both free and combined

water are lost of until a temperature or 480oC is reached. The second change occurs with a further rise in temperature when the particles fuse together by sintering. As a continuous mass is formed, there occurs a decrease in volume referred to as firing shrinkage (32-37% for low fusing and 28.34% for high fusing). The third change seen is glazing which occurs at temperatures of 955-1065oC. Glazing results in the formation of a glossy surface. After the mass has been fired, it is cooled very slowly because rapid cooled might result in surface cracking and crazing.

Porcelain restorations may be fired either by the temperature method or the temperature-time method. In the former, the furnace temperature is raised at a constant rate until a specific temperature is reached. In the latter, the temperature is raised at a given rate until certain levels are reached, after which the temperature is maintained for a measured period of time until the desired reactions are completed. Different media can be employed for firing like: a) Air b) Vacuum c) Diffusible gas

AIR FIRING PROCEDURE: All porcelain powder mixes have a certain amount of porosity present in them. When these porcelains are placed in the air furnace, the furnace atmosphere occupies these void spaces. Once the softening of glass begins, the grains of porcelain start lensing at their contact points. Surface tension causes some of the porosity to be swept out via the grain boundaries, but some of it gets entrapped by the flowing ceramic around the air voids.

With the increase in temperature, the void spaces

containing air assume a spherical appearance under the influence of surface tension. Still further rise in temperature increases the pressure of the entrapped air and the bubbles enlarge. Cooling decreases the pressure and hence the size of the bubble. The surface of air-fired porcelain is generally devoid of bubbles because intestinal air near the surface can escape easily. Whenever air-firing methods are employed, a very slow maturation period is preferred to allow for the maximum amount of entrapped air to escape. The porcelain should not be exposed to its full maturing temperature and it is advisable to stay 30 oC to 50oC below the maximum firing temperature.

POROSITY Bubbles or voids in the fired porcelain are caused by inclusion of air during firing or in some cases as a byproduct of vitrification of feldspar.

Porosity reduces both translucency and strength of dental

porcelain. Translucency depends on the number and size of the entrapped air bubbles. Large sized particles have fewer but larger air voids between them compared to small sized particles. Fewer bubbles, even of large size, give improved translucency. On the other hand, fine sized particles have multiple small air bubbles present in between them, which makes them highly opaque. It is, therefore, clear that porcelain powders fired in air must be of necessarily coarse nature. VACUUM FIRING This technique is used to reduce porosity in dental porcelains. It works on the basis of removing air or atmosphere from the interstitial spaces before surface sealing occurs. Although the vacuum (760 torr) removes most of the air from interstitial spaces, some of it is left behind. With the increase in temperature and because of surface tension, the remaining air spaces assume a spherical appearance. When air at normal atmospheric pressure is allowed to enter the furnace, it exerts a compressive effect on the surface skin, which further compresses the internal voids to one tenth of their original size. This results in a very

dense porcelain with very few remaining bubbles and that too of extremely small size.

Factors to be kept in mind while firing porcelain in vacuum are : 1. Porcelain powders must be dried slowly to eliminate the water vapour, and vacuum should be applied before the placement of porcelain in the hot zone of furnace. The interstitial spaces are hence reduced before the surface skin seals off the interior too rapidly. 2. Vacuum should not be applied after the surface skin has sealed and the porcelain has matured. Prolonged application can force the residual air bubbles to rise to the surface and cause surface blistering. Additionally, high temperatures can cause swelling of these blisters. 3. The vacuum should be broken while the work is still in the hot zone of the furnace. This permits the dense skin to hydraulically compress the low-pressure internal voids. 4. Vacuum firing cannot reduce the large sized bubbles to any significant degree. Hence, it is necessary to avoid porcelains with large interstitial spaces i.e., porcelain powders with small sized particles are preferred.

DIFFUSIBLE GAS FIRING In this technique, a diffusible gas like helium, hydrogen or steam is substituted for the ordinary furnace temperature. Air is driven out of the porcelain powder bed and replaced by the diffusible gas. With these gases, the interstitial spaces do not enlarge under the influence of increasing temperature, but decrease in size or disappear. This occurs because these gases diffuse outward through the porcelain or actually dissolve in porcelain.

VARIOUS STAGES OF MATURITY Several stages of dental porcelain have been identified when it is ‘sintered’ or ‘fired’. The common terminology used for describing the surface appearance of an unglazed porcelain is ‘bisque’.

Low bisque : The surface of porcelain is quite porous. The grains of porcelain begin to soften and ‘lense’ at their contact points. Shrinkage is minimal and the fired body is extremely weak or friable.

Medium bisque : Pores still exist on the surface of porcelain, but the flow of glass grains is increased. As a result, any entrapped furnace atmosphere that could not escape via the grain boundaries becomes trapped and sphere shaped. A definite shrinkage is evident.

High bisque: The flow of glass grains is further increased, thereby completely sealing the surface and presenting smoothness to the porcelain. In the case of non-feldspathic porcelains, a slight shine appears at this stage. The fired body is strong and any corrections by grinding can be made prior to final glazing at this stage.

ALL CERAMIC SYSTEMS

CLASSIFICATION 1. Conventional powder slurry ceramic • Hi Ceram – Alumina reinforced porcelain • Optec HSP – Leucite reinforced porcelain • Duceram LFC – Hydrothermal low fusing ceramic 2. Pressable ceramic • IPS Empress

• Optec Pressable ceramic 3. Infiltrated ceramic • In-Ceram 4. Castable ceramic • DICOR • Cera Pearl 5. Mechinable ceramic • Cerec Vitablocs Mark I and II • Celay Blocks • DICOR MGC

ALUMINA REINFORCED CERAMIC / ALUMINIOUS CERAMICS It was introduced by McLEAN and HUGES in 1965.

They

advocated the use of glass alumina composite. McLean used a relatively opaque of high alumina content for maximum strength surrounded by a combination of body and enamel powder 15% and 5% respectively, of alumina resulting in a restoration that has 40% more strength than traditional restoration.

Gradually high alumina ceramics developed which consisted of minimum 95% alumina. When alumina powder was fired first a welding

of contact points occur followed by normal sintering which, resulted in a unique fusing effect of partial fusion. Further there is a expansion of crystal lattice by migration of atoms which lead to movement of grain boundaries and reduction of porosity.

The strength of the crown

increased to about 800 Mpa.

Indications 1. There is a shoulder thickness of only 0.5 mm possible on the labial surface. 2. There is an occlusal clearance of more than 0.5 mm in lateral excursions. HI CERAM Hi-Ceram was developed in 1985 borrowing a technique from industrial manufacturing.

It is a system similar to aluminous core ceramic crown, using an epoxy die, a swaged resin coping and a conventionally applied ceramic.

Indications : 1. Anterior crowns 2. Posterior crowns where occlusal conditions are favourable. 3. Patients who do not want a metal core.

4. Patients who are allergic to metals. 5. Patients who require light reflection from tooth through the core of the crown for esthetic purpose.

Contraindication 1. For posterior crowns where occlusal stress is high.

OPTEC

HSP

(HIGH

STRENTTH

PORCELAIN)/OPTEC

(VENEER PORCELAIN)

Many porcelain systems cause wear to the opposing dentition during function, which usually necessitates nightguard use. New lowwear ceramics may remove the need for a nightguard in the future. With the advent of low-fusing, low-wear ceramics built over a pressable ceramic (Optimal Pressable Ceramic [OPC], Jeneric / Pentron, Inc.), has excellent esthetics, translucent margins and many of the new colors are designed to match bleached teeth. The Optimal System is the newest generation of ceramic powder, stemming from Jeneric / Pantronâ&#x20AC;&#x2122;s eight

years of research, development and clinical success with high-strength leucite based ceramic products.

Lifelike anterior metal ceramic restorations are very difficult to fabricate; even the most talent ceramist has difficulty producing natural color and translucency because of the metal core. The elimination of the metal framework or coping immediately increases the chance for esthetic success. Ceramic cores are either opaque or translucent; the opaque cores exhibit better fracture toughness. Translucency is better controlled with semi-opaque cores or when the porcelain matches the color and light transmission of the natural dentin as in the leucite-reinforced ceramics (Optec, Jeneric / Pentron, Inc.; IPS Empress, Ivoclar Williams). The strength needed for anterior crowns does not always call for a metal or ceramic opaque core.

According to Anusavice, “All-ceramic crowns

should be reserved for anterior and premolar teeth”.

It is a lucite –reinforced All ceramic material (leucite is 45-50%). IPS Empress and OPC basically are the same ; however, OPC’s leucite crystal (filler) is smaller, resulting in higher compressive strength (187 to 320 psi) and a flexural strength of over 23,000 psi. The process of heat pressing the ceramic rather than stacking the material differentiates OPC form IPS Empress.

It has 50% leucite in a glass matrix therefore stronger than conventional feldspathic porcelain. These leucite crystals are dispersed in a glassy matrix by controlling their nucleation during production. No core is required like Dicor. VP is higher in chroma than HSP.

Indications • Anterior Single Units. • Posterior Single Units. • Veneers.

Contraindications • Clenching and bruxism. • Short clinical crowns • Large or immature pulp chambers. • Abnormal occlusal relationships • Existing periodontal disease.

OPC is the second-generation product of IPS EMPRESS. OPC is 15% stronger. OPC has a clinical history of 8 years. OPC has 58 shades of porcelain powders compared to the 19 of IPS EMPRESS, which aids

in achieving the highest level of esthetics.

OPC is matched to the

universally used Vita shade guide system. No need to purchase a new chromoscope shade guide.

It is fabricated using injection-molding

technique.

PHYSICAL PROPERTIES

Flexural Strength It is approximately 167Mpa.

With OPC, Jeneric Pentron has

increased strength and reliability by reducing the size of the leucite crystal and improving its distribution without reducing the total crystalline content. This gives it a compressive strength of 187 to 320psi and flexural strength of over 23,000psi. Unlike a few other All-ceramic systems, Optimal is a bondable material, giving the entire tooth an additional measure of strength.

Translucency Its translucency is 3.

Marginal Fit Optimal provides an extremely high degree of fit to tooth. This results in increased load bearing capacity.

Low Fusing Ceramics Low fusing ceramics have been developed primarily for the use with titanium frameworks.

Titanium is now being used for metal

ceramics because of its biocompatibility and corrosion resistance.

Low fusion porcelains are required to adequately match the coefficient of thermal expansion of titanium to reduce residual stress, which may result in failure of the overlying ceramic.

The fusion temperature of these materials ranges from 650oC to 850oC. Lower fusing temperatures may also preserve the microstructure of the ceramics, in contrast to the high fusing material, which may suffer from dissolution of crystalline components.

PHYSICAL PROPERTIES Flexural Strength Flexural strength of low fusing ceramics is comparable to feldspathic ceramics.

Indications : â&#x20AC;˘ Used directly to fabricate all ceramic inlays, onlays and veneers.

â&#x20AC;˘ For repair and correction of metal ceramic margins.

DUCERAM LFC It is a low fusing ceramic.

It is composed of an amorphous

fluorine glass containing hydroxyl ions and the base layer composed of Duceram Metal Ceramic leucite containing porcelain.

Duceram LFC is then layered on base layer as a powder-slurry. It is then strengthened by ion exchange mechanism involving hydroxyl ions thus decreases the surface micro flaws and increase fracture resistance. It has a firing temperature of 702oC.

IPS EMPRESS

IPS EMPRESS is a heat-pressed glass-ceramic that has superior mechanical properties for several reasons. The high shrinkage of leucite crystals creates compressive stress in the vitreous phase, when prevents the development of surface cracks.

The randomly oriented leucite

crystals are tightly packed in the vitreous phase and stop the propagation of micro cracks. The combination of heat pressing, initial firing, and stain and glaze of the veneers creates an additional 50% in strength. The

higher cohesive strength and fracture toughness allow for thicker areas of porcelain with a lesser risk of fracture.

IPS EMPRESS glass-ceramic has been successfully used as metal free dental restorative in clinical situations for the past 6 years. Numerous studies confirm that this material fulfills the high standards of esthetics demanded form restorations such as inlays onlays and veneers.

IPS EMPRESS systems are characterized as follows: 1. It is an All-ceramic system. 2. It is a glass-ceramic system. 3. It is leucite reinforced. 4. It is based of principles of surface crystallization. 5. Features increased strength due to dispersion strengthening. 6. It is processed using a heat processing technique.

CHEMICAL COMPOSITION ON IPS EMPRESS The chemical composition of IPS EMPRESS glass-ceramic is given in weight %. • SiO2 – 59.0 to 63.0 • AI2O3 – 19. to 23.5 • H2O – 10.0 to 14.0

• Na2O – 3.5 to 6.5 • CeO2 - 0 to 1.0 • CaO – 0.05 to 3.0 • BaO – 0 to 1.5 • TiO2 – 0 to 0.5

Manufacturing of IPS empress glass-ceramic Initially a base glass whose composition is of particular importance is chosen this is important for controlled crystallization (at a later stage) is melted subsequently.

It is heat treated to initiate nucleation and

primary crystallization, and then it is grounded.

The powder to which the stabilizer, additives, fluorescent agent and pigments have been added is then pressed to form ingot. Once the ingot has been sintered to about 1200oC it is ready for sale on the market for processing in EP500 press furnace.

Fabrication of IPS Empress restoration : The fabrication of a dental crown according to layering technique, for example is characterized by wax up of a reduced model that is invested in a special investing material, after a muffle has been preheated the wax is burnt-out, it is placed in a EP500 press furnace (Ivoclar Company Limited, Schaan, Liechtenstein).

Subsequently, a glass-ceramic ingot for layering technique is pressed into the mould of the reduced crown at 1180oC according to the viscous flow process.

The crown framework is exposed to this

temperature for 35 minutes. It is then cooled, divested and finished. Then the ceramic incisal materials for layering technique for short â&#x20AC;&#x153;layering ceramicâ&#x20AC;? and glaze are applied. These materials are sintered at about 910 to 870oC respectively.

Glass-ceramic ingots for sintering

technique is preferred for fabrication of the various restorations like inlay, onlays, and veneers etc.

The ingot is pressed at 1050oC for staining technique.

This

provides IPS EMPRESS glass-ceramic with its ultimate strength and esthetic properties.

PHYSICAL PROPERTIES Flexural Strentth The basis strength of EMPRESS glass-ceramic has been shown to measure approximately 120 to 140 Mpa. The basic strength accounts to the EMPRESS glass-ceramic, which has been divided from the muffle but not exposed to further heat treatment of layering.

Heat processing the material significantly improves is flexural strength whereas heat-treating the material alone dose not. Additional firing after heat pressing further increases the material strength to about 140 to 220 Mpa. The flexural strength of the IPS EMPRESS glassceramic is the result of microscopic areas of compressive strain on the surface of the crown, inlays etc, produced by internal stress by heat. Significant increase in the flexural strength can be achieved by glazing the ceramic materials for the staining and the layering techniques.

Fracture Resistance IPS EMPRESS crowns have a good fracture resistance when compared with all other All-ceramic crowns. The fracture resistance of DICOR is not much higher than that of VITADUR.

The fracture

resistance of IPS EMPRESS is about 0.5 to 1 Kn. The fracture resistance of IPS EMPRESS greatly depends on the cementation method. Sandblasting, etching with HF and subsequently silanizing greatly increasing the fracture resistance. The fracture resistance is higher when the IPS EMPRESS is fixed with adhesive cements than conventional cements.

Fracture Toughness Dental ceramic can fail through growth of microscopic surface flaws that form during processing or from surface impact during service. New dental ceramics have been developed to improve resistance to crack propagation, which induced furomica, leucite, alumina and zirconia reinforced glass.

The leucite reinforced All-ceramic system, IPS

EMPRESS demonstrated significantly higher fracture toughness than alumina or fluromica reinforced materials DICOR and DICOR MGC.

INCERAM

SADOUN developed INCERAM in 1985.

It makes use of

aluminous core that is infiltrated with a glass to achieve high strength substratures that can support crowns and bridges. It belongs to a class of material known as interpenetration phase composites. These materials have at least two phases that are interveined and extend continuously from the internal to external surfaces. These material posses improved mechanical and physical properties when compared to the individual components.

They have improved fracture resistance and strength due to the fact that a crack must pass through alternative layer of components no matter what direction the crack propagates.

Composition of Inceram Al2O3 – 90.8% SiO2 – 3.6% K2O – 1.0% CaO – 0.04%

Fabrication Procedure An All-Ceramic restoration system INCERAM is based on the slip casting of an alumina core with its subsequent glass infusion. After the impression is taken the die is poured with special gypsum supplied with INCERAM, then the INCERAM ALUMINA is applied onto the die.

The alumina powder is mixed with deionized water supplied in pre-measured container.

Dispensing agent is added to create a

homogenous mix of alumina in water.

This mixture is sonicated in

VITASONIC thus initiating the dispersion process. applied to remove the air bubbles.

Then vacuum is

This solution of alumina is referred to as “slip” which is then painted onto the gypsum die with a brush. The alumina is built up to form a core for the ceramic tooth. The water is removed by the capillary action of the porous gypsum, which packs the particles into a rigid network.

The aluminous core is then placed in the IN-CERAMET furnace and sintered.

The cycle involves a slow heating of approximately

2oC/min to 1120oC for 2 hours to produce approximation of the particles with minimal compaction and minimal shrinkage of alumina. Sintering is only about 0.2% thus an interconnected porous network is created connecting pores on the outer surface with those on the inner surface.

Low viscosity lanthanum aluminosilicate glass is used to fill the pores in the alumina. The glass is mixed with water and placed on a platinum – gold alloy sheet. The external surface of the core is placed on the glass, which is heated in the IN-CERMET to 1100 oC for 4-6 hours. The glass becomes molten and flows into the pores by capillary diffusion. The excess glass is removed by sandblasting with alumina particles.

The last step is fabrication of INCERAM restoration involves application of aluminous porcelain to the core to produce the final form of restoration. The low viscosity lanthanum glass is used to infiltrate the alumina core in INCERAM.

This should be in air environment as

recommended by the manufacture.

The INCERAM aluminous glass

ceramic produced by lanthanum glass infiltration is about 50% translucent as dentin.

In clinical situations where there is a discolored preparation or a cast post and core this increased opacity over the dentin is advantageous were as when maximum translucency is necessary INCERAM ALUMINA is problematic. PHYSICAL PROPERTIES Flexural Strength The flexural strength of INCERAM ALUMINA varies from 300 Mpa to 600 Mpa. It is four times greater than other classes of dental ceramics. It is theorized that this high strength results from the primarily crystalline nature of this material and its minimal glassy phase. A flaw would have to propagate through its high modulus alumina to cause ultimate failure.

INCERAM material is not used as core alone ; they are also veneered with a low strength material to achieve the final esthetic result. The effect on strength of veneering cost a minimal drop in the strength of INCERAM ALUMINA material if the core remained at least 1mm thick. If the core material is thinned to about 0.5mm and then veneered with 1 mm thickness of porcelain, then the flexural strength drops to 255 Mpa. This should be adequate for incisors and bicuspids but not for molars.

Fracture Resistance The fracture strength of INCERAM ALUMINA is higher when compared to other all-ceramic systems. It is about 1060 (341 N).

Fracture Toughness Dental ceramics can fail through growth of microscopic surface flaws that form during processing or from surface impact during service. In Inceram alumina the resistance to crack propagation is improved by reinforcement with alumina. Fracture toughness is about 4.49 Mpa.m1/2 or 4.7 Mpa M-2.

Inceram Spinell A second-generation material, inceram spinell, is based on the inceram technique, has recently been introduced.

The technique of

fabrication is essentially the same as the original system.

The primary difference is a change in composition to produce a more translucent core. The porous core is fabricated from a magnesium – alumina powder to form the porous core after sintering instead of alumina powder as in INCERAM ALUMINA.

This type of material has a

specific crystalline structure referred to as “SPINELL”.

The porous spinell is secondarily infiltrated with a low viscosity, lanthanum aluminosilicate glass, which produces a more translucent substructure upon which Vitadur Alpha is veneered to form the final restoration. The glass infiltration of INCERAM SPINELL should be done in a vacuum environment.

INCERAM SPINELL is twice as translucent as

INCERAM ALUMINA because the refractive index of its crystalline phase is closer to that of glass and the vaccum infiltration leaves less porosity. The translucency of INCERAM SPINELL closely matches that of dentin.

Indications: • Anterior crowns • In clinical situations where maximum translucency is needed.

Contraindications : • Posterior restorations. • Anterior and posterior FPDs • In discolored preparations and cast posts as the level of translucency is excessive and leads to an overly glassy low value appearance.

PHYSICAL PROPERTIES Flexual Strength The flexural strength of INCERAM SPINELL is 15% to 40% that of INCERAM ALUMINA thus being indicated for anterior crowns only. About 350 Mpa. Fracture Toughness The fracture toughness of INCERAM SPINELL is about 2.7 Mpa M-2.

Inceram Zirconia INCERAM ZIRCONIA is also a second-generation material based on INCERAM fabrication technique. The difference is being a change in composition to produce a material that has improved flexural strength and fracture toughness.

The porous core fabricated with INCERAM ZIRCONIA has a tetragonal form of crystal. The porous core is secondarily infiltrated with a low viscosity, lanthanum alumino-silicate glass, which produces a stronger substructure.

Zirconia has a physical property called transformation toughening (strengthening) when an external source is applied to the material is goes through a phase transformation to a monoclinic form of zirconia. The monoclinic form of crystal is 3% to 5% larger, thus in places of micro cracks this process can seal the cracks.

PHYSICAL PROPERTIES Flexural Strength Flexural strength of INCERAM ZIRCONIA is twice as that of alumina. The highest strength at 800 Mpa.

Fracture toughness Also tough that of aluimina. It is about 6.8 Mpa M-2.

Indication • 3 unit FPDs for posteriors.

CASTABLE GLASS CERAMIC DICOR A glass ceramic is a material that is formed into the desired shape as a glass and subsequently heat-treated under controlled conditions to induce partial devitrification ir crystallization. This conversion process, which involves crystal nucleation and growth is referred to as “ceramming” and is accompanied by a small and controlled volume change. The crystalline particles, needles or plates formed during the ceramming process constitute an interlocking network, which increases the strength of the material by interrupting crack propagation. The first description of DICOR castable ceramic was given by Adair and Grossman in 1984.

The glasses ceramic material is composed of SiO 2, K2O, MgO, MgF2, minor amounts of Al2O3, and ZrO2 incorporated for durability, and

a fluorescing agent for esthetics. The fluoride acts as a nucleating agent, and improves the fluidity of the molten glass. After ceramming, the material is approximately 55% crystalline an contains tetrasilicic fluoride crystals (K2 Mg5 Si8O20Fl), which closely resemble mica. The refractive index of these crystals is close to that of the surrounding glass matrix, helping to maintain translucency in the devitrified body. Mica crystals are achromatic and the desired shade in final restoration is developed by adding external colorants. The disadvantage behind the use of these colorant stains is that they may be lost during occlusal adjustment, during routine prophylaxis or through the use of acidulated fluoride gels.

The fabrication method for DICOR restorations uses the lost wax and centrifugal casting techniques similar to those used for fabricating alloy castings. A wax pattern similar to the final restoration is made and invested in a phosphate bonded refractory material. Molten glass is then cast into the heated mould after dewaxing. The cast restoration is freed from the investment, covered by a protective â&#x20AC;&#x2DC;embedmentâ&#x20AC;? material and subjected to ceramming.

Addition of 2.5% lithium fluoride to the

embedment material may promote crystallization of mica and increase the fracture toughness of glass ceramic. The completed restoration is acid etched on its fit surface to enhance bonding to the underlying tooth.

Surface stains and colored luting cements are employed to improve upon the esthetics.

Properties The physical properties of DICOR are given in the table. PROPERTY

DICOR

ENAMEL

Density, g.cm3 Translucency Modulus of rupture psi Compressive strength, psi Modulus of Elasticity, 6 psix10 Microhardness

2.7 0.56 22000 120000 10.2

3.0 0.48 1500 58000 12.2

FELDSPATHIC PORCELAIN 2.4 0.27 11000 25000 12.0

362

343

450

Esthetic Qualities DICOR restorations are highly esthetic because of their translucency, which closely matches that of natural tooth enamel. The numerous small mica crystals that constitute castable ceramic closely match in their index of refraction to the surrounding glass phase. In addition, the castable ceramic permits a one-piece restoration made entirely of the same material, and no opaque substructure exists to impede light scattering. A chameleon effect is seen with DICOR restorations in which the restoration acquires a part of the colour from adjacent teeth and fillings as well as the underlying cement lute. Application of an external colouring system allows independent control over hue, chroma and value.

However, as mentioned before, there are chances of losing this external layer thereby defeating the best of esthetics.

Precision Of Fit It has been found to withstand 20 years of simulated toothbrush abrasion without any changes. The resistance of DICOR to chemicals and staining agents also compares favorably with conventional feldspathic porcelains. Little wear of the cast ceramic or the opposing dentition occurs when using DICOR restorations. Two reasons for this property are: a. Closely matching hardness between the cast ceramic material and natural enamel. b. The DICOR shading porcelains contain minimal abrasive opacifying agents.

Tissue Acceptance DICOR is chemically inert and has shown to pass all the biocompatibility tests.

The periodontal tissue reaction to DICOR is

considered quite favourable because 1. There is no need for opaquer porcelains to mask the metal substructure. These coarse grained opaque porcelains generally promote the adherence of plaque.

2. The absence of an opaque layer allows the technician to obtain natural contouring often found in metal ceramic restorations.

Little discomfort occurs on contact with hot or cold foods because of its extremely low thermal conductivity and a coefficient of thermal expansion, which closely matches that of natural enamel.

Radiographic Qualities The radiographic density of DICOR is similar to that of enamel allowing proper evaluation of the underlying structures and the margins.

Advantages 1. Excellent marginal fit 2. Relatively high strength 3. Surface hardness and occlusal wear is similar to enamel 4. Can reproduce wax patterns precisely by using the lost wax technique 5. Simple uncomplicated fabrication from waxup to casting, ceramming and colouring 6. Ease of adjustment 7. Excellent esthetics resulting from natural translucency

8. Inherent resistance to plaque accumulation (seven times less than on the natual tooth surfaces).

Disadvantages 1. Chances of losing low fusing feldspathic shading porcelains, which have been applied for good colour matching.

Uses Inlays, onlays, complete crowns and possibly partial tooth coverage restorations. It is not indicated for fixed partial denture or removable partial denture abutments with deep rests or internal attachments.

CERA PEARL Castable apatite ceramic was first developed by Hobo and Bioceram Group as CaO-P2O5-MgO-SiO2 glass ceramic. This material can be cast similar to the dental metal alloys. Its casting once obtained has an amorphous structure but when subjected to ceramming, crystalline oxylapatite, Ca10(PO4)6O results. This apatite is chemically unstable but

becomes stable when exposed to moisture by forming crystalline hydroxylapatite. Compared to normal enamel, the crystals of Cera Pearl show a somewhat irregular arrangement and this different arrangement probably accounts for its superior mechanical properties.

Cera Pearl is composed of CaO, P2O5, MgO, SiO2 and traces of other elements. CaO(45%) and P2O5 (15%) are the main ingredients in glass formation.

They are essential for formation of hydroxylapatite

crystals as well. MgO (5%) helps in the formation of hydroxyapatite and along with CaO decreases the viscosity of the compound when melted. SiO2(34%) in combination with P2O5 forms the matrix. Further SiO 2 regulates the thermal properties.

Because the crystalline constituent is similar to natural enamel, Cera Pearl is also expected to be quite biocompatible. The Youngâ&#x20AC;&#x2122;s modulus, tensile strength and compressive strength of Cera Pearl are appreciably higher than conventional porcelains and most restorative materials where as hardness compares favourably with the natural enamel. The values for these mechanical properties are given in the table below. Cera Pearl is indicated for both crowns and inlays. However, Cera Pearl is still currently in a research phase and is not yet commercially available. It is included in the text because it is a castable

glass ceramic and has properties that are comparable to other ceramic

Knoop Hardness Number (KHN)

Coefficient of Thermal Expansion (10-6 / C)

Thermal Conductivity (Cal cm/cm2secÂ°C)

11.0

.0023

220-240

14.4

390 70 590 120

11.4 7.0 12.0 25.0

.0022 .0014 .0024 .0540

39.0

.0026

(MPa)Tensile Strength

350

Youngâ&#x20AC;&#x2122;s Modulus (GPA)

590

103

150

140

80 20 70 58

14 70 80 70

390 280 170 360

185

Material

Cera Pearl Gold Alloy Enamel Dentin Porcelain Amalgam Composite resin

(MPa)Compressive Strength

materials.

SHRINK FREE CERAMIC CERESTORE It is a shrink-free alumina crown developed by the Coors Biomedical Co. and later sold to Johnson & Johnson. It is fabricated using lost wax technique and then injection molding to produce a coping. MgAl2O4 spinell and an alpha-alumina oxide make the core replaced by Alceram.

The use of a shrink-free ceramic coping formed on an epoxy

die by a transfer molding process overcomes the limits and firing shrinkage of conventionally produced aluminous porcelain jacket crowns. The Cerestore coping is veneered with conventional aesthetic porcelain.

Flexural strength: It is approximately 150 Mpa.

CERAMIC MACHINING SYSTEMS CAD-CAM

(Computer

Assisted

Design-Computer

Aided

Manufacturing) system has been introduced to the dental profession recently. Development of CAD-CAM system for the dental profession began in 1970â&#x20AC;&#x2122;s with DURET in France, ALTSCHULER in US & BRANDESTINI in Switzerland.

Optical scanning and computer generation of restoration were attempted as early as 1971 (ALTSCHULER 1971/1973).

With the

continued improvement in the technology, a number of systems are currently being investigated.

The teams most actively pursuing this

technology of CAD/CAM systems in dentistry are: 1. French group headed by Dr. FRANCOIS DURET. 2. Denti CAD units by Dr. DIANNE RCHOW. 3. CEREC system by MORMANN and BRANDESTINI.

The introduction of CAD/CAM system to restorative dentistry represents a major technological breakthrough. It is now possible to design and fabricate ceramic restoration at a single appointment, as opposed to the traditional method of making impression, fabricating a provisional prosthesis and using a laboratory for development of a restoration. Certain errors, which were inherent to the indirect method, have been eliminated in these systems.

Additionally CAD/CAM

generated save the dentist and patient time, provides an esthetic restoration and have the potential for extended wear resistance.

All CAD-CAM system are technically complex & involves three distinct and complex steps: 1. Collection of information 2. Designing of restoration and 3. Fabrication of the restoration

The popular CAD-CAM systems used in dentistry are: • CELAY system • CEREC system • DCS Precident system

• PROCERA system

CEREC CEREC is a dental CAD/CAM machine. CAD/CAM stands for computer assisted design, computer aided manufacturing. Mormann’s work led to the development of Siemens’ CEREC CAD-CAM system. It was developed in Zurich Switzerland. It is used to fabricate inlays, onlays, ¾ crowns, 7/8 crowns and veneers. This system enables the direct chair side placement of ceramic restoration without auxiliary laboratory support.

CEREC CAD/CAM machine is used to produce full ceramic restorations in one patient visit. It has been used clinically since 1986. CEREC 2 was introduced in 1996; CEREC 3 and Scan were introduced by Sirona Dental Systems (Germany) in 2000.

The CEREC technique consist of: 1. Three-dimensional scanning of the cavity or taking an optical impression. 2. Immediate data transformation and

3. Axial milling, which is integrated into a mobile unit.

Occlusal surfaces can now be machined on the Cerec 2 unit smaller pixel size/higher accuracy in depth measuring = increased resolution of the optical impression.

There are 3 different programs for design, Extrapolation, Correlation, and linear. (1) Anatomically adapted (extrapolation) (2) Correlated to functionally generated path (correlation

(3) Bucco-

linearly flat (inner).

The Cerec system is the only method in dentistry to permit the exact machining of ceramic veneers. The precision of Cerec 2 grinding unit improvements form the Cerec 1 system, in an SEM examination marginal widths of Cerce 2 were considerably smaller than Cerec1.

THE CEREC FAMILY: CEREC CAD/CAM was developed in ZURICH SWITZERLAND. It has been in clinical use since 1985.86.

Since the introduction of

CEREC CAD/CAM in 1985 there has been major advancement

CAD/CAM systems, which has resulted in the development of CEREC 2 AND CEREC 3 systems.

CEREC 3 is the latest version. CEREC 3 has many advantages over CEREC 2 system.

Those having CEREC 2 systems by

incorporating new software called CEREC L ink can exploit these advantages.

The following section gives a brief introduction to the

CEREC family.

CEREC: The CEREC was first introduced in 1986. it consisted of a mobile unite containing a small camera, a computer with scan and 3-axis-of rotation milling machine. This old milling machine was water-pressure driven â&#x20AC;&#x153;hydroâ&#x20AC;? version.

CEREC2: It is a tried-and-tested, compact CAD/CAM (Computer Aided Design-Computer

Integrated

Machining)

system

for

chairside

applications. It is the CAD/CIM system with the largest number of users worldwide, several million successful restorations and clinical experience since 1986. it consists of a mobile unit containing a small camera, a computer with scan and 3-axis-of-rotation milling machine. The milling

machine has an electric motor called “E” version to provide a better and smoother cutting of ceramic resulting in better fitting restorations.

The occlusal surfaces can now be machined on the Cerec 2 unit. It has smaller pixel size/higher accuracy in depth measuring which increases the resolution of the optical impression. There are 3 different programs for designing: Extrapolation, Correlation, and linear. (1) Anatomically adapted (extrapolation) (2) Correlated to functionally generated path (correlation) (3) Bucco-linearly flat (linear).

The precision of Cerec 2 grinding unit has been found to be 2.4 times higher than Cerec.

CEREC3: It is the modular CAD/CAM system that adapts flexibly to practice requirements. It provides virtually unlimited scope for incorporating the CEREC 3 modules into the practice layout. It gives flexible integration into the practice workflow (direct or indirect working; labside or chairside; one or more treatment sessions – the choice being yours). It provides rapid imaging, design, handling hygiene through the integration of the SIDEXIS intraoral X-ray system and the SIROCAM 2 intraoral camera.

CEREC 3 is flexible and offers the most advanced solution for every practice concept. The new highlight in the CEREC product range is the modular CEREC 3, which offers virtually unlimited scope to optimize practice workflow. Consisting of a separate imaging unit and milling unit, the CEREC 3 adapts to a wide variety of different practice layouts.

The systems are designed for multiple as well as single

restorations and enable to use the imaging unit for other tasks during the milling process.

The imaging and milling units can be located in one room or in separate locations. They communicate with each other either via cable or via radio signals.

The CEREC 3 milling unit can be installed in a wide variety of different locations like in the treatment room itself (essay access), in a cupboard (reduced noise), in an unused corner or niche (saves space), in the practice lab or as a fascinating eye-catcher in the waiting room.

The multiple functions of the CEREC3 imaging unit are creating optical impressions, designing the ceramic restoration, and chairside patient communication.

Advantages of CEREC 3: 1. The CEREC 3 imaging unit incorporates a mobile PC, which has been specially approved for medical applications. Milling chamber is separate form the imaging / designing unit. 2. The system is now Windows – based. 3. Cerec 3 can be used in conjunction with a Cerec 2 by using the “Link” software. 4. Two burs (one is tapered) do the cutting instead of one bur and one diamond wheel. 5. No “adjust” process (time savings) 6. Faster milling times (5 minute savings) 7. Greater occlusal anatomy 8. All design windows can be open at once 9. Help screen runs automatically and guides through the process.

MILLING CHAMBER: The new CEREC 3 software is Windows based allowing greater compatibility and sharing possibilities.

CEREC EQUIPMENT The intuitive user interface has been optimized for dental applications and does not require any specialist computer knowledge.

Equipment: • Flat panel monitor. • High-precision measuring camera. • Microprocessor-controlled image capture card, which processes the images from the 3-D measuring camera in real time. • Windows-based CEREC 3-Software.

The CEREC 3 imaging unit with SIDEXIS and SIROCAM 2 is designed for mobile applications as well as for integration into a networked practice system.

CEREC SCAN:

It is an entry-level model for indirect working. Low capital outlay is ideal for new practice start-ups. All processing steps can be delegated to the assistant.

Upgrade option: It can be turned into a fully-fledged CEREC system via the addition of an imaging unit.

Based on the CEREC 3 milling unit, the CEREC Scan has been optimized for the indirect working mode, i.e. the creation of ceramic restoration from dental models.

The resultant cost reductions make the CEREC Scan an attractive option for dentists who are setting up in practice for the fist time and whose financial resources are limited.

By adding the imaging unit at a later date the CEREC Scan can be converted into to a fully-fledged CEREC 3 system.

FABRICANTING PROCEDURE:

Following the preparation phase the assistant takes a conventional insitu impression and then produces a partial model made of quick-setting silicone This model is then clamped into the holder of the milling unit, where it is scanned by the built-in laser (duration: approx.5 minutes).

The design process is performed on a separate a PC in the dental practice. The actual production of the ceramic restoration takes place in the milling unit.

Although the CEREC Scan restorations are produced indirectly they can still be completed in a single treatment session, due not least to the speed of the laser scanning operation. The patient can watch the fascinating scanning and milling process “live”. The CERECE Scan is geared to the same broad range of clinical indications as the CEREC 3. The production process can be delegated to an assistant or dental technician in the practice laboratory.

This cuts costs and helps to

integrate the CEREC concept into the existing treatment procedure.

In LAB from SIRONA: Introduced at the 2002 Chicago Mid-Winter meeting, the inLab system is designed specifically for Laboratory applications. The idea is to use CEREC’s fast manufacturing processes for producing crown

“copings” and bridge “frameworks”. These substructures are to be milled from VITA INCERAM SPINELL, ALUMINA and ZIRCONIA blocks. The flexural strength of these materials is as follows: • INCERAM SPINELL: 350Mpa. • INCERAM ALUMINA: 550Mpa. • INCERAM ZIROCONIA: 750Mpa.

Ideally, the clinician and the technician can apply the appropriate strength material for varying clinical applications. Once the substructure has been milled, the technician glass infiltrates the pre-sintered framework and then builds up the final restoration with a traditional porcelain stacking procedure with VITADUR ALPA porcelain.

The process of building the substructure (coping or bridge framework) is as follows: 1) Scanning of the model 8-12 minutes 2) Designing the substructure (on a 5 minutes PC) 3) Milling the substructure 12-30 minutes 4) Glass infiltration 5-10 minutes A crown coping will take about 30 minutes to the finish. A bridge takes slightly longer at 57 minutes. Note however, the technician can be performing other functions during much of this process, namely the scanning and milling. Actual technician hands-on time is mere 5-15

minutes depending on the size of the restoration. This compares with a very long time to accomplish the same takes with regular INCERAM techniques, which is one of the main reasons INCERAM is not as widespread as it should be, but it should be because INCREAM has one of the best track records of ALL-CERAMIC materials.

Another bonus to this system over, says Procera is the choice of color matching. When the substructure is infiltrated with glass there is a choice of four colors. No opaqueing is required. This alone makes the inLab system more desirable but the laser scanning system is more accurate than mechanical systems. In fact the marginal accuracy of the inLabâ&#x20AC;&#x2122;s is excellent.

CEREC SOFTWARE The original software of CEREC system is the Cos 1.0. This was replaced with updated versions like Cos 2.0 and Cos 2.1, which are used for CEREC 2 systems.

Crown 1.30 and 1.31:

There have been many software upgrades since CEREC 2 came onto the market. Most of these upgrades have been offered to users free of charge.

CROWN 1.30 is the latest release. It replaces Crown 1.21 and allows to use the CEREC 2 with Link software version R600. Compared to working with R425, the PC constructs the milling data instead of the CEREC 2. This makes things much faster.

Other features include: • Continue milling after instrument change • Perfect adaptation of the restoration to the used block-size by automatic • Block-rotation prior or the milling, which leads to smaller blocks and longer lifetime of disk and bur.

CEREC 3 Software: The first software used for CEREC 3 systems was the R425. The CEREC 3 system now used the following software R600, R601, R800, R850 and the recently updated versions R900.

R425:

It is the older version, which does not allow transfer of data from PC back to CEREC 2.

R600: It allows all designs, including the Correlation & linear. It helps to save files (Restoration/Export) anywhere on your computer, or to send the file to any one of the drives (floppy, zip, CD, etc) or might have on your computer itself.

You can open files (Restoration/import) from

anywhere on your computer or your drives. When designing in Link, you can now choose which type of bur you want to mill with. This allows you to use your computer to generate the milling data for your CEREC 2 (your computer generates milling data faster than your CEREC2).

The CEREC 3 software is easy to use and produces optimum results. The CEREC 3 software like the corresponding hardware is based on a modular concept. We can choose the basic software for the creation of inlays and onlays or opt for the CEREC 3 Crown and/or CEREC 3 Veneer software packages. Whatever choice is made it produces highquality ceramic restorations simply, quickly and with the utmost reliability.

100

More than three quarters of all CEREC users deploy crown construction software. Compared with the previous versions, the new CEREC 3 Crown is even quicker and easier to use.

An example to illustrate how simple it is to create high-quality ceramic restorations will be given in the clinical procedure for CEREC system.

CEREC LINK: It is a software package, which allows CEREC 2 users to exploit all the functions of CEREC 3 (including parallel design and milling). It helps in export of CEREC 2 images to a PC, access to PC functions during the design process and parallel milling and design.

OPTICAL IMPRESSION: After tooth preparation the impression of the prepared tooth should be taken. In the CEREC CAD-CAM system instead of a conventional.

Impression with elastomeric impression material an optical impression with a CEREC camera is taken. Before taking an optical impression the prepared tooth surfaces are powdered with a special

101

powder, which has the ability to reflect the infrared light emitted from the camera.

BACKGROUND INFORMATION ON POWDERING: To take an optical impression it is necessary to powder (or opaque) the tooth surface to be imaged because of two reasons: The surface of the tooth must be covered with a non-reflective coating to make it easier for the infrared camera to see detail. Without the non-reflective coating the effect on the camera is similar to our looking into a very bright light. Because of the high translucency of enamel, without an opaque surface applied to the tooth, the infrared beam would be projected back to the camera from totally different depths within the tooth.

METHODS OF POWDERING: Powdering of the prepared tooth surface can be done using either: 1. BUTANE-PROPELLED POWDERIGN SYSTEM 2. PAINT ON SYSTEM or SCAN WHITE 3. POWDER MEISTER SYSTEM

BUTANE PROPELLED POWDERING SYSTEM: The butane-propelled powdering systems has been the most widely used powdering system with CEREC, as it was the first introduced

102

system of powdering but it has many disadvantages, which are as follows: it frequently clogs; even when a concerted attempt is made to hold the butane can upright. The powdering tubs are flimsy and easily deflected by the cheek or tongue. In order to change the direction of the powdering tube, a second hand is required, necessitating the clinician to let go of mirror or cheek.

PAINT-ON OR SCANEWHITE SYSTEM: The above difficulties with the butane powdering system have forced many users to use a paint-on system. This paint-on system called Scan White has its own disadvantages. In the January 1999 issue of the International Journal of Computerized Dentistry, the German clinician Andreas Lenzen listed these disadvantages: • The editing of the marginal line is usually unavoidable. • It is not always opaque in the case of dark backgrounds. • A relatively long time is required to remove it form dentin.

THE POWDER MEISTER: The powder Meister makes powdering easy.

With the

ergonomically designed powdering tube, there is no longer a difficult area of the mouth to place imaging powder. With only a slight twist of thumb

103

and index finger, the direction of powder flow can be changed with no interruption of the powdering process.

The rigid stainless steel

powdering tube can act as a cheek retractor and apply powder at the same time. In addition it is clog-proof and eliminates the need to constantly replace costly butane cans. The real advantage of the Powder Meister is its ability to place precise amounts of powder in very difficult access areas.

Notice the extremely even powder placement that is shown in this second molar area. The distal proximal box of the second molar as well as the mesial contact area of the third molar is well powdered. Being able to easily rotate the direction of the powdering tube with the same hand that holds the powdering device allows the clinician to easily place powder in any desired area with no difficulty.

This well powdered second molar preparation assures the clinician a well fitting restoration with a minimum of intraoral adjustment.

INSTALLATION: The powder Meister attaches to the air supply of the handpiece delivery system with a male quick disconnects.

The corresponding

female connection is installed in the handpiece delivery system and

104

controlled by the foot control. For clinicians not having an existing footcontrolled air supply going to a female quick disconnect, can easily and inexpensively be accomplished. The Powder Meister comes with a male quick disconnect with a convenient built-in/off switch which allows the clinician to easily activate the air supply to the Powder Meister.

POWDER MEISTER ADVANTAGES:  Clog-free operation  Even powder flow  Ergonomic design  Autoclavable tip  Durable construction  One-handed operation  An end to the need for expensive butane cans

CHARACTERISTICS OF THE THREE IMAGING POWDERS: VITA POWDER: Vita powder is titanium dioxide and zirconium oxide. Of the three powders, Vita is most likely to have larger “flames” of powder visible on the surface being powdered. However, Dr. Dennis Fasbinder, at the University of Michigan, found that there was no difference in the

105

resulting marginal gap between restorations made on test dies powdered with Vita powder or Dicor powder, which has a “smoother” appearance. DICOR POWDER: Caulk’s, Dicor powder is an excellent powder comprised of titanium dioxide, zirconium oxide, and talc. Dicor powder provides a wonderfully smooth powder flow absent of the larger “flakes” that are noticeable with the Vita powder. Dicor powder’s only disadvantage is the necessity of buying a new powdering tip with each bottle, which dramatically increases the cost.

PROCAD POWDER: Of the three powders, ProCad powders has the greatest flow properties. The highly dispersed silica and titanium dioxide mixture is so flow-able that it pours out of its bottle almost like you can imagine sand would pour. The advantage of ProCad powder is this “flow-able nature” which makes “snowdrifting”: and large flakes of powder the least likely to happen. The disadvantage of the ProCad powder is the tendency to be slightly messier in the mouth. The high flow properties allow the powder to escape beyond the area where the powdering tip is pointed. ProCad powder is also the most difficult to wash out of the mouth.

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HINTS ON POWDERING: IMAGING LIQUID: The imaging liquid is absolutely essential for excellent powdering. There are those who attempt to merely dampen the tooth with water to help the powder to stick which does not help as the same airflow that takes the powder to the tooth also evaporates the moisture that was intended to help adhere the powder. The imaging liquid is a glycerin and water combination that makes the surface of the tooth slightly sticky, causing the powder to adhere very well. The imaging liquid is applied generously to the area to be powdered and dry thoroughly before powdering.

ADJUSTING THE POWDER MEISTERâ&#x20AC;&#x2122;S POWDER FLOW: To begin powdering with the Powder Meister it is important to adjust the amount of air pressure going to the powder bottle. With the foot on the air supply foot control, open the air restrictor valve until powder just starts being expelled into the suction tube. Opening the air restrictor valve only a little bit more will provide ideal powdering. Using a minimum amount of airflow reduces the possibility of snowballs or snowdrifts.

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NOTE: Until getting used to powdering with the Powder Meister, it is suggested that smaller amounts of powder be placed in the bottle. Some clinicians report that placing rice or silica gel crystals in the powder bottle help remove excess humidity form the powder. In climates with high humidity in the air, the powder will collect too much moisture for good powdering. (The powder bottle can also be microwaved periodically to expel excess moisture.)

APPLYING POWDER TO THE PREPARATION: Before applying powder to the preparation, it is helpful to spray the first bit of powder on a non-critical area, such as an adjacent tooth. This frees the powder tube of any large flakes of powder and allows a preview of the powder flow. Any time the airflow through any powdering device (including the powder Meister) is stopped, powder settles in the powdering tube and a few large flakes form. Each time the flow is started again some of these large flakes can be seen as the powder is applied to the tooth. Being aware of this tendency is helpful. The easily rotated powdering tube of the powder Meister greatly minimizes the number of times it is necessary to stop and start the airflow.

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A common tendency is for clinicians to apply powder with too much air pressure. Less accidental “snow drifting” will occur with less air pressure. It takes a few more seconds to powder with less air pressure, but the consistency of results is worth the time. There are those clinicians that apply powder with the rubber dam in place. This might be essential with the conventional butane propelled powdering system, but is not necessary with the Powder Meister. The stainless steel powdering tube can easily be used to push a cotton roll away form the prepared tooth prior to powdering or to retract the cheek while powdering. As long as the tip is not completely immersed in saliva, it will not clog.

For

moisture control during powdering upper molars, a “Dry Tip” distributed by Microcopy and available through Patterson Dental, is much more effective than a cotton roll.

IMPROVING THE CHARACTERISICS OF THE POWDER: With the removal of Dicor powder from the market, the clinician can choose between the remaining two imaging powders, ProCad powder and Vita powder. Most clinicians find that ProCad powder gives a very grainy optical image and are frustrated by the large flakes and lumps that are found in the Vita powder. Vita powder can be filtered, which results

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in an optical image of a very high quality, almost equaling the results obtained with Dicor powder. To filter the Vita powder, stretch nylon stocking over the Vita powder bottle and fasten it in place with a rubber band. Touch the bottle to a plaster vibrator and collect the filtered powder in a cup.

POWDERING SUBGINGIVAL MARGINS: There is no reason why porcelain bonding needs to be limited to supragingival preparations however; if the margins cannot be seen they cannot be powdered. Exposing the margin of a subgingival restoration is quick, easy and predictable with electrosurgery. If the tissue is inflamed, there may be some bleeding following the use of electrosurgery. With the proper haemostatic technique bleeding can be easily controlled. Avoid using retraction string in porcelain bonding, as there is no good time to remove it. If it is removed prior to the bonding procedure, bleeding can be induced at a time when a totally dry field is necessary. Attempting to remove the string after the bonding procedure can be difficult since the string can be bonded to the tooth.

After the powdering of the prepared tooth surface is completed a hand-held camera is placed over the prepared powder-coated cavity to obtain a fixed image on the computer screen. The camera used for

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capturing the optical impression is CEREC camera.

The camera is

adjusted till a clear image and all aspects of the tooth so that the computer can read all internal walls cavosurfaces equally. This procedure is made easy by using the camera accessories like the C-STAT while taking the optical impressions.

CAMERA ACCESSORIES C-STAT is a camera accessory used to support SIROCAM 2 camera. The following section describes about C-STAT and how to use it with SIROCAM 2 camera for realization of exact digitalized picture of perfect angulation.

Without the C-STAT in place, the clinician tends to rest the end of the camera on the most posterior tooth in order to stabilize the camera. The result, over time, is an accumulation of small scratches on the tip of the camera lens. With enough accumulation these scratches can interfere with accurate z-values being read. Because this lens must be able to withstand autoclaving, it is quite sophisticated and therefore expensive ($900) to replace. The C-STAT not only protects this expensive lens, but the stabilizing tip is a wonderful camera support. The kit comes with 6 individual, autoclavable, C-STATâ&#x20AC;&#x2122;s.

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The inside of the support should not touch the camera prism while sliding the support on the camera. Make sure that the inside of the support is free of white impression powder, as it will avoid scratching the prism. In most cases the camera can be laid with the sliding support on the CEREC machine.

But be cautious to lay down a support with a wax impression when using the Function or Correlation programs.

In this case it is

recommended that the support be removed before putting back the camera. Then the camera is secure and the wax impression will not be damaged. When grinding the rests it is recommended to use a plastic bur. Then polish with an abrasive rubber wheel. Do not work with too much speed and too much pressure, and suction off the excess. To realize the best retention of impression wax perforate the rest base with a rose burr (no.24). Press the warmed wax on the perorated rest base and shape it with a wax knife or a scalpel. To prevent the prism form being smudged with wax, cut away the excess on the inside of the support. The white and the black supports are provided in the same shape. For instance you can use white ones for the anterior regions (veneers and anterior crowns) and the black ones for the premolar and molar regions.

ANTERIOR REGION:

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To take pictures form crown preparation in the anterior region, cut both rests to about 1.5-2 mm. The camera can be stabilized over the two rests on the incisal edges or the premolar cusps and rotated to the desired position.

PREMOLAR AND MOLAR REGION: For use in the premolar and molar regions, grind away the anterior rest. Taper the posterior rest by grinding it to a point. In this way realize a stable support in an interproximal space. To take the picture, slide the camera through the support, to find the appropriate position.

The

distance between the camera lens and the occlusal surface should be 4-5 mm. Angulate the camera slightly to the occlusal surface on the posterior rest of the support.

FUNCTION AND CORRELATION: GREEN For the Function and Correlation programs, which demand congruent digital pictures, it is recommended, to make an impression. Shorten the anterior rest and remove the posterior rest. Perforate the posterior rest base with a round burr (no-8) 6-7 times. With occlusal wax, such as Moyco Beauty Pink, make a small impression. It is easy to take another congruent picture with this positioning support.

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CHARACTERISTICS: C-STAT consists of plastics and can be cleaned in the thermodisinfector. Sterilization is possible till 135° Celsius. The rests can be modified with instrument and materials form to adapt the support to the different functions.

Once the camera is adjusted with the help of the C-STAT and a clear image of all the aspects of the cavity is obtained, the operator releases the foot pedal “freeze frame” the preparation on the screen.

The focal length of the camera lens is 10 mm. Any depth greater than 10 mm will not be focused properly and result in the generation of ill fitting restorations.

CONTROLLING THE TONGUE DURIGN THE OPTICAL IMAGE: Some patients have tongues that can be almost unmanageable during the taking of the optical image. This can be quite difficult because these unruly tongues will invariably wipe away the powder form critical parts of the tooth preparation or fight the camera position as it is being aligned.

This problem can be overcome by using Dry Tips by

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Microcopy. Dry Tips are water absorbant, and when placed between the tongue and the preparation, are extremely effective at protecting the preparation form intrusion by the tongue. When the camera is placed in the mouth, the camera pushes on the Dry Tip, which in turn pushes the tongue out of the way.

The proper software should be selected for designing and milling the restoration. These have been dealt with earlier in the section CEREC family under CEREC software.

More than three quarters of all CEREC users deploy crown construction software. Compared with the previous, the new CEREC 3 Crown is even quicker and easier to use.

DESIGNING OF THE RESTORATION: The restoration is designed from the images shown on the computer screen by using series of icons or symbols. The operator can electronically design the restoration by moving a cursor along the limits of the preparation thereby defining the boundaries.

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The internal limits are created, as are the walls and cavosurfaces margins.

Thus the gingival floor, axial walls, cavosurfaces margins,

proximal contours (contacts) and marginal ridges are established.

The procedure can be stopped at anytime and edited to override the computer and allow the operator to correct the electronically generated features. Once the restoration has been designed, the computer develops and onscreen, three-dimensional model or image of the inlay or onlay or veneer.

The entire information generated can be stored automatically on a programmed floppy disk. The design phase usually takes 2 to 8 minutes even when designing multiple cusp replacement or veneers.

An example of designing of a restoration is given below: â&#x20AC;˘ The following examples illustrate how simple it is to create highquality ceramic restorations â&#x20AC;˘ Begin by selecting the type of restoration (inlay, onlay, partial crown, crown or veneer), the design method (extrapolation, tooth database, correlation or function), as well as the tooth in question.

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• The optical impression can be taken directly in the patient’s mouth or from a model. The outcome is a three-dimensional data model, which is automatically stored. • Begin by encircling the equators of the neighbouring teeth. Following this you trace the precise baseline. The integrated tooth database adapts the selected restoration to the anatomical situation of the neighbouring teeth. • The orientation of the crown and the height of the proximal marginal ridges are determined on the basis of the neighbouring fissures • The positions and height of the cuspal apices are calculated wit reference to the neighbouring teeth and then displayed. All the other design lines are calculated automatically. The restoration is then ready for immediate milling. Alternatively, you can view each design step in turn and modify each line individually. • If you decide not to mill the restoration immediately, you have the option of viewing the equator and the relevant contact points with the neighbouring teeth. Various viewing modes and cross sections allow you to cheek the thickness and height of the contact points. • In this window you can view any cross-section of your choice through the restoration.

All the verticals can be individually

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edited.

In addition, this window allows you to determine the

thickness of the ceramic material in the occlusal region.

MILLING PROCEDURE: After all the data have been supplied, the computer selects the size of the ceramic block required. There are many types of preformed blocks present commercially to be used with CEREC CAD/CAM system.

The blocks used in this system are as follows: • 3M MZ100 • VITA Mark II and Master • Ivoclar ProCAD • VITA Mark II Esthetic Line • VITA Alumina and Spinell • Other blocks

3M MZ 100:

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3M Paradigm MZ100 Block for CEREC is made from 3M Z100 block material contains 85 wt% ultrafine zirconia-silica ceramic particles that reinforce a highly cross-linked polymeric matrix.

The polymer

matrix consists of bisGMA (Bisphenol A diglycidyl ether dimethacrylate) and TEGDMA (tri[ethylene glycol] dimethacrylate), and employs a patented ternary initiator system. The characteristics of 3M MZ100 are as follows: The Mark II Vitablocs The Mark II Vitablocs, manufactured by Vita, represent the second generation of CERECVitablocs. Manufactured from a new fine particle dental ceramic with wear characteristics similar to natural tooth enamel. This means a CEREC restoration made of Mark II blocks does not wear the opposing enamel cusps any more than natural tooth enamel does.

Traditional dental ceramic restorations cause a noticeable higher rate of wear in the opposing enamel cusp. On this subject a study was carried.

Out by Dr. I. Krejci et al. in the Dental Institute of Zurich. The results have been published.

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The microstructure of CEREC Vitablocs makes the material very easy t grind, finish and polish. The homogenous microstructure also enables better, more even and retentive results of acid etching. This is essential for achieving a secure bond between restoration and natural tooth substance by means of the adhesive technique.

The flexural strength of the Mark II material has been considerably improved and amounts to approximately 160 Mpa. ProCAD BLOCKS: ProCAD blocks have just recently been introduced to the market form Ivoclar.

Like Ivoclar’s popular Empress material, ProCAD is

reinforced with tiny leucite particles, and has been referred to as “Empress on a stick”.

Notes on usage: 1.

ProCAD blocks are held in place by a new screw (Patterson item # 84050013).

Since ProCAD is a harder material a new lubricant must be used (75ml per water tank) or you may double up on the current Dentatec lubricant (i.e. use 50ml instead of 25 ml).

Bur/wheel life will be shortened if you mill the two materials on the same instruments.

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Every ProCAD propellant comes with a new nozzle.

Shade cross-reference: 100 = A1, A2, B1, B2, C1 200 = A3, A3.5 300 = B3, B4 400 = C2, D2, D3 500 = A4, C3, C4, D4

In order to stain and glaze the ProCAD material, it’s recommended to use the ProCAD shading paste, but other stains have also worked.

ALUMINA AND SPINELL COMPING BLOCKS: The Alumina and Spinell coping blocks are available for doing InCeram crowns. The dentist or assistant makes an Alumina or Speinell coping (using the “Lab” software which comes with CEREC II) and sends the coping to the lab. The coping is then glass-infiltrated and the technician applies layers of InCeram Porcelain, which is fused to the coping making a very strong and esthetic crown. Alumina blocks are for posterior copings and the Spinell blocks are designed for anteriors.

Megadenta Bloxx is available only in Europe and have one, two or three shades incorporated into each block.

Once the desired size block is selected then it is mounted on a metal stub, which allows it to be inserted into the milling unit. After the

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block is inserted the small window is closed and the milling device is activated. The milling is accomplished by a three-axis-of-rotation cutting machine, which mills 25-Âľm slices.

A diamond wheel is driven by electric motor, which generally takes 4 to 7 minutes to complete the procedure.

The milling allows for the occlusal contours of all cuspal inclines, marginal ridges and proximal contours. It does not provide for internal and secondary occlusal anatomy. The operator develops this Intraorally after the inlay has been cemented.

For milling of crown copings and bridge-frameworks with CEREC in Lab the long-tapered-diamant and the cylinder-diamant with a diameter of 1.6 mm are used. The usage of the 1.2mm cylinder-diamant, to mill outer shape of copings and bridge frameworks, gives no benefits. The long-tapered-diamant has to be screwed to the left side and the cylinerdiamant to the right side. Care should be taken, when changing worn diamants.

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The 1.6 mm (long) diamant is used for the vast majority of restorations. The 1.2 mm is used mainly for anterior restorations and crown with endodontic posts.

LONGEVITY OF THE CYLINDER The number of millings that are possible wit a cylinder are a function of the type and size of restoration, whether or not extended milling is used, and the kind of material (Vita Mark II or ProCad) being milled. Extended milling increases not only the milling time but also the amount of wear on the cylinder. It has been shown that milling ProCad blocks slightly decreased the life of the milling instruments. Using extra Dentantec solution and tooth preparations free of irregularities will prolong instrument life.

The larger the restoration, the older the cutters and the use of extended milling all make the estimated time longer.

DENTATEC SOLUTION AND EXTENDED MILLING: While milling too much heat is generated. This heat generated is harmful to the milling machine and the diamants used. So it should be dissipated using a coolant like Dentatec solution. change of water at the start of every 6th milling.

Cerec suggests a

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The Dentatec solution also act as a lubricant in the milling process. In addition to providing a lubricating function, which increases the life of the milling instruments, the solution also contains an antimicrobial. Even with the antimicrobial, if the CEREC 2 is not used for a period of time, an odor come form the milling chamber. To eliminate this, change the water after prolonged period of unuse.

When the milling pictogram is clicked the CEREC 3 software tells what size of ceramic blocks is required. Then insert the corresponding block into the milling unit and initiate the milling process. The imaging and milling units communicate via a wireless link (option).

Before the milling process begins the computer control system automatically detects and compensates for tool wear. A cylindrical and a conical diamond burr shape the restoration. The conical burr enables very fine details to be created on the occlusal surface.

SPEED OF CEREC CAD/CAM SYSTEM: The main advantage of using CEREC CAD/CAM system is its speed in manufacturing a restoration in a very short period of time. The

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following table shows the time taken to produce various restorations by using CEREC CAD/CAM system.

Process step

Coping

bridge framework

Scanning (automatic)

approx. 10min.

approx. 20min.

Design

approx. 2min.

approx. 6min.

Milling (automatic)

approx. 15min.

approx. 50min.

STAINING AND GLAZING: In certain circumstances it may be necessary and/or appropriate to â&#x20AC;&#x2DC;naturalizeâ&#x20AC;&#x2122; the CEREC restorations.

This can be accomplished by

adding stain to the restoration and then firing (glazing) it in an oven.

The Ney Miniglaze oven is a simple, manual and inexpensive chairside oven available for this process.

To add porcelain a more

expensive (and automatic) vacuum furnace like the Labs use, such as the Vita Vacumat 30 is needed.

CEMENTATION OF RESTORATION: The weakest part of the CEREC restorations the luting agent layer is exposed margin. The long-term success of the restorations depends

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mainly on the success of luting agent, which requires a low shrinkage rate, high wear resistance, bonding to both tooth structure and the ceramic, polishability, and color stability. Previous result have generally indicated that dual cure resin composites are preferred for the luting of ceramic inlays, because of their ability to set completely and have greater resistance to occlusal loading compared with GIC. The GIC is reliable chemical bond to tooth structure and its fluoride release.

The final

smoothening is achieved using a polishing paste applied with a rubber cup. FINISHING & POLISHING: The frequent frustration with a CEREC2 restoration is the time it takes to finish the restoration after it has been bonded. This obstacle can easily be overcome.

The place to start, especially when using

extrapolation, is before the tooth has been prepared for the CEREC 2 restoration.

Observe carefully the shape of the existing occlusion,

marginal ridge heights, and cusp.

Placement before any tooth reduction has begun. Form a mental image of these anatomical landmarks for reproduction later. An intraoral picture, frozen on the monitor, would be helpful.

Later, when the

restoration has been bonded, any areas of gross excess can be quickly reduced.

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When reducing excess porcelain, the appropriate diamond is essential. It is possible to crack porcelain, even after the restoration has been bonded, with a diamond that is too coarse.

The wonderful

characteristic of the Vita Mark II porcelain that allows it to be nonabrasive to the opposite tooth also allows it to be easily carved with a fine-grit diamond. The bur used for occlusal reduction is a 1923 F (F is for fine) football â&#x20AC;&#x201C; shaped Neodiamond form Microcopy.

The

Neodiamond is an inexpensive, â&#x20AC;&#x153;one useâ&#x20AC;? diamond. This football-shaped diamond can be used more than once, but should be discarded at the first sign of dullness. One of the most common mistakes leading to frustration in finishing the restoration is using a diamond past its useful life. Make the initial gross occlusal reduction and the finishing of the interproximal areas with the rubber dam in place.

Note: Be sure to use water spray during gross reduction.

diamond used at high speed against porcelain can cause heat buildup and porcelain cracking. It is also possible to crack the porcelain restoration by having the patient close too hard on the articulating paper in the adjustment process. This porcelain has excellent strength characteristic. However, a sharp opposing cusp under premature excess pressure can crack a bonded porcelain restoration.

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The interproximal finishing is done with a round end taper 850012 F from Axis. Because of the vertical nature of the proximal box walls, the infrared camera is not able to process data as accurately as it can on the occlusal. As a result of this situation there may be more discrepancy in the fit in this area, causing the need for extra finishing at the vertical part of the proximal box wall. This is easily done with the taper diamond or a Profin from Dentatus. If the bottom line has been accurately drawn, there will be little need for finishing this area. However, the profin is excellent for smoothing the occasional area of residual cement that has been left behind.

Once the appropriate occlusion has been established, smooth any rough areas with the same fine-grit football-shaped diamond as above but now at low speed and without water spray. Caulk Enhance polishing cups used in a slow speed followed by brown rubber points used in a high-speed handpiece at low RPM, gives a very acceptable polish.

The following instruments help in the various steps in preparation of the restorations, finishing and polishing the CEREC restorations.

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Proper anatomical occlusal morphology and a smooth “wet look” shine on the porcelain surface are requirements for achieving excellent CEREC restorations. This can be achieved by LS-7257 Prep N’ Glaze Logic Set. This comprehensive set provides the clinician with everything required to deliver CEREC restorations, from start to finish.

The solution: KaVo SONICflex prep Ceram (0571 0331) permits perfect finishing and exactly defined cavities through precise transfer of the geometry of the tips directly to the tooth substance. With tips specially developed for adhesive inlays and onlays with optimum bevel angles:  Tips with defined edge angles: lateral (60°) and cervical (75°).  Tips diamond-coated on one side (mesial and distal).

Features: • Avoidance of undesired undercuts. • Optimized result: The result of the preparation in the difficult

approximal

region

reproducible

and

considerably improved. • Less treatment stress, especially in critical procedures.

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• Less treatment time: Considerable time saving compared with conventional methods. • Quality improvement: Through cavity design, which protects substance and adjacent teeth. • Wide range of applications: May be used for all All-ceramic and fine hybrid composite and other inlay systems, such as CEREC IPS EMPRESS and TARGIS VECTRIS (registered trade marks of Sirona Dental Systems GmbH, Bensheim and Ivoclar AG, Schaan).

DCS PRICEDENT The DCS Precident system (Digitizing Computer System) called the Dux or titan system in USA was developed in 1988 and introduced to the market in 1990.

Since then about 150 units have been used in

Germany and other countries.

Originally this system was designed for fabricating metal copings for porcelain fused to metal crowns and FPD’s.

The following features are available in this system: 1. Acquisition of data form the prepared tooth is performed manually on the digitizer. A touch probe is traced along the conventional stone

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cast. The 3 dimensional morphology of the prepared tooth can be easily obtained and reconstructed from a limited amount of data. 2. Up to 7 units FPD on one side of the arc can be made with this system. a. All ceramic coping can also be produced with the specially designed end-mill and porcelain block. b. It takes about 30 to 45 minutes form digitizing to milling process in the fabrication of a single crown. c. The marginal accuracy of milled coping has been proved clinically acceptable.

This system consist of 3 main parts: 1. A desktop computer. 2. A digitizer and 3. A milling machine with 3 degree of freedom.

FABRICATION TECHNIQUE: DIGITIZING: Tooth preparation and impression making are performed in the conventional manner. The trimmed working die of the prepared tooth is placed on the digitizer table. The sensor tips 1.0 mm in diameter and 10.0mm in length is used to trace the prepared tooth. On the display a 2-

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dimensioanl outline of the prepared tooth with a marginal line and a 0.2*0.2mm grids will be indicated.

When each grid is touched with the sensor tip 3-dimensioanl outline of the prepared surface area will be measured and transferred to the data bank.

The areas for which data are already stored will be

changed to blue.

Once the entire area has been digitized the 3-

dimensional reconstruction of the stored data about the prepared tooth is displaced. The white line on the 3-dimensional reconstruction represents the marginal line. If the line is not smooth, digitization should be done again. COMPUTER-AIDED DESIGNIGN: Data for fabricating a metal coping can be obtained by adding offset for the desired thickness of metal on the top of the prepared tooth surface data. Thickness can be varied according to the coping design. This coping data for complete or partial porcelain coverage can be developed in this system.

Occlusal morphology cannot be designed by this system. The time required for digitizing, designing and the data conversion to milling path data is about 15 to 20 minutes for a single crown and 20 to 30 minutes for a 3 unit FPD.

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COMPUTER AIDED MILLING: Metal copings are milled from titanium blocks. In accordance with CAD data, the milling program selects the titanium block that will results in the minimum remaining material.

End mill of 3 and 2 nm in diameter are used in the milling process. The steps in the milling process are: 1. A titanium block is fixed in the milling machine with the jig. 2. The inside of the coping is milled with the CAD data. 3. The titanium block is removed, turned over and replaced when the milling of the inside of the coping is finished, the milling machine will automatically stop to allow the side of the titanium block to be changed. 4. The outer surface of the coping to which the porcelain or the resin material will be attached later is milled. 5. To allow the removal of the coping from the block, the connecting part between the coping and the remaining block is cut. 6. The time required for milling a single crown coping is about 30 to 45 minutes. About 90 to 120 minutes are required for the 3 unit FPD coping.

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7. The infrastructure for ceramic crown can also be milled using this system form a block of high performance METROXIT ZIRCONIUM OXIDE TZP BIOCERAMICR type TAP (tetragonal polycrystalline Zirconium oxide).

FINISHING AND POLISHING: Finishing and polishing are performed in the conventional manner on the die. Porcelain or composite resin can be used as a facing material and is applied with the conventional method.

ACCURACY AT THE MARGINS: The average gap between the coping and die at the margin is 30 to 50 micrometer. Although there is stillroom for improvement, it is fair to conclude that this system is able to achieve clinically acceptable marginal accuracy comparable to that of conventional complete cast crown (30 to 50 microns) and other CAD/CAM system (50 to 100 microns).

PROCERA SYSTEM This process for manufacturing crowns, process and implant superstructures uses a combination of copy milling, spark erosion and laser welding.

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PROCERA technology was first developed for processing titanium.

The application of PROCERA system for manufacturing

individual crown made of extremely dense sintered aluminium oxide ceramics resulted with the increasing demand for improved aesthetics.

ALUMINIUM OXIDE CERAICS: Crowns manufactured with PROCERA system shows strength values never reached by an all-ceramic system. Flexural strength is 699 +/-70.8 Mpa according to the manufacture. ANDERSSON and ODEN research at the UNIVERSITY of MICHIGEN indicates a flexural strength approximately twice as high as that of IN-CERAM and more than three times of other ALL-CERAM systems.

THE PROCERA ALL-CERAMIC SYSTEM: The three main parts of the PROCERA system are: 1. A scanner, 2. A personal computer, 3. A modern or disk for transmission of data to the workstation.

FABRICATING PROCEDURE:

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The die of the prepared tooth is first mechanically scanned. The scanner has a sapphire ball tip that reads the die shape by circular scanning, describing the tooth using approximately 20000 measured values.

When scanning is completed the technician can design the coping on the computer monitor. Various programs are offered to the operator such as design of the crown, its desired shape and preparation margins.

15 to 25% shrinkage of the aluminum oxide ceramic material is expected during sintering process. This is compensated by enlarging the design in the computer files.

The data are collected and then transferred to a PROCERA workstation via modem. This means that the master cast need no longer be sent out of the dentist office. The process of manufacturing the coping could theoretically be initiated at any point on the earth and at the workstation an enlarged die model is precision milled by a computercontrolled milling machine.

High â&#x20AC;&#x201C; purity aluminium oxide powder with a defined grain size is then pressed onto the die using very high pressure.

This enormous

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pressure give the material a high packing density, a main factor in the material strength. The outside of the coping is milled before the sintering process. By sintering at a very high temperature (1550°C) the coping will shrink to the original dimension and will have excellent marginal fit.

VENEERING THE PROCERA CROWN: A special ceramic material with co-efficient of thermal expansion adjusted to aluminium oxide (7*10-6 micro meter /ml) has been developed for the PROCERA technique.

THE BASE KIT: It consist of • 16 dentin shades • 5 translucent shades • 4 incisal shades.

THE MASTER KIT: It has 12 modifiers accurately adjusted to each other and it also offers 8 basic dentin shades.

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This leads to a wide range of possibilities for customized design of the restoration.

CELAY The CELAY SYSTEM employs a copy milling machine and uses manufactured porcelain blankâ&#x20AC;&#x2122;s to mill out ceramic inlays, onlays, crowns and bridges is the CELAY system (Siervo et al, 1994). This system is a precision copy- milling machine.

The Celay system is unique in its milling capabilities. Its milling arms are able to move in 8 axes of freedom, which allows the milling of complex, three-dimensional shapes. Thus, it can mill the occlusal aspects of restorations in very fine detail. The marginal fidelity of these milled restorations is excellent. According to the manufacturer, marginal gap of only 50mm can be achieved. Marginal gaps of 60 mm were attained in an independent study. The Celay system provides the ability to fabricate both direct and indirect ceramic restorations. Copy milling technology requires the generation of a pattern of the desired restoration.

This

pattern can be fabricated directly from the mouth or on a pattern of the desired restoration. This pattern is then copy milled using the Celay

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machine to generate the final restoration. The system uses an approach similar to the pantographic method of duplicating keys.

FABRICATION TECHNIQUE: Preparation of porcelain inlays should allow for a porcelain thickness of 1.5 mm, and the ideal occlusal depth and the isthmus width of the porcelain inlays is 2mm. Preparation should be slightly conical with rounded internal line angles. Cavo surface margins should be sharp and not beveled. Any undercut or deep areas are filled in with light polymerized glass Ionomer cement. The dies are then sealed with 2 coats of thin cyanoacrylate and any undercuts are blocked out with wax. An ultra thin die lubricant is placed as a separator. An appropriate amount of a special blue composite resin is paled in the die and carved to shape, creating what is termed a “Pro-inlay”. The occlusal aspect of the proinlay can be created with carving instruments or burs after it had been light polymerized for a minimum of 2 minutes. After this, the pro-inlay is then removed form the die and polymerized form the bottom for another minute.

The pro-inlay is fixed in the Celay using the ‘point’ method an then ready to be copy milled. One or tow inlays are mounted with the ‘rod’ method. This procedure requires that a small hole be drilled in one of the

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central surfaces, after which a special pin is cemented wit cyanoacrylate for positioning in the Celay. The reference â&#x20AC;&#x201C;scanning disk is placed in the machine, and the appropriate size porcelain blank is chosen. The reference disk acts as a scanning stylus that is moved across the surface of pro-inlay.

MILLING INSTRUMENTS: The following milling instruments and polishing instruments are used: 1. A coarse diamond disk with a grit size of 126 um (Diametal, Biel, Switzerland) for efficient bulk reduction. 2. A finishing diamond disk with a grit size of 64um (Diametal) for precision milling of the final contour. 3. Round tipped diamonds with a grit size of 64um (Diametal) for narrow concavities that is secondary occlusal anatomy. 4. Sharp tipped diamond with a grit size of 64um (Diametal) for secondary occlusal anatomy. 5. Polishing instruments loaded with diamond powder (Shofu).

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Schematic representation of copy milling.

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This 37 years-old women wanted to replace the defective and aging amalgam in her maxillary right first molar with a more esthetic restoration

The tooth is isolated with rubber dam and the preparation is coated with imaging liquid, a thin oily substance

The tooth is sprayed with imaging powder, a white powder to make it photoreceptive

Schematic summary of CAD/CAM and copy milling operations.

A digitizing camera is used to record the dimensions instead of making a traditional impression

The CAD/CAM (CEREC) calculate dimensions before milling of the porcelain inlay

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A block of porcelain has been placed into the machine and is now being milled.

After 7 minutes the final porcelain restoration drops to the because of the tray.

A 30 micron diamond quickly curs off the porcelain sprue.

The try-in shows a slight gap that will be filled with resin cement.

The preparation is etched for 15 to 20 seconds

The tooth is partially dried following the acid etch

The dentin bonding agent is applied in multiple cores then air dried and polymerized.

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The desk-top Celay (Vident) machine has its own selfcontained liquid cooling system.

The proper shade and size of pre-manufactured Vita Celay porcelain ceramic blank is selected.

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The pattern is traced manually and the machine mills the ceramic blank to the exact shape and size of the pattern

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REFERENCES 1. David A Graber., Ronald E Goldstein. Porcelain and composite inlays and onlays esthetics posterior restorations.

Quintessence

Publication. 2. Aschheim Dale.

Esthetics dentistry second edition.

A clinical

approach to techniques and materials. Mosby Publication. 137-180. 3. Baratieri., Luiz N. Esthetics direct adhesive restoration on fractured anterior teeth. Quintessence Publication. 265-310. 4. Robert G. Craig. Restorative dental materials. Xth Edition. Mosby Publication. Harcourt Brace and Company Pvt. Ltd. 467-496. 5. Ronald E. Goldstein.

Esthetics in dentistry. IInd Edition.

B.C.

Decker Inc. 339-390. 6. John W. McLean.

Dental ceramics proceedings of the first

international symposium on ceramics. Quintessence Publication. 7. Jack L. Ferracane. Materials in dentistry principles and applications. IInd Edition. Lippincott Williams and Wilkins. 158-165. 8. David A. Graber.

Porcelain laminate-veneers.

Quintessence

Publication. 9. Philips. Science of dental materials. Kenneth J. Anusvice. X th Edition. W.B. Saunders Company, Harcourt Asia Pvt. Ltd. 583-618.

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10.A. Parameswaran, K.S. Karthikeyan.

Materials in restorative

dentistry. Meenakshi Ammal Trust. 203-231. 11.Vimal K.Sikri. Textbook of operative dentistry. CBS Publishers. 439-481. 12.Theodore M. Robertson. Herald O. Heyman. Sturdevants art and science of operative dentistry. IV Edition. Mosby Company. 133226.