US20050056350A1 - Method for producing tooth replacements and auxiliary dental parts - Google Patents
Method for producing tooth replacements and auxiliary dental parts Download PDFInfo
- Publication number
- US20050056350A1 US20050056350A1 US10/976,734 US97673404A US2005056350A1 US 20050056350 A1 US20050056350 A1 US 20050056350A1 US 97673404 A US97673404 A US 97673404A US 2005056350 A1 US2005056350 A1 US 2005056350A1
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- United States
- Prior art keywords
- biocompatible material
- recited
- powder
- density
- layer
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- 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.)
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C13/00—Dental prostheses; Making same
- A61C13/0003—Making bridge-work, inlays, implants or the like
- A61C13/0006—Production methods
- A61C13/0018—Production methods using laser
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C13/00—Dental prostheses; Making same
- A61C13/0003—Making bridge-work, inlays, implants or the like
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C13/00—Dental prostheses; Making same
- A61C13/0003—Making bridge-work, inlays, implants or the like
- A61C13/0004—Computer-assisted sizing or machining of dental prostheses
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C13/00—Dental prostheses; Making same
- A61C13/08—Artificial teeth; Making same
- A61C13/09—Composite teeth, e.g. front and back section; Multilayer teeth
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C13/00—Dental prostheses; Making same
- A61C13/20—Methods or devices for soldering, casting, moulding or melting
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C5/00—Filling or capping teeth
- A61C5/70—Tooth crowns; Making thereof
- A61C5/73—Composite crowns
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61C—DENTISTRY; APPARATUS OR METHODS FOR ORAL OR DENTAL HYGIENE
- A61C5/00—Filling or capping teeth
- A61C5/70—Tooth crowns; Making thereof
- A61C5/77—Methods or devices for making crowns
-
- 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
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B22—CASTING; POWDER METALLURGY
- B22F—WORKING METALLIC POWDER; MANUFACTURE OF ARTICLES FROM METALLIC POWDER; MAKING METALLIC POWDER; APPARATUS OR DEVICES SPECIALLY ADAPTED FOR METALLIC POWDER
- B22F10/00—Additive manufacturing of workpieces or articles from metallic powder
- B22F10/20—Direct sintering or melting
- B22F10/28—Powder bed fusion, e.g. selective laser melting [SLM] or electron beam melting [EBM]
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B28—WORKING CEMENT, CLAY, OR STONE
- B28B—SHAPING CLAY OR OTHER CERAMIC COMPOSITIONS; SHAPING SLAG; SHAPING MIXTURES CONTAINING CEMENTITIOUS MATERIAL, e.g. PLASTER
- B28B1/00—Producing shaped prefabricated articles from the material
- B28B1/001—Rapid manufacturing of 3D objects by additive depositing, agglomerating or laminating of material
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- B—PERFORMING OPERATIONS; TRANSPORTING
- B33—ADDITIVE MANUFACTURING TECHNOLOGY
- B33Y—ADDITIVE MANUFACTURING, i.e. MANUFACTURING OF THREE-DIMENSIONAL [3-D] OBJECTS BY ADDITIVE DEPOSITION, ADDITIVE AGGLOMERATION OR ADDITIVE LAYERING, e.g. BY 3-D PRINTING, STEREOLITHOGRAPHY OR SELECTIVE LASER SINTERING
- B33Y10/00—Processes of additive manufacturing
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B33—ADDITIVE MANUFACTURING TECHNOLOGY
- B33Y—ADDITIVE MANUFACTURING, i.e. MANUFACTURING OF THREE-DIMENSIONAL [3-D] OBJECTS BY ADDITIVE DEPOSITION, ADDITIVE AGGLOMERATION OR ADDITIVE LAYERING, e.g. BY 3-D PRINTING, STEREOLITHOGRAPHY OR SELECTIVE LASER SINTERING
- B33Y80/00—Products made by additive manufacturing
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
- Y02P—CLIMATE CHANGE MITIGATION TECHNOLOGIES IN THE PRODUCTION OR PROCESSING OF GOODS
- Y02P10/00—Technologies related to metal processing
- Y02P10/25—Process efficiency
Definitions
- This invention relates to a method of forming a dental part and/or a tooth replacement part.
- Tooth replacements in the form of crowns, bridges, inlays and the like frequently comprise complex molded bodies which must usually take account in each specific case of the spatial configuration of intact tooth parts (tooth stumps), entire teeth or parts of the jaw that have been lost, on the one hand, and the spatial situation in relation to adjacent and/or antagonistic teeth, on the other hand.
- tooth replacement elements are produced in complex processes.
- the most widespread method is to produce the shaped bodies required—usually made of precious-metal or base-metal alloys, as well as pure metals—in a multi-step impression and casting process.
- the objective of the invention is to provide another, more advantageous way of producing such shaped bodies (and auxiliary dental parts required in implantology) that provides flexibility in manufacturing dental parts of different shapes, but which reduces the amount of waste and results in a strong dental part.
- a method in accordance with the principles of the invention includes a method of making a shaped body for use as a dental part.
- the method comprises guiding a laser beam over a powder layer using a computer-controlled laser scanning system based on data representing the shape of a cross-section through the shaped body.
- the powder comprises a biocompatible material of grain size in the range from 0 ⁇ m to 50 ⁇ m, to create a layer in the shaped body.
- the method further comprises substantially melting the powder with the laser beam, and repeating the guiding and melting over successive powder layers using successive cross-sectional representative data so as to build the shaped body entirely from layers of laser-melted material.
- a shaped dental part for use in a patient's mouth.
- the shaped dental part comprises a body formed from melted particles of biocompatible material, the body having a surface shaped to fit in the patient's mouth and having a density of up to 98% of the density of the biocompatible material.
- the particles having pre-melting sizes in the range 0 ⁇ m-50 ⁇ m, and having essentially equal proportions of alloy components in each particle.
- the invention relates to a method that has become known in another field as “rapid prototyping” for producing complex tools or components as disclosed in U.S. Pat. No. 4,863,538 included herein by reference.
- shaped bodies made of a sintering powder are built up in layers by exposing each layer successively to the energy of a laser beam that leads to local sintering, whereby the laser beam is guided over the respective powder layer by means of a computer-controlled system using data that represent the configuration of the shaped piece in this layer.
- the powder elements affected in each case are superficially melted and form a fixed bond with each other and the underneath layer. Due to the precise focusing of the laser beam, the energy supply can be configured exactly—at relatively high density—and controlled in accordance with the stored spatial data of the shaped body required.
- the porosity of the resultant part is significantly less than what is achieved under conventional laser sintering.
- densities achieved with the conventional selective laser sintering technique ranges from 70-80%, while the densities achieved through ceramic sintering techniques range from 60-70%.
- the density of the resultant part using a method according to the invention may be greater than 98% of the density of the biocompatible material, and may be as high as 99.9% of the density of the biocompatible material.
- a dense, and therefore strong, part may be formed using the laser selective melting technique. This permits the resultant part to be made with the desired shape without using a mold, but the part is also more able to withstand the high stresses that result from biting and chewing.
- the invention provides for a powder consisting of a biocompatible material of varying grain size between 0 and 50 ⁇ m.
- the invention thus ensures that the shaped body designed for dental purposes is compatible with human tissue (see Hoffmann-Axthelm, Lexikon der Zahn Kunststofftechnik [Encyclopedia of Dental Medicine], 6th/11th edition, p. 97, and Reuling, Biokompatibiltician dentaler Legierieux [Biocompatibility of Dental Alloys]).
- the grain size distribution ensures the forming of dense layers with the advantage of minimal creation of cavities between the layer after melting, which would be susceptible to bacteria cultures forming; in addition, it defines the size and fitting accuracy of the restoration.
- the laser beam follows the contour of the wall to be produced within the cross-section of thin-walled areas.
- the surface of the shaped body produced in accordance with the invention is particularly well-suited for the frequently desired veneering process using ceramic or other materials, as is the case with crowns or bridges. Furthermore, because it is easy to influence the file on which the control process is based, it is possible to make corrections to the configuration of the shaped body that may appear desirable (with respect to the traced result) for a wide variety of reasons.
- the powder preferably comprises an alloy with essentially equal proportions of the alloy components in each grain of powder.
- a shaped body that is selectively melted according to the invention maintains its uniform distribution of alloy components.
- a metal powder with the following composition has proved effective for use with the method according to the invention, whereby the method is not confined to said composition: Ni61, 4Cr22, 9M08, 8Nb3, 9Fe2, 5Mn0.4Ti0.1, where the alloy comprises 61.4% Ni, 22.9% Cr, 8.8% Mo, 3.9% Nb, 2.5% Fe, 0.4% Mn and 0.1% Ti.
Abstract
In a method for forming a dental part, a laser beam is guided over a powder layer of biocompatible material. The laser is guided by a computer controlled laser scanning system based on data representing the shape of the cross-section through the shaped body. The powder is substantially melted by the laser beam to form a layer in the shaped body, to build the shaped body entirely from layers of laser-melted material.
Description
- The present application is a divisional of prior application Ser. No. 10/146,610 filed 14 May 2002, which is a continuation-in-part of application Ser. No. 10/081,039 filed 19 Feb. 2002.
- This invention relates to a method of forming a dental part and/or a tooth replacement part.
- Tooth replacements in the form of crowns, bridges, inlays and the like frequently comprise complex molded bodies which must usually take account in each specific case of the spatial configuration of intact tooth parts (tooth stumps), entire teeth or parts of the jaw that have been lost, on the one hand, and the spatial situation in relation to adjacent and/or antagonistic teeth, on the other hand. In the prior art, such tooth replacement elements are produced in complex processes. The most widespread method is to produce the shaped bodies required—usually made of precious-metal or base-metal alloys, as well as pure metals—in a multi-step impression and casting process.
- Computer-controlled milling of such shaped bodies out of the solid material has become known. This method inevitably leads to considerable waste that has to be reprocessed at great effort and expense.
- The objective of the invention is to provide another, more advantageous way of producing such shaped bodies (and auxiliary dental parts required in implantology) that provides flexibility in manufacturing dental parts of different shapes, but which reduces the amount of waste and results in a strong dental part.
- A method in accordance with the principles of the invention includes a method of making a shaped body for use as a dental part. The method comprises guiding a laser beam over a powder layer using a computer-controlled laser scanning system based on data representing the shape of a cross-section through the shaped body. The powder comprises a biocompatible material of grain size in the range from 0 μm to 50 μm, to create a layer in the shaped body. The method further comprises substantially melting the powder with the laser beam, and repeating the guiding and melting over successive powder layers using successive cross-sectional representative data so as to build the shaped body entirely from layers of laser-melted material.
- In another embodiment of the present invention, a shaped dental part for use in a patient's mouth. The shaped dental part comprises a body formed from melted particles of biocompatible material, the body having a surface shaped to fit in the patient's mouth and having a density of up to 98% of the density of the biocompatible material. The particles having pre-melting sizes in the range 0 μm-50 μm, and having essentially equal proportions of alloy components in each particle.
- The invention relates to a method that has become known in another field as “rapid prototyping” for producing complex tools or components as disclosed in U.S. Pat. No. 4,863,538 included herein by reference. According to said method, shaped bodies made of a sintering powder are built up in layers by exposing each layer successively to the energy of a laser beam that leads to local sintering, whereby the laser beam is guided over the respective powder layer by means of a computer-controlled system using data that represent the configuration of the shaped piece in this layer. As a result of supplying such energy, the powder elements affected in each case are superficially melted and form a fixed bond with each other and the underneath layer. Due to the precise focusing of the laser beam, the energy supply can be configured exactly—at relatively high density—and controlled in accordance with the stored spatial data of the shaped body required.
- Conventionally, in a sintering process, compressed powdered material is heated to a temperature close to but not at melting, usually in a controlled-atmosphere furnace. This is done so that particles may bond by solid state bonding, but not melt. Such sintering increases both density and strength of the material, because compaction alone leads to both properties being low. The latter is also true with sintering without compaction (compressing) the powdered material, as is the case with the selective sintering process addressed before.
- It has been found that, rather than selectively sintering metal powder by superficially melting the uncompressed material, a still considerably higher density of the finished product can be achieved by substantially entirely melting the powdered material, primarily metal. Quite surprisingly, such “selective melting” of the powder does not lead to uncontrolled flowing away of the material, probably because the cohesion forces suffice to keep the thin layer of material in place, even in its molten state.
- Using this method of “selective melting”, the porosity of the resultant part is significantly less than what is achieved under conventional laser sintering. For example, densities achieved with the conventional selective laser sintering technique ranges from 70-80%, while the densities achieved through ceramic sintering techniques range from 60-70%. In contrast, the density of the resultant part using a method according to the invention may be greater than 98% of the density of the biocompatible material, and may be as high as 99.9% of the density of the biocompatible material. Thus, a dense, and therefore strong, part may be formed using the laser selective melting technique. This permits the resultant part to be made with the desired shape without using a mold, but the part is also more able to withstand the high stresses that result from biting and chewing.
- Furthermore, the invention provides for a powder consisting of a biocompatible material of varying grain size between 0 and 50 μm. In contrast to current application of the selective laser sintering method for technical purposes, the invention thus ensures that the shaped body designed for dental purposes is compatible with human tissue (see Hoffmann-Axthelm, Lexikon der Zahnmedizin [Encyclopedia of Dental Medicine], 6th/11th edition, p. 97, and Reuling, Biokompatibilität dentaler Legierungen [Biocompatibility of Dental Alloys]). The grain size distribution ensures the forming of dense layers with the advantage of minimal creation of cavities between the layer after melting, which would be susceptible to bacteria cultures forming; in addition, it defines the size and fitting accuracy of the restoration.
- While larger cross-sectional areas of the dental part to be produced, are impacted by the laser beam by oscillating it in one direction, and shifting the oscillating beam in a direction perpendicular thereto, as explained in U.S. Pat. No. 4,863,538 mentioned above, according to the invention the laser beam follows the contour of the wall to be produced within the cross-section of thin-walled areas.
- Due to its certain degree of roughness, the surface of the shaped body produced in accordance with the invention is particularly well-suited for the frequently desired veneering process using ceramic or other materials, as is the case with crowns or bridges. Furthermore, because it is easy to influence the file on which the control process is based, it is possible to make corrections to the configuration of the shaped body that may appear desirable (with respect to the traced result) for a wide variety of reasons.
- The powder preferably comprises an alloy with essentially equal proportions of the alloy components in each grain of powder. This provides a major advantage compared to the conventional production of shaped dental bodies from melted alloys, because there is no risk of segregation of the alloy components in the melt and/or in the shaped body after casting. In addition, the production of semi-finished products that are made of certain alloys and are particularly advantageous for dental purposes necessitates complicated and costly processes, such as suction casting and the like, whereas pulverization of such alloys is significantly less complex. However, whereas a melt produced from such a powder (for subsequent production of shaped cast bodies) is exposed for its part to the risk of segregation and thus non-homogeneity, a shaped body that is selectively melted according to the invention maintains its uniform distribution of alloy components.
- A metal powder with the following composition has proved effective for use with the method according to the invention, whereby the method is not confined to said composition: Ni61, 4Cr22, 9M08, 8Nb3, 9Fe2, 5Mn0.4Ti0.1, where the alloy comprises 61.4% Ni, 22.9% Cr, 8.8% Mo, 3.9% Nb, 2.5% Fe, 0.4% Mn and 0.1% Ti.
Claims (15)
1. A method of making a shaped body for use as a dental part, comprising:
guiding a laser beam over a powder layer using a computer-controlled laser scanning system based on data representing the shape of a cross-section through the shaped body, the powder comprising a biocompatible material of grain size in the range from 0 μm to 50 μm, to create a layer in the shaped body;
substantially melting the powder with the laser beam; and
repeating the guiding and melting over successive powder layers using successive cross-sectional representative data so as to build the shaped body entirely from layers of laser-melted material.
2. The method as recited in claim 1 , wherein the molten powder substantially maintains the shape of each cross-section through the shaped body.
3 The method as recited in claim 1 , wherein the shaped body has an average density of up to 98% of the density of the biocompatible material.
4. The method as recited in claim 1 , wherein the shaped body has an average density of up to 99.9% of the density of the biocompatible material.
5. The method as recited in claim 1 , wherein the powder comprises an alloy with essentially equal proportions of alloy components in each grain of the powder.
6. The method as recited in claim 1 , wherein the biocompatible material is a metal alloy.
7. The method as recited in claim 1 , wherein the biocompatible material is Ni61.4, Cr22.9, Mo8.8, Nb3.9, Fe2.5, Mn0.4, and Ti0.1.
8. An intermediate for being made into a shaped dental part for use in a patient's mouth, comprising:
a partial body comprising biocompatible material and having a surface shaped to fit in the patient's mouth; and
a layer of powder alloy disposed upon a surface of the partial body and comprising particles of the biocompatible material, the particles generally being of a predetermined density, having varying grain sizes in a range of about 0 μm to about 50 μm, and having essentially equal proportions of alloy components in each particle;
wherein the biocompatible material of the partial body has a density of not less than about 98% of the predetermined density of the particles.
9 The intermediate as recited in claim 8 , wherein the biocompatible material of the partial body has a density between 98% and 99.9% of the predetermined density.
10 The intermediate as recited in claim 8 , wherein the biocompatible material is a metal alloy.
11. The intermediate as recited in claim 8 , wherein the biocompatible material is 61.4% Ni, 22.9% Cr, 8.8% Mo, 3.9% Nb, 2.5% Fe, 0.4% Mn, and 0.1% Ti.
12. The intermediate as recited in claim 8 wherein the particle layer is of a thickness for forming a layer of cohesively maintained biocompatible material, when melted by a guided laser beam, to enlarge the partial body.
13. An intermediate for being made into a shaped dental part for use in a patient's mouth, comprising:
a partial body comprising biocompatible material and having a surface shaped to fit in the patient's mouth; and
a layer of powder alloy disposed upon a surface of the partial body and consisting of particles of biocompatible material generally having a predetermined density and essentially equal proportions of alloy components, the particles further having varying grain sizes in a range of from about 0 μm to about 50 μm;
wherein the biocompatible material of the partial body has a density of not less than about 98% of the predetermined density of the particles; and
wherein the particle layer is of a thickness for forming a layer of cohesively maintained biocompatible material, when melted by a guided laser beam, to enlarge the partial body.
14. The intermediate as recited in claim 14 , wherein the biocompatible material is a metal alloy.
15. The intermediate as recited in claim 14 , wherein the biocompatible material is 61.4% Ni, 22.9% Cr, 8.8% Mo, 3.9% Nb, 2.5% Fe, 0.4% Mn, and 0.1% Ti.
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/976,734 US20050056350A1 (en) | 1999-01-19 | 2004-10-29 | Method for producing tooth replacements and auxiliary dental parts |
US12/578,371 US20100028191A1 (en) | 1999-01-19 | 2009-10-13 | Method for Producing Tooth Replacements and Auxiliary Dental Parts |
US13/316,062 US20120148987A1 (en) | 1999-01-19 | 2011-12-09 | Method For Producing Tooth Replacements And Auxiliary Dental Parts |
US15/422,194 US20170135789A1 (en) | 1999-01-19 | 2017-02-01 | Method for producing tooth replacements and auxiliary parts |
Applications Claiming Priority (5)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE19901643A DE19901643A1 (en) | 1999-01-19 | 1999-01-19 | Process for the production of dentures and dental auxiliary parts |
DE19901643.7 | 1999-01-19 | ||
US8103902A | 2002-02-19 | 2002-02-19 | |
US10/146,610 US20020187458A1 (en) | 1999-01-19 | 2002-05-14 | Method for producing tooth replacements and auxiliary dental parts |
US10/976,734 US20050056350A1 (en) | 1999-01-19 | 2004-10-29 | Method for producing tooth replacements and auxiliary dental parts |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
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US10/146,610 Division US20020187458A1 (en) | 1999-01-19 | 2002-05-14 | Method for producing tooth replacements and auxiliary dental parts |
Related Child Applications (1)
Application Number | Title | Priority Date | Filing Date |
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US12/578,371 Continuation US20100028191A1 (en) | 1999-01-19 | 2009-10-13 | Method for Producing Tooth Replacements and Auxiliary Dental Parts |
Publications (1)
Publication Number | Publication Date |
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US20050056350A1 true US20050056350A1 (en) | 2005-03-17 |
Family
ID=34279311
Family Applications (5)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/146,610 Abandoned US20020187458A1 (en) | 1999-01-19 | 2002-05-14 | Method for producing tooth replacements and auxiliary dental parts |
US10/976,734 Abandoned US20050056350A1 (en) | 1999-01-19 | 2004-10-29 | Method for producing tooth replacements and auxiliary dental parts |
US12/578,371 Abandoned US20100028191A1 (en) | 1999-01-19 | 2009-10-13 | Method for Producing Tooth Replacements and Auxiliary Dental Parts |
US13/316,062 Abandoned US20120148987A1 (en) | 1999-01-19 | 2011-12-09 | Method For Producing Tooth Replacements And Auxiliary Dental Parts |
US15/422,194 Abandoned US20170135789A1 (en) | 1999-01-19 | 2017-02-01 | Method for producing tooth replacements and auxiliary parts |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
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US10/146,610 Abandoned US20020187458A1 (en) | 1999-01-19 | 2002-05-14 | Method for producing tooth replacements and auxiliary dental parts |
Family Applications After (3)
Application Number | Title | Priority Date | Filing Date |
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US12/578,371 Abandoned US20100028191A1 (en) | 1999-01-19 | 2009-10-13 | Method for Producing Tooth Replacements and Auxiliary Dental Parts |
US13/316,062 Abandoned US20120148987A1 (en) | 1999-01-19 | 2011-12-09 | Method For Producing Tooth Replacements And Auxiliary Dental Parts |
US15/422,194 Abandoned US20170135789A1 (en) | 1999-01-19 | 2017-02-01 | Method for producing tooth replacements and auxiliary parts |
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US (5) | US20020187458A1 (en) |
Cited By (22)
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US20060166159A1 (en) * | 2005-01-25 | 2006-07-27 | Norbert Abels | Laser shaping of green metal body used in manufacturing an orthodontic bracket |
US20070092854A1 (en) * | 2005-10-24 | 2007-04-26 | Powell Theodore M | Methods for manufacturing dental implant components |
WO2007045643A1 (en) * | 2005-10-17 | 2007-04-26 | Sirona Dental Systems Gmbh | Method for producing a denture |
ES2282037A1 (en) * | 2006-03-08 | 2007-10-01 | Juan Carlos Garcia Aparicio | Method for manufacturing digitally-designed removable dental prostheses and system required for this purpose |
US20080153067A1 (en) * | 2005-10-24 | 2008-06-26 | Biomet 3I, Inc. | Methods for placing an implant analog in a physical model of the patient's mouth |
US20080286722A1 (en) * | 2007-05-18 | 2008-11-20 | Biomet 3I, Inc. | Method for selecting implant components |
US20090130630A1 (en) * | 2007-11-16 | 2009-05-21 | Suttin Zachary B | Components for Use with a Surgical Guide for Dental Implant Placement |
US20090169841A1 (en) * | 2005-01-25 | 2009-07-02 | Ormco Corporation | Methods for shaping green bodies and articles made by such methods |
US20110129792A1 (en) * | 2008-04-15 | 2011-06-02 | Berckmans Iii Bruce | Method of creating an accurate bone and soft-tissue digital dental model |
US20110183289A1 (en) * | 2005-06-30 | 2011-07-28 | Implant Innovations, Inc. | Method For Manufacting Dental Implant Components |
US8221121B2 (en) | 2008-04-16 | 2012-07-17 | Biomet 3I, Llc | Method for pre-operative visualization of instrumentation used with a surgical guide for dental implant placement |
US8882508B2 (en) | 2010-12-07 | 2014-11-11 | Biomet 3I, Llc | Universal scanning member for use on dental implant and dental implant analogs |
US8926328B2 (en) | 2012-12-27 | 2015-01-06 | Biomet 3I, Llc | Jigs for placing dental implant analogs in models and methods of doing the same |
US8944818B2 (en) | 2011-05-16 | 2015-02-03 | Biomet 3I, Llc | Temporary abutment with combination of scanning features and provisionalization features |
US9089382B2 (en) | 2012-01-23 | 2015-07-28 | Biomet 3I, Llc | Method and apparatus for recording spatial gingival soft tissue relationship to implant placement within alveolar bone for immediate-implant placement |
US9452032B2 (en) | 2012-01-23 | 2016-09-27 | Biomet 3I, Llc | Soft tissue preservation temporary (shell) immediate-implant abutment with biological active surface |
US9668863B2 (en) | 2009-08-19 | 2017-06-06 | Smith & Nephew, Inc. | Porous implant structures |
US9668834B2 (en) | 2013-12-20 | 2017-06-06 | Biomet 3I, Llc | Dental system for developing custom prostheses through scanning of coded members |
US9700390B2 (en) | 2014-08-22 | 2017-07-11 | Biomet 3I, Llc | Soft-tissue preservation arrangement and method |
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Also Published As
Publication number | Publication date |
---|---|
US20120148987A1 (en) | 2012-06-14 |
US20100028191A1 (en) | 2010-02-04 |
US20020187458A1 (en) | 2002-12-12 |
US20170135789A1 (en) | 2017-05-18 |
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