US3896547A - Prosthetic article and method for manufacture - Google Patents
Prosthetic article and method for manufacture Download PDFInfo
- Publication number
- US3896547A US3896547A US466167A US46616774A US3896547A US 3896547 A US3896547 A US 3896547A US 466167 A US466167 A US 466167A US 46616774 A US46616774 A US 46616774A US 3896547 A US3896547 A US 3896547A
- Authority
- US
- United States
- Prior art keywords
- percent
- article
- element selected
- inorganic oxide
- alloy
- 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
Links
Classifications
-
- C—CHEMISTRY; METALLURGY
- C22—METALLURGY; FERROUS OR NON-FERROUS ALLOYS; TREATMENT OF ALLOYS OR NON-FERROUS METALS
- C22C—ALLOYS
- C22C19/00—Alloys based on nickel or cobalt
- C22C19/03—Alloys based on nickel or cobalt based on nickel
- C22C19/05—Alloys based on nickel or cobalt based on nickel with chromium
- C22C19/051—Alloys based on nickel or cobalt based on nickel with chromium and Mo or W
- C22C19/055—Alloys based on nickel or cobalt based on nickel with chromium and Mo or W with the maximum Cr content being at least 20% but less than 30%
-
- 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
-
- 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
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/02—Inorganic materials
- A61L27/04—Metals or alloys
- A61L27/047—Other specific metals or alloys not covered by A61L27/042 - A61L27/045 or A61L27/06
-
- C—CHEMISTRY; METALLURGY
- C23—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; CHEMICAL SURFACE TREATMENT; DIFFUSION TREATMENT OF METALLIC MATERIAL; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL; INHIBITING CORROSION OF METALLIC MATERIAL OR INCRUSTATION IN GENERAL
- C23C—COATING METALLIC MATERIAL; COATING MATERIAL WITH METALLIC MATERIAL; SURFACE TREATMENT OF METALLIC MATERIAL BY DIFFUSION INTO THE SURFACE, BY CHEMICAL CONVERSION OR SUBSTITUTION; COATING BY VACUUM EVAPORATION, BY SPUTTERING, BY ION IMPLANTATION OR BY CHEMICAL VAPOUR DEPOSITION, IN GENERAL
- C23C24/00—Coating starting from inorganic powder
Definitions
- ABSTRACT There is disclosed a prosthetic article formed of an alloy containing 12-20 percent chromium; 7-12 percent cobalt; 1.5-5 percent of at least one of molybdenum, tungsten, columbium, and tantalum; 5-9 percent of at least one aluminum and titanium; 0.050.2 percent carbon; 0.0050.l percent boron; 0.05-0.2 percent of at least one of zirconium and hafnium; and the balance nickel, which may receive a strongly bonded, fused, inorganic oxide coating; and a method for manufacturing the article which includes melting the alloy in air,
- Metals used for dental prosthetic devices must also be capable of accepting inorganic oxide coatings such as dental procelain. To do this, the metals must have a compatible oxide coating on their surface. A compatible oxide coating is one that forms a bond with the fused inorganic oxide coating which is. applied later. Alloys used in dental prosthetic devices must also have a coefficient of thermal expansion not too different from that of the fused inorganic oxide coatings that are used in conjunction with them, otherwise the temperature cycling experienced in applying and fusing one or more layers of inorganic oxide coating would result in cracking of the coating and sloughing off if great differences in thermal expansion were experienced between the oxide and the metal.
- Non-precious dental alloys have been known in the past.
- One such alloy is an alloy that is primarily nickel and includes beryllium as a critical alloying element. This alloy is described in US. Pat. No. 3,749,570.
- the alloy has satisfactory physical properties, problems are encountered both in the preparation of the alloy and in the preparation of devices from it because of the highly toxic nature of beryllium. All processes in forming such an alloy into a suitable prosthetic device must be carried on with extreme caution so that fumes, dust, or other forms of the alloy or its compounds are not inhaled or ingested by workers.
- Particularly in small laboratories, such as those in individual dentists offices it is very difficult if not impossible to provide adequate safety measures for using such a dangerous material. Even if adequate safety equipment is available, it is difficult to insure that all workers in the laboratories are sophisticated enough to understand the hazards of working beryllium alloys and to employ the safety devices that are available.
- the invention includes a prosthetic device made of a non-precious alloy which forms a natural oxide coating that is not only compatible with conventional fused inorganic oxides applied to dental devices, but actually participates in the bond between the fused inorganic oxide and the metal.
- the expansion and contraction of the alloy with changes of temperature correspond so closely with the expansion and contraction of the fused inorganic oxides that cracking of the fused oxides is avoided.
- the alloy also does not contain highly toxic materials so that it may be melted, cast, ground, and otherwise worked without special precautions to avoid toxic effects.
- prosthetic device is defined as a metal device that is attached to a living animal in direct contact with living tissue to replace a missing part or to repair a malfunctioning part.
- Prosthetic devices may be as simple as metal. inlays to fill teeth but are usually more complex, such as caps for teeth, bridges, plates or implants in bones of legs, jaws, etc.
- fused inorganic oxide refers to a substance made of inorganic oxide having its physical form altered by being subjected to high temperature. Typically a fused inorganic oxide is glazed porcelain or a vitreous material such as those used in detnal work.
- bony tissue refers to any hard bone-like tissue and includes tissue such as teeth.
- bonded is defined to mean: firmly fixed to a surface without the use of an intermediary bonding material such as organic cement.
- the alloys employed in the articles of this invention are those containing from 12-20 percent chromium; from 7-12 percent cobalt; from 1.5-5 percent of at least one of molybdenum, tungsten, columbium, or tantalum; from 5-9 percent of at least one of aluminum and titanium; from 0.5-0.2 percent carbon;- from 0.005-0.1 percent boron; from 0.050.2 percent of at least one of zirconium and hafnium; and the balance substantially nickel.
- the alloy is formed usually by melting in air and then casting, after which it may or may not be coated completely or partially with a fused inorganic oxide coating that is bonded to its surface.
- the article is shaped to conform to, and to be attached to, bony tissue of a living animal.
- the alloy has been found to be entirely compatible not only with the bony tissue to which it is attached but also with soft tissue with which it is in contact.
- a cap fora tooth made from the alloy of this invention coated with porcelain can be worn comfortably indefinitely by a human being. Neither the porcelain nor the alloy reacts unfavorably with the tooth or the gums, and the, alloy is corrosion resistant enough to remain uncorroded in contact with body fluids and to resist galvaniceffects with different metals such as may be found withinthe mouth.
- a person having a cap made of the alloy referred to above in his mouth along with a gold filling in a different tooth and a silver amalgam filling in still a different tooth will have no galvanic reaction set up between the cap and the other metals to destroy any of the metals or to create discomfort.
- the alloy of this invention must contain the essential ingredients enumerated above; however, other ingredients may also be included within its composition.
- One particularly useful alloy that is commercially available contains 15-18 percent chromium, 8-11 percent cobalt, 0.75-2.2 percent molybdenum, 1.8-3 percent tungsten, 0.5-2 percent columbium, l-3 percent tantalum, 3-4 percent aluminum, 0.1-2 percent carbon, 3-4 percent titanium, 0.01-0.05 percent boron, 0.0l-0..2 percent zirconium, and the balance nickel.
- This alloy is described in US. Pat. No. 3,459,545 as an alloy suitable for turbine blades in gas turbine engines.
- the alloys described above are suitable to be shaped by any of the techniques usually employed in forming prosthetic devices for alloys.
- the initial step in shaping an alloy involves melting it in air and casting it.
- the resulting cast article has a thin oxide coating which adheres tightly to the metal and is compatible with the fused inorganic oxides that are generally employed for coating such prosthetic devices.
- the fused inorganic oxides are primarily silicon oxide and aluminum oxide or various compounds of silicon, aluminum and oxygen. Photomicrographs of the bond between the alloys described above and such materials as dental porcelain indicate that the bond is not effected at a sharp interface between the porcelain and the metal oxide layer.
- the natural oxide coating on the metal merges with the fused inorganic oxide to create a deep bond that has a composition gradient from the surface of the metal to the fused inorganic oxide coating. It is speculated that this deep bond, indicating a special compatibility between the fused inorganic oxides and the metal oxide coating, is the reason for the extremely firm bond that permits the alloy of this invention to be coated with fused inorganic oxides that do not crack during temperature cycling or chip off when subjected to compressive forces or abrasion.
- the fused inorganic oxides may be glazed, as dental porcelainis, or they may be porous, for example in the form of a porcelain bisque Fused dental porcelain may be applied in several layers, as is conventional in the art.
- the metal shaped as a prosthetic device may first be coated with an opaque layer to mask the metal, after which it is coated with a porcelain layer, and finally coated with a vitreous enamel layer to produce a natural, translucent, tooth-like appearance.
- the metal prosthetic device is to be implanted directly in bony tissue, it preferably is coated with porcelain bisque.
- Porcelain bisque is compatible with living tissue and is porous enough for fibrous tissue to grow into the pores thereby forming a firm connection between the bony tissue and the prosthetic device.
- an artificial hip joint may be made so that the portion connected to the femur is coated with porcelain bisque.
- An alloy pin so made will not only be compatible with bone tissue but will permit fibrous bone tissue to grow in the pores of the porcelain bisque to effect a very firm connection.
- Those portions of dental prosthetic devices that are implanted directly in jawbones also are preferably coated with porcelain bisque.
- a wax model of the cap is prepared by conventional techniques.
- the wax model is surrounded with what is referred to in this art as high-heat oxy-phosphate investment, and a wax insert is appropriately placed to form a sprue. Wax is removed from the investment by heating the investment to 700F for thirty minutes followed by a burnout for 1 hour at 1600F.
- the investment is fixed in a conventional centrifical casting device; and an alloy containing 16 percent chromium, percent cobalt, 2 percent molybdenum, 2.5 percent tungsten, 1 percent columbium, 1.25 percent tantalum, 3.5 percent aluminum, 3.5 percent titanium, 0.18 percent carbon, 0.02 percent boron, 0.1 percent zirconium, and 59.95 percent nickel is placed in a quartz crucible and melted wit a torch fed with acetylene and oxygen. A gas mixture obtained by setting oxygen pressure at 10 psi and acetylene pressure at 8 psi is employed. The alloy melts at a temperature slightly higher than 2450F as indicated by the metal in the crucible slumping. A casting flux is added when the alloy begins to slump; and when the temperature is raised slightly higher the alloy becomes very fluid and forms in the shape of a sphere in the crucible. When the alloy is highly fluid it is allowed to run from the crucible into the mold.
- the casting is removed from the mold, and it is worked on as necessary with burrs or other tools, after which it is thoroughly cleaned by sandblasting with fine sand.
- Copings can be dressed down to 0.1-0.2 mm, which is about half the thickness required for gold dental alloys.
- An article comprising a solid alloy comprising from about 12-20 percent chromium, from about 7-12 percent cobalt, from about 1.5-5 percent of at least one element selected from molybdenum, tungsten, columbium and tantalum, from about 5-9 percent of at least one element selected from aluminum and titanium, from about 0.05-0.2 percent carbon, from about 0.005-0.1 percent boron, from about 0.050.2 percent of at least one element selected from zirconium and hafnium and the balance nickel which is shaped to conform with the shape of bony tissue of a living animal and for attachment to said bony tissue.
- An article comprising a solid alloy comprising from about 12-20 percent chromium, from about 7-12 percent cobalt, from about 1.5-5 percent of at least one element selected from molybdenum, tungsten, columbium and tantalum, from about 5-9 percent of at least one element selected from aluminum and titanium, from about 0.050.2 percent carbon, from about 0.005-0.l percent boron, from about 0.05-0.2 percent of at least one element selected from zirconium and hafnium and the balance nickel, having a fused inorganic oxide bonded to the surface thereof.
- said alloy consists essentially of 15-18 percent chromium, 8-11 percent cobalt, 0.75-2.2 percent molybdenum, 1.8-3 percent tungsten, 0.5-2 percent columbium, 1-3 percent tantalum, 3-4 percent aluminum, 0.1-0.2 percent carbon, 3-4 percent titanium with a total content of aluminum and titanium not exceeding 7.5 percent, 0.01-0.05 percent boron, 0.0l-0.2 percent zirconium and the balance essentially nickel.
- the article of claim 3 shaped to conform with the shape of bony tissue of a living animal for attachment to said bony tissue.
- a process for producing a prosthetic device comprising:
- A. Forming a shaped article of an alloy comprising from about 12-20 percent chromium, from about 7-12 percent cobalt, from about 1.5-5 percent of at least one element selected from molybdenum, tungsten, columbium and tantalum, from about 5-9 percent of at least one element selected from aluminum and titanium, from about 0.05-0.2 percent carbon, from about 0.0050.1 percent boron, from about 0.05-0.2 percent of at least one element selected from zirconium and hafnium and the balance nickel, said article being shaped for attachment to bony tissue of a living animal;
- said alloy consists essentially of 15-18 percent chromium, 8-11 percent cobalt, 0.75-2.2 percent molybdenum, 1.8-3 percent tungsten, 0.5-2 percent columbium, 1-3 percent tantalum, 3-4 percent aluminum, 0.1-0.2 percent carbon, 3-4 percent titanium with a total content of aluminum and titanium not exceeding 7.5 percent, 0.01-0.05 percent boron, 0.01-0.2 percent zirconium and the balance essentially nickel.
- a physiologically compatible prosthetic alloy consisting essentially of from about 12-20 percent chromium, from about 7-12 percent cobalt, from about 1.5-5 percent of at least one element selected from molybdenum, tungsten, columbium and tantalum, from about 5-9 percent of at least one element selected from aluminum and titanium, from about 0.05-0.2 percent carbon, from about 0.0050.1 percent boron, from ab0ut-0.050.2 percent of at least one element selected from zirconium and hafnium and the balance nickel.
Abstract
Description
Claims (13)
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US466167A US3896547A (en) | 1974-05-02 | 1974-05-02 | Prosthetic article and method for manufacture |
DE19752514672 DE2514672A1 (en) | 1974-05-02 | 1975-04-04 | PROSTHETIC ITEMS AND MATERIALS SUITABLE FOR THEM |
FR7511464A FR2269322A1 (en) | 1974-05-02 | 1975-04-11 | |
JP50049206A JPS50147419A (en) | 1974-05-02 | 1975-04-24 |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US466167A US3896547A (en) | 1974-05-02 | 1974-05-02 | Prosthetic article and method for manufacture |
Publications (1)
Publication Number | Publication Date |
---|---|
US3896547A true US3896547A (en) | 1975-07-29 |
Family
ID=23850770
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US466167A Expired - Lifetime US3896547A (en) | 1974-05-02 | 1974-05-02 | Prosthetic article and method for manufacture |
Country Status (4)
Country | Link |
---|---|
US (1) | US3896547A (en) |
JP (1) | JPS50147419A (en) |
DE (1) | DE2514672A1 (en) |
FR (1) | FR2269322A1 (en) |
Cited By (21)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4126924A (en) * | 1977-02-07 | 1978-11-28 | General Atomic Company | Socket and joint prostheses |
US4129944A (en) * | 1975-02-03 | 1978-12-19 | Johnson & Johnson | Dental constructions and dental alloys |
US4145764A (en) * | 1975-07-23 | 1979-03-27 | Sumitomo Chemical Co., Ltd. | Endosseous implants |
US4336617A (en) * | 1980-01-21 | 1982-06-29 | Shin-Etsu Chemical Company Limited | Prosthetic substituted member for living body and a method for the surgical treatment by use thereof |
US4382909A (en) * | 1980-03-13 | 1983-05-10 | Degussa Aktiengesellschaft | Gold free alloys for firing on ceramic compositions |
US4397634A (en) * | 1979-06-20 | 1983-08-09 | Biggs Anthony J | Surgical pins and method |
EP0194392A1 (en) * | 1985-03-13 | 1986-09-17 | General Electric Company | Nickel-base superalloys especially useful as compatible protective environmental coatings for advanced superalloys |
FR2750867A1 (en) * | 1996-07-15 | 1998-01-16 | Bourrelly Georges | Cobalt-chromium based alloy for dental and orthopaedic implants |
US6103383A (en) * | 1998-01-27 | 2000-08-15 | Jeneric/Pentron Incorporated | High tungsten, silicon-aluminum dental alloy |
US20070015110A1 (en) * | 2005-05-26 | 2007-01-18 | Zimmer Dental, Inc. | Prosthetic dental device |
WO2009032766A1 (en) * | 2007-08-30 | 2009-03-12 | Zimmer Dental, Inc. | Dental implant prosthetic device with improved osseointegration and esthetic features |
US8075312B2 (en) | 2005-08-30 | 2011-12-13 | Zimmer Dental, Inc. | Dental implant with improved osseointegration features |
US8231387B2 (en) | 2008-07-02 | 2012-07-31 | Zimmer, Inc. | Porous implant with non-porous threads |
US8562348B2 (en) | 2008-07-02 | 2013-10-22 | Zimmer Dental, Inc. | Modular implant with secured porous portion |
US8562346B2 (en) | 2005-08-30 | 2013-10-22 | Zimmer Dental, Inc. | Dental implant for a jaw with reduced bone volume and improved osseointegration features |
US8602782B2 (en) | 2009-11-24 | 2013-12-10 | Zimmer Dental, Inc. | Porous implant device with improved core |
US8851891B2 (en) | 2008-11-06 | 2014-10-07 | Zimmer Dental, Inc. | Expandable bone implant |
US8899982B2 (en) | 2008-07-02 | 2014-12-02 | Zimmer Dental, Inc. | Implant with structure for securing a porous portion |
US9095396B2 (en) | 2008-07-02 | 2015-08-04 | Zimmer Dental, Inc. | Porous implant with non-porous threads |
US9149345B2 (en) | 2007-08-30 | 2015-10-06 | Zimmer Dental, Inc. | Multiple root implant |
US9707058B2 (en) | 2009-07-10 | 2017-07-18 | Zimmer Dental, Inc. | Patient-specific implants with improved osseointegration |
Families Citing this family (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE3145945A1 (en) * | 1981-11-20 | 1983-06-01 | Fried. Krupp Gmbh, 4300 Essen | USE OF A COBALT-CHROME ALLOY AS A MATERIAL FOR DENTAL PROSTHETICS " |
DE3534751A1 (en) * | 1985-09-28 | 1987-04-09 | Krupp Gmbh | METHOD FOR PRODUCING SOLVABLE DENTAL PROSTHESES AND DENTAL PROSTHETIC CONNECTING DEVICE |
DE3540323A1 (en) * | 1985-11-11 | 1987-05-14 | Wolfgang Prof Dr Ing Hohmann | Nickel-based casting material for the production of cast dental prostheses |
Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3466748A (en) * | 1967-12-15 | 1969-09-16 | Robert W Christensen | Anchor screw for dental prosthesis |
US3606615A (en) * | 1969-11-12 | 1971-09-21 | Krupp Gmbh | Tooth prostheses and surgical implants |
US3787900A (en) * | 1971-06-09 | 1974-01-29 | Univ Iowa State Res Found | Artificial bone or tooth prosthesis material |
-
1974
- 1974-05-02 US US466167A patent/US3896547A/en not_active Expired - Lifetime
-
1975
- 1975-04-04 DE DE19752514672 patent/DE2514672A1/en active Pending
- 1975-04-11 FR FR7511464A patent/FR2269322A1/fr not_active Withdrawn
- 1975-04-24 JP JP50049206A patent/JPS50147419A/ja active Pending
Patent Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3466748A (en) * | 1967-12-15 | 1969-09-16 | Robert W Christensen | Anchor screw for dental prosthesis |
US3606615A (en) * | 1969-11-12 | 1971-09-21 | Krupp Gmbh | Tooth prostheses and surgical implants |
US3787900A (en) * | 1971-06-09 | 1974-01-29 | Univ Iowa State Res Found | Artificial bone or tooth prosthesis material |
Cited By (29)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4129944A (en) * | 1975-02-03 | 1978-12-19 | Johnson & Johnson | Dental constructions and dental alloys |
US4145764A (en) * | 1975-07-23 | 1979-03-27 | Sumitomo Chemical Co., Ltd. | Endosseous implants |
US4126924A (en) * | 1977-02-07 | 1978-11-28 | General Atomic Company | Socket and joint prostheses |
US4397634A (en) * | 1979-06-20 | 1983-08-09 | Biggs Anthony J | Surgical pins and method |
US4336617A (en) * | 1980-01-21 | 1982-06-29 | Shin-Etsu Chemical Company Limited | Prosthetic substituted member for living body and a method for the surgical treatment by use thereof |
US4382909A (en) * | 1980-03-13 | 1983-05-10 | Degussa Aktiengesellschaft | Gold free alloys for firing on ceramic compositions |
EP0194392A1 (en) * | 1985-03-13 | 1986-09-17 | General Electric Company | Nickel-base superalloys especially useful as compatible protective environmental coatings for advanced superalloys |
FR2750867A1 (en) * | 1996-07-15 | 1998-01-16 | Bourrelly Georges | Cobalt-chromium based alloy for dental and orthopaedic implants |
US6103383A (en) * | 1998-01-27 | 2000-08-15 | Jeneric/Pentron Incorporated | High tungsten, silicon-aluminum dental alloy |
US20070015110A1 (en) * | 2005-05-26 | 2007-01-18 | Zimmer Dental, Inc. | Prosthetic dental device |
US8814567B2 (en) | 2005-05-26 | 2014-08-26 | Zimmer Dental, Inc. | Dental implant prosthetic device with improved osseointegration and esthetic features |
US8562346B2 (en) | 2005-08-30 | 2013-10-22 | Zimmer Dental, Inc. | Dental implant for a jaw with reduced bone volume and improved osseointegration features |
US8899981B2 (en) | 2005-08-30 | 2014-12-02 | Zimmer Dental, Inc. | Dental implant for a jaw with reduced bone volume and improved osseointegration features |
US10070945B2 (en) | 2005-08-30 | 2018-09-11 | Zimmer Dental, Inc. | Dental implant for a jaw with reduced bone volume and improved osseointegration features |
US8075312B2 (en) | 2005-08-30 | 2011-12-13 | Zimmer Dental, Inc. | Dental implant with improved osseointegration features |
US9149345B2 (en) | 2007-08-30 | 2015-10-06 | Zimmer Dental, Inc. | Multiple root implant |
WO2009032766A1 (en) * | 2007-08-30 | 2009-03-12 | Zimmer Dental, Inc. | Dental implant prosthetic device with improved osseointegration and esthetic features |
US9066771B2 (en) | 2008-07-02 | 2015-06-30 | Zimmer Dental, Inc. | Modular implant with secured porous portion |
US8899982B2 (en) | 2008-07-02 | 2014-12-02 | Zimmer Dental, Inc. | Implant with structure for securing a porous portion |
US8231387B2 (en) | 2008-07-02 | 2012-07-31 | Zimmer, Inc. | Porous implant with non-porous threads |
US9095396B2 (en) | 2008-07-02 | 2015-08-04 | Zimmer Dental, Inc. | Porous implant with non-porous threads |
US8562348B2 (en) | 2008-07-02 | 2013-10-22 | Zimmer Dental, Inc. | Modular implant with secured porous portion |
US8851891B2 (en) | 2008-11-06 | 2014-10-07 | Zimmer Dental, Inc. | Expandable bone implant |
US9744007B2 (en) | 2008-11-06 | 2017-08-29 | Zimmer Dental, Inc. | Expandable bone implant |
US9707058B2 (en) | 2009-07-10 | 2017-07-18 | Zimmer Dental, Inc. | Patient-specific implants with improved osseointegration |
US8602782B2 (en) | 2009-11-24 | 2013-12-10 | Zimmer Dental, Inc. | Porous implant device with improved core |
US9439738B2 (en) | 2009-11-24 | 2016-09-13 | Zimmer Dental, Inc. | Porous implant device with improved core |
US9901424B2 (en) | 2009-11-24 | 2018-02-27 | Zimmer Dental, Inc. | Porous implant device with improved core |
US10687919B2 (en) | 2009-11-24 | 2020-06-23 | Zimmer Dental, Inc. | Porous implant device with improved core |
Also Published As
Publication number | Publication date |
---|---|
DE2514672A1 (en) | 1975-11-13 |
FR2269322A1 (en) | 1975-11-28 |
JPS50147419A (en) | 1975-11-26 |
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