CA2295896C - Method for producing tooth replacements and auxiliary dental parts - Google Patents

Method for producing tooth replacements and auxiliary dental parts Download PDF

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Publication number
CA2295896C
CA2295896C CA002295896A CA2295896A CA2295896C CA 2295896 C CA2295896 C CA 2295896C CA 002295896 A CA002295896 A CA 002295896A CA 2295896 A CA2295896 A CA 2295896A CA 2295896 C CA2295896 C CA 2295896C
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CA
Canada
Prior art keywords
powder
layer
sintering
laser beam
shaped body
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.)
Expired - Lifetime
Application number
CA002295896A
Other languages
French (fr)
Other versions
CA2295896A1 (en
Inventor
Haig Dolabdjian
Roland Strietzel
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.)
Bego Bremer Goldschlagerei Wilh Herbst GmbH and Co KG
Original Assignee
Bego Bremer Goldschlagerei Wilh Herbst GmbH and Co KG
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
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Application filed by Bego Bremer Goldschlagerei Wilh Herbst GmbH and Co KG filed Critical Bego Bremer Goldschlagerei Wilh Herbst GmbH and Co KG
Publication of CA2295896A1 publication Critical patent/CA2295896A1/en
Application granted granted Critical
Publication of CA2295896C publication Critical patent/CA2295896C/en
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Classifications

    • 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
    • A61C13/0022—Blanks or green, unfinished dental restoration parts
    • 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
    • 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
    • B33Y70/00—Materials specially adapted for additive manufacturing
    • C—CHEMISTRY; METALLURGY
    • C22—METALLURGY; FERROUS OR NON-FERROUS ALLOYS; TREATMENT OF ALLOYS OR NON-FERROUS METALS
    • C22C—ALLOYS
    • C22C1/00—Making non-ferrous alloys
    • C22C1/04—Making non-ferrous alloys by powder metallurgy
    • C22C1/0433—Nickel- or cobalt-based alloys
    • 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
    • A61C13/0013—Production methods using stereolithographic techniques
    • 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
    • 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
    • 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]
    • 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
    • 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

Abstract

Application of the laser sintering process, in which shaped pieces 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 body in this layer, for the production of tooth replacement elements (crowns, bridges, inlays and the like) and/or dental parts, whereby the powder comprises a biocompatible material of varying grain size between 0 and 50 µm.

Description

SEGO Bremer Goldschlagerei Wilh. Herbst GmbH & Co., Wilhelm-Herbst-Strat3e 1, 28359 Bremen, Germany Method for producing tooth replacements and auxiliary dental parts 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. However, computer-controlled milling of such shaped bodies out of the solid material, which inevitably leads to considerable waste that has to be reprocessed at great effort and expense, has also become known.
The objective of the invention is to provide another, more advantageous way of producing such shaped bodies (and auxiliary dental parts required in implantology).
The invention uses a method that has become known in another field as "rapid prototyping" for producing complex tools or components. 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. Due to the precise focusing of the laser beam, the energy supply can be configured exactly - at high density - and controlled in accordance with the stored spatial data of the shaped body required.
Furthermore, the invention provides for a powder consisting of a biocompatible material of varying grain size between 0 and 50 Nm. In contrast to current application of the 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/1lth edition, p. 97, and Reuling, Biokompatibilitat dentaler Lec~ieruncten [Biocompatibility of Dental Alloys]). The grain size distribution ensures extremely dense sintering with the advantage of a high compressive load capacity of the shaped body and minimal creation of cavities, which would be susceptible to bacteria cultures forming; in addition, it defines the size and fitting accuracy of the restoration.
However, it is also possible to carry out precise local compacting of the powdery initial material in another way, whether by supplying energy in a different manner or, - in the case of plastics as the initial material - by controlling locally confined polymerization. In general, however, optically focusable electromagnetic radiation is preferable to other means of energy transfer, such as corpuscular radiation carried out in a vacuum.
Due to its certain degree of roughness, the sintering 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 sintered according to the invention main-tains 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:
Ni (Nickel) 61.4 Cr (Chromium) 22.9 Mo (Molybdenum) 8.8 Nb (Niobium) 3.9 Fe (Iron) 2.5 Mn (Manganese) 0.4 Ti (Titanium) 0.1 Total 100

Claims (3)

1. Method for producing tooth replacement elements or auxiliary dental parts, wherein the method comprises a laser sintering process, in which shaped bodies made of a sintering powder are built up in layers by exposing each layer succes-sively 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, whereby the powder comprises a biocompatible material of varying grain sizes between 0 and 50 µm.
2. Method according to claim 1, characterized by the fact that the powder comprises an alloy with essentially equal proportions of the alloy components in each grain of powder.
3. Shaped body for use as a tooth replacement or as dental auxiliary parts, wherein the shaped body is built of a powder being laser sintered and comprising a biocompatible material of varying grain sizes between 0 and 50 pm and by applica-tion of a method according to claim 1 or 2.
CA002295896A 1999-01-19 2000-01-14 Method for producing tooth replacements and auxiliary dental parts Expired - Lifetime CA2295896C (en)

Applications Claiming Priority (2)

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

Publications (2)

Publication Number Publication Date
CA2295896A1 CA2295896A1 (en) 2000-07-19
CA2295896C true CA2295896C (en) 2005-05-24

Family

ID=7894535

Family Applications (1)

Application Number Title Priority Date Filing Date
CA002295896A Expired - Lifetime CA2295896C (en) 1999-01-19 2000-01-14 Method for producing tooth replacements and auxiliary dental parts

Country Status (5)

Country Link
EP (3) EP1021997B2 (en)
AT (1) ATE361716T1 (en)
CA (1) CA2295896C (en)
DE (4) DE29924924U1 (en)
ES (1) ES2285813T3 (en)

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US7927538B2 (en) 2008-07-30 2011-04-19 Ivoclar Vivadent Ag Light-curing slips for the stereolithographic preparation of dental ceramics
US8147861B2 (en) 2006-08-15 2012-04-03 Howmedica Osteonics Corp. Antimicrobial implant
AU2008201238B2 (en) * 2007-03-19 2012-08-09 Degudent Gmbh Method for the manufacture of dental protheses
US8268099B2 (en) 2002-11-08 2012-09-18 Howmedica Osteonics Corp. Laser-produced porous surface
US8556981B2 (en) 2005-12-06 2013-10-15 Howmedica Osteonics Corp. Laser-produced porous surface
US9364896B2 (en) 2012-02-07 2016-06-14 Medical Modeling Inc. Fabrication of hybrid solid-porous medical implantable devices with electron beam melting technology
US10588749B2 (en) 2009-08-19 2020-03-17 Smith & Nephew, Inc. Porous implant structures

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US6776614B2 (en) 2002-02-13 2004-08-17 Lingualcare, Inc. Modular system for customized orthodontic appliances
DE10219983B4 (en) 2002-05-03 2004-03-18 Bego Medical Ag Process for manufacturing products using free-form laser sintering
EP1870667A3 (en) * 2002-10-18 2008-03-19 Aepsilon Rechteverwaltungs GmbH Devices and methods for capturing surfaces and for producing denture elements
US20060147332A1 (en) 2004-12-30 2006-07-06 Howmedica Osteonics Corp. Laser-produced porous structure
DE10315563A1 (en) 2003-04-05 2004-10-28 Bego Medical Ag Process for producing implant structures for dental implants and implant structure for dental implants
DE10335272A1 (en) * 2003-08-01 2005-03-03 Bego Semados Gmbh Arrangement for guiding a dental implant drill, drilling template and drilling template receiving implant for the arrangement and method for producing this surgical template
DE10342231B4 (en) * 2003-09-11 2008-04-30 Sirona Dental Systems Gmbh Blank for the production of a tooth replacement part and method for producing the same
DE10350570A1 (en) * 2003-10-30 2005-06-16 Bego Semados Gmbh Making bone replacement material employs laser beam to sinter or melt loose particles, bonding them together into granular unit with controlled porosity
DE102004009126A1 (en) * 2004-02-25 2005-09-22 Bego Medical Ag Method and device for generating control data sets for the production of products by free-form sintering or melting and device for this production
DE102004052364A1 (en) * 2004-10-28 2006-06-22 BEGO Bremer Goldschlägerei Wilh. Herbst GmbH & Co. KG Method for producing a dental model, a dental model with a ceramic layer deposited thereon, as well as a dental molding, dental model, and use of a 3D printer and a kit
DE102005052113A1 (en) 2005-06-03 2006-12-28 Stefan Wolz Process for the production of dental parts from dental metal powder
DE102006010808B4 (en) * 2006-03-07 2009-08-13 BEGO Bremer Goldschlägerei Wilh. Herbst GmbH & Co. KG Apparatus, system, method, computer program and data carrier for electrophoretic deposition with a movable electrode
ES2282037B1 (en) * 2006-03-08 2008-09-16 Juan Carlos Garcia Aparicio MANUFACTURING PROCEDURE FOR DIGITAL REMOVABLE DENTAL PROTESIES DESIGNED AND SYSTEM REQUIRED FOR SUCH PURPOSE.
WO2009014718A1 (en) 2007-07-24 2009-01-29 Porex Corporation Porous laser sintered articles
DE102008031926A1 (en) 2008-07-08 2010-01-14 Bego Medical Gmbh Process for layering steeply inclined surfaces
DE102008031925B4 (en) 2008-07-08 2018-01-18 Bego Medical Gmbh Dual manufacturing process for small series products
EP2289652B2 (en) 2009-08-25 2022-09-28 BEGO Medical GmbH Device and method for generative production
EP2289462B1 (en) 2009-08-25 2012-05-30 BEGO Medical GmbH Device and method for continuous generative production
DE102009039880A1 (en) 2009-09-03 2011-03-31 Schmidt, Rainer, Dr. med. dent. Inter-oral reconstruction aid for use at front tooth for producing veneer, has mold formed as shaping- and/or application aid, and outer surface comprising adhesive surface for layer to be aligned on adjacent teeth
DE102010029078A1 (en) 2010-05-18 2011-11-24 Matthias Fockele Producing an article by layer-wise structures made of powdered metallic or ceramic material, comprises individually preparing material powder layers subsequent to each other on a support, and location-selectively solidifying each layer
EP2404590B1 (en) 2010-07-08 2019-06-12 Ivoclar Vivadent AG Light hardening ceramic dross for stereolithographic production of highly stable ceramics
DE202011003443U1 (en) 2011-03-02 2011-12-23 Bego Medical Gmbh Device for the generative production of three-dimensional components
US9135374B2 (en) 2012-04-06 2015-09-15 Howmedica Osteonics Corp. Surface modified unit cell lattice structures for optimized secure freeform fabrication
US9180010B2 (en) 2012-04-06 2015-11-10 Howmedica Osteonics Corp. Surface modified unit cell lattice structures for optimized secure freeform fabrication
WO2013167903A1 (en) 2012-05-10 2013-11-14 Renishaw Plc Method of manufacturing an article
EP2849672B1 (en) 2012-05-10 2019-10-16 Renishaw Plc. Method of manufacturing an article
DE102012108217A1 (en) 2012-05-24 2013-12-24 Degudent Gmbh Producing a molding, preferably medical molding e.g. hip joint or knee joint, comprises producing molding based on digitalized data, simultaneously producing fixing structure originating from molding, fixing the molding, and post-processing
GB2509138A (en) 2012-12-21 2014-06-25 Nobel Biocare Services Ag Dental component with screw fixation
GB2509135A (en) 2012-12-21 2014-06-25 Nobel Biocare Services Ag An abutment with conical metal adapter
GB2509136A (en) 2012-12-21 2014-06-25 Nobel Biocare Services Ag Dental component with metal adapter
DE102014203458A1 (en) 2014-02-26 2015-09-10 Gebr. Brasseler Gmbh & Co. Kg Method for producing a medical instrument by means of an additive method
EP3111882B1 (en) 2015-07-02 2020-08-05 Coltène/Whaledent AG Method for producing an individually manufactured dental replacement structure
US11298747B2 (en) 2017-05-18 2022-04-12 Howmedica Osteonics Corp. High fatigue strength porous structure
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Cited By (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8268099B2 (en) 2002-11-08 2012-09-18 Howmedica Osteonics Corp. Laser-produced porous surface
US8556981B2 (en) 2005-12-06 2013-10-15 Howmedica Osteonics Corp. Laser-produced porous surface
US8728387B2 (en) 2005-12-06 2014-05-20 Howmedica Osteonics Corp. Laser-produced porous surface
US8147861B2 (en) 2006-08-15 2012-04-03 Howmedica Osteonics Corp. Antimicrobial implant
AU2008201238B2 (en) * 2007-03-19 2012-08-09 Degudent Gmbh Method for the manufacture of dental protheses
US7927538B2 (en) 2008-07-30 2011-04-19 Ivoclar Vivadent Ag Light-curing slips for the stereolithographic preparation of dental ceramics
US10588749B2 (en) 2009-08-19 2020-03-17 Smith & Nephew, Inc. Porous implant structures
US10945847B2 (en) 2009-08-19 2021-03-16 Smith & Nephew, Inc. Porous implant structures
US11529235B2 (en) 2009-08-19 2022-12-20 Smith & Nephew, Inc. Porous implant structures
US11793645B2 (en) 2009-08-19 2023-10-24 Smith & Nephew, Inc. Porous implant structures
US9364896B2 (en) 2012-02-07 2016-06-14 Medical Modeling Inc. Fabrication of hybrid solid-porous medical implantable devices with electron beam melting technology

Also Published As

Publication number Publication date
EP1021997B1 (en) 2007-05-09
EP3103412A1 (en) 2016-12-14
DE59914332D1 (en) 2007-06-21
EP1021997B2 (en) 2020-07-01
CA2295896A1 (en) 2000-07-19
DE19901643A1 (en) 2000-07-20
DE29924925U1 (en) 2007-06-21
DE29924924U1 (en) 2006-12-21
ES2285813T3 (en) 2007-11-16
EP1021997A2 (en) 2000-07-26
EP1021997A3 (en) 2001-12-19
EP1836993A1 (en) 2007-09-26
ATE361716T1 (en) 2007-06-15

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