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WO1993024427A1 - Corps ceramiques adaptes, leur procede de production et leur utilisation - Google Patents

Corps ceramiques adaptes, leur procede de production et leur utilisation Download PDF

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Publication number
WO1993024427A1
WO1993024427A1 PCT/EP1993/001307 EP9301307W WO9324427A1 WO 1993024427 A1 WO1993024427 A1 WO 1993024427A1 EP 9301307 W EP9301307 W EP 9301307W WO 9324427 A1 WO9324427 A1 WO 9324427A1
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WO
WIPO (PCT)
Prior art keywords
pyrolysis
mixture
ceramic
volume
reactive
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/EP1993/001307
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German (de)
English (en)
Inventor
Rainer Hahn
Petra Hahn
Werner Hahn
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Individual
Original Assignee
Individual
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Individual filed Critical Individual
Priority to EP93912781A priority Critical patent/EP0705234A1/fr
Publication of WO1993024427A1 publication Critical patent/WO1993024427A1/fr
Priority to PCT/EP1994/001694 priority patent/WO1994027558A1/fr
Priority to EP94918374A priority patent/EP0700281A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • C—CHEMISTRY; METALLURGY
    • C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
    • C08K—Use of inorganic or non-macromolecular organic substances as compounding ingredients
    • C08K3/00—Use of inorganic substances as compounding ingredients
    • C08K3/02—Elements
    • C08K3/08—Metals
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K6/00—Preparations for dentistry
    • A61K6/80—Preparations for artificial teeth, for filling teeth or for capping teeth
    • A61K6/802—Preparations for artificial teeth, for filling teeth or for capping teeth comprising ceramics
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K6/00—Preparations for dentistry
    • A61K6/80—Preparations for artificial teeth, for filling teeth or for capping teeth
    • A61K6/84—Preparations for artificial teeth, for filling teeth or for capping teeth comprising metals or alloys
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61K—PREPARATIONS FOR MEDICAL, DENTAL OR TOILETRY PURPOSES
    • A61K6/00—Preparations for dentistry
    • A61K6/80—Preparations for artificial teeth, for filling teeth or for capping teeth
    • A61K6/884—Preparations for artificial teeth, for filling teeth or for capping teeth comprising natural or synthetic resins
    • C—CHEMISTRY; METALLURGY
    • C03—GLASS; MINERAL OR SLAG WOOL
    • C03C—CHEMICAL COMPOSITION OF GLASSES, GLAZES OR VITREOUS ENAMELS; SURFACE TREATMENT OF GLASS; SURFACE TREATMENT OF FIBRES OR FILAMENTS MADE FROM GLASS, MINERALS OR SLAGS; JOINING GLASS TO GLASS OR OTHER MATERIALS
    • C03C14/00—Glass compositions containing a non-glass component, e.g. compositions containing fibres, filaments, whiskers, platelets, or the like, dispersed in a glass matrix
    • C—CHEMISTRY; METALLURGY
    • C04—CEMENTS; CONCRETE; ARTIFICIAL STONE; CERAMICS; REFRACTORIES
    • C04B—LIME, MAGNESIA; SLAG; CEMENTS; COMPOSITIONS THEREOF, e.g. MORTARS, CONCRETE OR LIKE BUILDING MATERIALS; ARTIFICIAL STONE; CERAMICS; REFRACTORIES; TREATMENT OF NATURAL STONE
    • C04B35/00—Shaped ceramic products characterised by their composition; Ceramics compositions; Processing powders of inorganic compounds preparatory to the manufacturing of ceramic products
    • C04B35/622—Forming processes; Processing powders of inorganic compounds preparatory to the manufacturing of ceramic products
    • C04B35/64—Burning or sintering processes
    • C04B35/65—Reaction sintering of free metal- or free silicon-containing compositions
    • C—CHEMISTRY; METALLURGY
    • C03—GLASS; MINERAL OR SLAG WOOL
    • C03C—CHEMICAL COMPOSITION OF GLASSES, GLAZES OR VITREOUS ENAMELS; SURFACE TREATMENT OF GLASS; SURFACE TREATMENT OF FIBRES OR FILAMENTS MADE FROM GLASS, MINERALS OR SLAGS; JOINING GLASS TO GLASS OR OTHER MATERIALS
    • C03C2214/00—Nature of the non-vitreous component
    • C03C2214/04—Particles; Flakes
    • C—CHEMISTRY; METALLURGY
    • C03—GLASS; MINERAL OR SLAG WOOL
    • C03C—CHEMICAL COMPOSITION OF GLASSES, GLAZES OR VITREOUS ENAMELS; SURFACE TREATMENT OF GLASS; SURFACE TREATMENT OF FIBRES OR FILAMENTS MADE FROM GLASS, MINERALS OR SLAGS; JOINING GLASS TO GLASS OR OTHER MATERIALS
    • C03C2214/00—Nature of the non-vitreous component
    • C03C2214/20—Glass-ceramics matrix

Definitions

  • the present invention relates to ceramic fitting bodies and a method for their production.
  • the method is used in particular in the manufacture of prostheses and tooth restorations.
  • Dentures and filling materials for teeth are subject to heavy wear and therefore must have a corresponding strength and hardness to mechanical influences, a high wear resistance and resistance to food, saliva and bacteria. They must also be physiologically compatible, biocompatible, and also easy to process and have a good fit.
  • Ceramic tooth restorations have so far been produced using laboratory technology and fixed to the healthy tooth structure using a suitable fastening medium. After the carious tooth hard tissue has been removed, the defect is prepared divergingly towards the occlusal surface and prepared for receiving an externally produced restoration.
  • the cavity is generally molded using elastomeric impression materials and a model of the jaw or cavity is created.
  • the respective restoration is produced indirectly in a complicated production chain using costly system technology, for example cast centrifuges and sintering furnaces.
  • the laboratory effort is extremely high and the accuracy is limited due to the indirect production over several intermediate steps. More recent methods provide for direct digitization of the cavity data, for example using a video system.
  • the restoration is created digitally on the screen and then ground out of prefabricated blanks by numerical control of a suitable grinding machine.
  • DD-A-261 741 discloses a method for producing inlays from glass ceramics, in which the inlay can be reproduced electro-optically by generating corresponding imaging information signals from the tooth to be preserved, which signals are converted in a computer to control signals for a processing machine .
  • the variety of shapes and accuracy to be produced is severely limited due to inaccuracies in the image formation and the digital construction, but above all due to the insufficient imaging properties and the limited accuracy of simple grinding machines.
  • DE-A-40 09 985 describes the production of dental prostheses with an electrically conductive ceramic material, for example with nitride ceramics.
  • the electrically conductive material enables the blank initially produced to be processed by means of electrical discharge. Even with such a procedure, the accuracy of the shape leaves something to be desired.
  • DE-A-39 09 994 describes a dental ceramic mass in powder form which contains a light-polymerizable plastic additive. This ceramic mass solidifies through polymerization under the influence of light. The solidified mass is then removed from the tooth stump or from the cavity and fired in a ceramic furnace, the plastic matrix burning. This leads to an extremely high volume shrinkage, which leads to clinically unacceptable fit accuracies.
  • Reactive fillers are substances, for example elements of the transition metals, which can react with the degradation products from the polymer matrix. The reacted filler is thus incorporated into a matrix of converted, glass-like polymer.
  • this basic technique has so far not entered the field of dental ceramics.
  • shape-fitting bodies can be produced starting from a mixture of silicon-containing polymer and reactive filler, by first making this mixture modelable, then - either directly in a patient's tooth cavity or on a suitable model of a cavity or Prosthesis - brought into the desired shape, this shape hardens (preceramic) and the polymer matrix of this preceramic is finally subjected to pyrolysis.
  • the present invention therefore relates to a process for the production of ceramic fitting bodies, which comprises the steps: a) transferring a mixture comprising 90 to 50% by volume of silicon-containing polymer, 10 to 50% by volume of reactive filler and optionally comprises further additives, in a plastically deformable, hardenable mixture with a kneading-like viscosity range; b) converting the mass obtained under a) into a shape desired for the fitting body; c) stabilizing the molded mass by at least partially curing the polymer component to form a preceramic; and d) pyrolysis of the stabilized preceramic in an atmosphere low in oxygen and water vapor with at least partial formation of a ceramic composite material.
  • the silicon-containing polymers are compounds with the structural repeating unit
  • X is a carbon atom, C, a nitrogen atom, N, or an oxygen atom, 0, that is to say polycarbosilanes, polysilazanes and polysiloxanes.
  • R denotes a hydrogen atom, H, and / or one or more different organic radicals which can be present alongside one another within the polymers.
  • organic radicals are usually alkyl radicals, preferably having 1 to 4 carbon atoms, for example methyl, ethyl and propyl, aryl radicals and arylalkyl radicals, preferably having 6 to 8 carbon atoms, for example phenyl or substituted phenyl such as methylphenyl or benzyl, and Residues comprising o_, ⁇ -ethylenically unsaturated groups, preferably with 2 to 6 carbon atoms, for example vinyl or allyl.
  • the polymers can also have other foreign atoms, for example boron.
  • ⁇ , ⁇ -ethylenically unsaturated groups is necessary in order to enable the polymers to crosslink later during curing.
  • their proportion is variable and can be selected within wide limits by a person skilled in the art. Good results are achieved, for example, if the proportion of unsaturated residues, such as vinyl, is between 10 and 30 mol%, based on the total amount of the R residues.
  • the proportion of radicals R which are hydrogen is generally low and is usually not more than 25 mol%, based on the total amount of the radicals R.
  • Polysiloxanes are preferred polymers. Good results can be achieved, for example, with polysiloxanes with the repeating unit R - £ ⁇ Si - O ⁇ 5 * - I
  • the reactive filler is to be understood as meaning those substances which, under the conditions of polymer pyrolysis, are able to react with solid or gaseous decomposition products of the polymer and / or with a reaction gas, for example with carbon, hydrocarbon species or nitrogen, and can thereby be carbonized or nitrided .
  • Transition metals Ti, V, Cr, Zr, Nb, Mo, Hf, Ta, W and Fe, but also Al, B and Si, in elementary form, are particularly suitable for this. Particularly good results are achieved according to the invention if metallic titanium is used as the reactive filler.
  • the reactive filler is in pure form, e.g. with a
  • the average particle size is expediently less than 250 ⁇ m, preferably less than 100 ⁇ m, and very particularly preferably between 0.1 and 10 ⁇ m.
  • the silicon-containing polymers are used in an amount of 50 to 90% by volume, preferably 60 to 80% by volume, the reactive filler in an amount of 10 to 50% by volume, preferably 20 to 40% by volume , each based on the total amount of the mixture of polymer and reactive filler.
  • the mixture can optionally contain further additives, for example polymer catalysts or initiators, dyes, electrically conductive ceramic materials, reinforcing particles and / or inert fillers.
  • further additives for example polymer catalysts or initiators, dyes, electrically conductive ceramic materials, reinforcing particles and / or inert fillers.
  • the total amount of additives is appropriate not more than 25% by volume based on the total amount of the mixture.
  • the fitting body to be manufactured can be individually adapted to the indication-specific requirements with regard to wear and / or chewing stress.
  • the short fibers or platelets known in this field are particularly suitable as reinforcing particles.
  • Inert fillers are, for example, the fillers customary in the field of dental ceramics, such as glass or quartz powder or oxide-ceramic and non-oxide-ceramic fillers, for example aluminum oxide, zirconium oxide, silicon nitride and silicon carbide.
  • the mixture can be obtained by mixing the individual components, namely the silicon-containing polymer, the reactive filler and, if appropriate, the additives.
  • the reactive filler can be suspended in glycerin beforehand.
  • the mixing can then take place, for example, in a high-speed mixer.
  • a kneading-like viscosity range is then set.
  • the kneading-like viscosity range is understood to mean the viscosity at which the mixture becomes plastically deformable, that is to say it can be modeled and stuffed. This range varies widely and is familiar to the dental technician.
  • the desired viscosity can be set, for example, by adding viscosity-increasing agents.
  • the mixture is preferably brought into a moldable form by regulating the viscosity of the mixture by partially crosslinking the silicon-containing polymers. This can be done simply by heating in the presence or absence of a polymerization catalyst or initia- tors.
  • the temperatures used to crosslink the polymer are typically below 400 ° C.
  • the curing time is usually no more than 4 hours.
  • the conditions are variable and can be set in a manner known per se, taking into account the desired degree of crosslinking and the catalyst which may be used. In order to avoid excessive crosslinking, the mixture is cooled suddenly after reaching the target viscosity.
  • the modelable mass obtained is then brought into the desired shape.
  • an already prefabricated macro filler into the fitting body to be manufactured.
  • These macro fillers are expediently a compatible, prepolymerized polymer ceramic filler and / or a ceramic and / or metallic molded part.
  • the shaping can either be carried out directly on the patient by introducing the mass into the tooth cavity, or it is carried out on a model of a tooth cavity or jaw produced in a conventional manner.
  • the tooth or model surfaces can be provided with a suitable layer before the molding compound is introduced. This can either take on the function of a separating layer on the tooth or model surface and ensure lifting of the restoration after the polymerisation of the preceramic, or, as an adhesion promoter, enable the polymer to be shrunk on the possibly conditioned model surface.
  • the molded mass is then stabilized to form a pre-ceramic by curing the polymer matrix. It is advisable to oversize the preceramic restoration somewhat in order to compensate for smaller volume shrinkage during hardening and possibly later pyrolysis. After reconstruction of the defect Coarse excesses can be removed relatively easily and the curing process and the restoration can be reworked manually if necessary. Any shortfalls and inaccuracies can be relatively easily polymerized at this stage. If necessary, several layers of the polymer-containing composition according to the invention can also be applied in succession and cured step by step, as a result of which not only can several materials be combined with one another, but also the polymerization shrinkage is reduced. When using models, the setting expansion or contraction of the model mass can also be matched to the volume shrinkage during curing and pyrolysis.
  • the curing is expediently, but not necessarily, in the presence of a polymerization catalyst or initiator.
  • a polymerization catalyst or initiator The chemical and thermal catalysts and initiators customary in this field are suitable for this.
  • the use of photoinitiators is preferred, in particular if the mass is to be stabilized or hardened in the desired shape in a tooth cavity in the mouth of the patient himself. In this case, a rapid curing of the surface of the shaped body can be achieved under the action of a suitable light source, which is sufficient for stabilization in the desired shape.
  • the initiators customary in the curing of dental plastics in particular organic peroxides, are preferred. Very good results can be achieved, for example, with benzoyl peroxide.
  • catalysts or initiators are used in the pre-ceramic stabilization, these are already added when the silicon-containing polymer and reactive filler are mixed.
  • chemical initiators are added, a two-component system can be produced, for example in the manner of the paste-paste system known in dental technology.
  • Photoinitiators enable light curing one-component systems.
  • the photoinitiators can also be used in a mixture with thermal and / or chemical initiators, it being possible for the photoinitiator to be a thermal initiator, for example benzoyl peroxide.
  • Catalysts and initiators are expediently used in an amount of up to 10% by volume, preferably in an amount of 0.001 to 5% by volume, particularly preferably in an amount of 0.1 to 2% by volume.
  • the conditions for the hardening of the shaped material for the pre-ceramic are set when chemical catalysts are used so that the hardening time is approximately 5 minutes.
  • Thermal curing is expediently carried out at temperatures between 150 and 400 ° C. for about 1 to 8 hours in conventional laboratory ovens.
  • Light-induced curing which can be carried out directly on the patient, is expediently carried out by means of a suitable light source at wavelengths between 350 and 650 nm.
  • the conditions should be selected such that the exposure time is between 20 and 120 seconds.
  • Catalyst mixtures can also be used to influence the coloring of the ceramic fitting to be manufactured. Combinations of peroxides with different cocatalysts are known for this purpose in the field of dental ceramics.
  • the coloring materials known in the art are used for coloring.
  • the preceramic so obtained is pyrolyzed with controlled supply of heat, as a result of which the polymer phase is at least partially ceramized, ie converted into a ceramic. Ceramization is understood to mean that the points of the fitting body treated in this way, ie generally the functionally relevant points, have a glass content of at least 50% by volume.
  • the pyrolysis temperature is between approximately 500 ° C. and 1600 ° C.
  • the pyrolysis takes place in an atmosphere which is poor in oxygen and water vapor, usually in the presence of an inert gas or a reactive gas.
  • the low oxygen and water vapor atmosphere can be generated, for example, by evacuating the pyrolysis device, purging with the inert gas or the reactive gas, or by baking out. For practical reasons, it is expedient to work under normal pressure, but the pyrolysis can also be carried out under reduced or elevated pressure.
  • Argon and helium are suitable as inert gases.
  • the pyrolysis is preferably carried out under a reactive gas atmosphere. Any gas that can be reacted with the reactive filler is suitable as the reactive gas. In this way, the shrinkage of the preceramic during the transition to the ceramic can be largely compensated for by the increase in volume of the reaction product of filler and reactive gas.
  • Possible reactive gases are, for example, N 2 , NH 3 , CH 4 and BH 3 .
  • Nitrogen-containing gases, in particular N 2 are preferred, the reactive fillers of which are nitrided when used.
  • the reactive gas can also be used diluted with an inert gas.
  • the implementation and incorporation into the reactive filler can be varied by regulating the partial pressure of the reactive gas.
  • TiN and titanium carbonitride which are integrated in a silicon oxyarbide matrix, are formed in the pyrolysis under an N 2 atmosphere.
  • the pyrolyzed fitting can also contain other metal compounds such as oxides, silicides and carbides.
  • Titanium carbonitride is a mixed crystal which has a golden yellow color within narrow limits of the N / C ratio.
  • the N / C ratio can also be influenced by the choice of the N 2 partial pressure and thus the coloring desired from an aesthetic point of view can be achieved.
  • the reactive gas atmosphere can be generated, for example, by using the pyrolysis device, e.g. B. the pyrolysis furnace, fumigated from the outside.
  • the reactive gas can also be provided in liquid form, so that the reactive gas atmosphere only increases with increasing heating, for. B. developed during the pyrolysis process.
  • the reactive gas atmosphere is preferably generated by means of gas-releasing substances.
  • Such substances for example in tablet form, together with the preceramic material to be pyrolyzed, in a closed system, for example a pressure or pyrolysis chamber, which must be lockable in a pressure-tight manner and which may consist, for example, of titanium or ceramic material, by means of a suitable heat source , for example a dental ceramic oven, heated, whereby the gas is released.
  • a suitable heat source for example a dental ceramic oven, heated, whereby the gas is released.
  • Ammonium nitrite is particularly suitable as the nitrogen-releasing substance.
  • the heat treatment can 'in a suitable furnace, by irradiation with suitable laser or by applying a voltage source and the induced current flow take place.
  • the pyrolysis in an oven is expediently carried out at a temperature between 1,000 and 1,600 ° C., preferably between 1,100 and 1,300 ° C., the reactive gas atmosphere being generated as above.
  • the pyrolysis times are between depending on the type and volume of the fitting to be created 30 minutes and 72 hours.
  • the preceramic is heated to 1,200 ° C. in the furnace at a heating rate of 5 K / min and isothermally kept at 1,200 ° C. for 1 hour. It is then cooled at a cooling rate of 500 ° K / min.
  • the use of pressure or pyrolysis chambers described above is particularly advantageous here, since they only have to be small in size and can therefore be conveniently heated in a conventional dental ceramic oven. As a result, the expenditure on equipment, which is associated, for example, with the use of conventional pyrolysis furnaces, is greatly reduced.
  • the pyrolysis can also be carried out by means of a laser at suitable energy densities and suitable pulse frequencies and with the aid of suitable gas supply devices.
  • This method has the advantage that the preceramic can be pyrolyzed directly on the patient.
  • a temperature gradient occurs within the fitting body to be pyrolyzed, as a result of which the fitting body is converted from the surface and an elastic polymer matrix remains in the core of the fitting body.
  • An outer layer of approximately 100 ⁇ m is expediently pyrolytically ceramized in such a way that its glass content is at least 50%.
  • Pyrolysis can also be carried out by means of induced current flow by applying high-frequency alternating voltages, as are known from surgery.
  • the starting material must be electrically conductive and / or electrically conductive doped.
  • Ceramic materials for example nitrides or borides of the transition metals, as described, for example, in DE-A-40 09 985, are suitable for this.
  • the ceramic restoration can - if necessary - be reworked, polished and attached to the tooth structure in a conventional manner.
  • the invention thus enables a direct production of ceramic insert fillings on the patient and / or via a suitable model; the conventional, complicated laboratory production chain is eliminated or can be reduced to a minimum.
  • the significant simplification of the manufacturing technology reduces the number of possible sources of error on the one hand, and on the other hand the manufacturing costs are significantly reduced.
  • the reliability of the fitting bodies produced according to the invention can be improved sustainably and the structure and color adaptation can be matched to the individual requirements of the patient. It is also possible to overlay various base materials and to incorporate reinforcing particles and / or fibers.
  • the base materials used for the ceramics also enable an extremely fine-grained structure with average particle sizes not exceeding 100 ⁇ m, which has a favorable effect on the wear on opposing tooth surfaces. With the method described, a 4-point bending strength (determined according to DIN 51 110) of more than 80 MPa can be achieved without problems.
  • the restoration With a retentive geometry of the tooth cavity and at least partial pyrolysis in the patient's mouth, the restoration remains in the defect and does not have to be attached with a foreign medium.

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  • Health & Medical Sciences (AREA)
  • Chemical & Material Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Ceramic Engineering (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Epidemiology (AREA)
  • Plastic & Reconstructive Surgery (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Organic Chemistry (AREA)
  • Materials Engineering (AREA)
  • Manufacturing & Machinery (AREA)
  • Dispersion Chemistry (AREA)
  • Geochemistry & Mineralogy (AREA)
  • Inorganic Chemistry (AREA)
  • General Chemical & Material Sciences (AREA)
  • Structural Engineering (AREA)
  • Medicinal Chemistry (AREA)
  • Polymers & Plastics (AREA)
  • Dental Preparations (AREA)
  • Dental Prosthetics (AREA)

Abstract

On produit des corps ajustés, d'une forme précise, à partir d'un mélange de polymère siliceux et d'une charge réactive. Le mélange est d'abord malléabilisé, puis mis en forme, durci et finalement soumis à une pyrolyse.
PCT/EP1993/001307 1992-05-25 1993-05-25 Corps ceramiques adaptes, leur procede de production et leur utilisation Ceased WO1993024427A1 (fr)

Priority Applications (3)

Application Number Priority Date Filing Date Title
EP93912781A EP0705234A1 (fr) 1992-05-25 1993-05-25 Corps ceramiques adaptes, leur procede de production et leur utilisation
PCT/EP1994/001694 WO1994027558A1 (fr) 1993-05-25 1994-05-25 Reconstitutions dentaires ceramiques, protheses dentaires, implants et corps moules medicaux et leur procede de fabrication
EP94918374A EP0700281A1 (fr) 1993-05-25 1994-05-25 Reconstitutions dentaires ceramiques, protheses dentaires, implants et corps moules medicaux et leur procede de fabrication

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE4217115A DE4217115C2 (de) 1992-05-25 1992-05-25 Medizinische keramische Paßkörper, beispielsweise medizinische Implantate, Prothesen und Zahnrestaurationen, sowie ein Verfahren zu ihrer Herstellung
DEP4217115.6 1992-05-25

Publications (1)

Publication Number Publication Date
WO1993024427A1 true WO1993024427A1 (fr) 1993-12-09

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PCT/EP1993/001307 Ceased WO1993024427A1 (fr) 1992-05-25 1993-05-25 Corps ceramiques adaptes, leur procede de production et leur utilisation

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EP (1) EP0705234A1 (fr)
DE (1) DE4217115C2 (fr)
WO (1) WO1993024427A1 (fr)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE4217115A1 (de) * 1992-05-25 1993-12-02 Hahn Rainer Dr Vorrichtung und Verfahren zur Herstellung keramischer Paßkörper, insbesondere medizinischer Implantate und Zahnrestaurationen
EP2480618A4 (fr) * 2009-09-25 2014-03-05 Ferrotec Usa Corp Mélange pour adhésion et couchage de haute résistance

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Publication number Priority date Publication date Assignee Title
DE19503637C2 (de) * 1995-02-05 1998-04-09 Hahn Rainer Zahnrestaurationsteil aus Keramikmaterial sowie Verfahren zum Herstellen eines solchen
DE19635357C2 (de) * 1996-08-22 2001-12-13 Ralf Ziesemer Vorgefertigte Zahnersatzkrone für die Zahnstumpfrestauration oder den Aufbau von Zahnprothesen
DE10201516A1 (de) * 2002-01-17 2003-08-07 Fraunhofer Ges Forschung Leitfähiges Formteil und Verfahren zu seiner Herstellung
DE102005016763B4 (de) * 2005-04-11 2008-02-14 Kettenbach Gmbh & Co. Kg Set zur Herstellung einer provisorischen Zahnkrone oder -brücke

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DE4009985A1 (de) * 1989-03-29 1990-10-04 G C Dental Ind Corp Dentalprothese
DE3926077A1 (de) * 1989-08-07 1991-02-14 Peter Prof Dr Greil Keramische verbundkoerper und verfahren zu ihrer herstellung
DE4023849A1 (de) * 1990-07-27 1992-01-30 Dornier Gmbh Keramischer werkstoff

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US3423828A (en) * 1965-10-01 1969-01-28 Dentists Supply Co Porcelain and resin tooth with silicon bonding agent
US4481227A (en) * 1980-09-12 1984-11-06 Asami Tanaka Method of coloring bakeable porcelain dental restorations
DE3522737A1 (de) * 1985-06-21 1987-01-02 Wolfgang Geppert Zahnersatz und verfahren zu dessen verwendung
DD261741A1 (de) * 1986-04-30 1988-11-09 Inst F Leichtbau U Oekonomisch Inlays aus bearbeitbarer glaskeramik
DE3909994A1 (de) * 1989-03-25 1990-09-27 Koerber Karlheinz Dentale keramikmassen und ihre anwendung
DE4217115C2 (de) * 1992-05-25 1995-04-27 Hahn Rainer Dr Medizinische keramische Paßkörper, beispielsweise medizinische Implantate, Prothesen und Zahnrestaurationen, sowie ein Verfahren zu ihrer Herstellung

Patent Citations (3)

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Publication number Priority date Publication date Assignee Title
DE4009985A1 (de) * 1989-03-29 1990-10-04 G C Dental Ind Corp Dentalprothese
DE3926077A1 (de) * 1989-08-07 1991-02-14 Peter Prof Dr Greil Keramische verbundkoerper und verfahren zu ihrer herstellung
DE4023849A1 (de) * 1990-07-27 1992-01-30 Dornier Gmbh Keramischer werkstoff

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE4217115A1 (de) * 1992-05-25 1993-12-02 Hahn Rainer Dr Vorrichtung und Verfahren zur Herstellung keramischer Paßkörper, insbesondere medizinischer Implantate und Zahnrestaurationen
EP2480618A4 (fr) * 2009-09-25 2014-03-05 Ferrotec Usa Corp Mélange pour adhésion et couchage de haute résistance

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DE4217115C2 (de) 1995-04-27
EP0705234A1 (fr) 1996-04-10

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