|Publication number||US3918100 A|
|Publication date||Nov 11, 1975|
|Filing date||May 13, 1974|
|Priority date||May 13, 1974|
|Publication number||US 3918100 A, US 3918100A, US-A-3918100, US3918100 A, US3918100A|
|Inventors||Bevil J Shaw, Richard P Miller|
|Original Assignee||Us Navy|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (8), Referenced by (58), Classifications (18)|
|External Links: USPTO, USPTO Assignment, Espacenet|
' iJnited States Patent [1 1 Shaw et :11.
[4 1 Nov. 11, 1975 1 1 SPUTTERING OF BONE ON PROSTHESES  Inventors: Bevil .1. Shaw, Murrysville; Richard P. Miller, Pittsburgh. both of Pa.
221 Filed: May 13, 1974  Appl. No.: 469.182
 U.S.Cl. v.3/1.9; 3/1.91:3/1.911; 3/1912; 3/1913; 32/10 A; 128/92 C; 128/92 G; 204/192  Int. Cl. A61F 1/00; C23C 15/00  Field of Search 204/192. 298: 3/19. 1.911. 3/1912. 1.913; 32/10 A; 128/92 C. 92 G  References Cited UNITED STATES PATENTS 2.239.642 4/194] Burkhardt ct a1 204/192 2.537.070 1/1951 Longfellow 128/92 BA 3.593.342 7/1971 Niebauer et a1. 3/1
3.605.123 9/1971 Hahn 3/1 3.609.367 10/1971 Hodosh.... 32/10 A 3.635.811 1/1972 Lane 204/192 3.789.029 1/1974 Hodosh... 260/25 R 3.790.507 2/1974 Hodosh 260/25 R Primary lirami)wr.1ohn H. Mack Ass/Mun! liraiinerAaron Weisstuch Allurney. Agent. or" FirmR. S. Sciascia; C. E. Vautrain. Jr.
 ABSTRACT A system of coating prostheses with ground bone particles is presented. Prostheses made of various metals and other substances are coated using if sputtering techniques to form a film which adheres to thedevice. stimulates living bone attachment thereto and which is ultimately replaced by new bone. Beet cattle bone material. some ground to 125 mesh and the remainder in chunks. has been successfully used in one embodiment as the coating applied by the if sputtering process.
12 Claims. N0 Drawings 1 SPUTTERING OF BONE ON PROSTHESES The present invention concerns improvements in bone replacement prostheses and, more particularly,
electrode at high energy levels for deposit on a prosthesis. Bone material from beef cattle has been successfully adhered by this method to prostheses of polished stainless steel and aluminum, and to Pyrex test tubes the sputtering of bone onto such prostheses to form a 5 and microscope slides. covering which stimulates bone growth and attachment Accordingly, it is an object of the present invention to natural bone. to provide a system for forming prostheses having a Despite recent advances in the field of prosthetic refilm which adheres to the prosthesis base and to which placement of bone, effective prosthetic replacement living bone may adhere. has not been achieved. Where total bone replacement Another object of this invention is to provide a sysis necessary, as in hip prostheses, present methods and tem for forming hip joint prostheses wherein a metallic devices are not adequate. The stresses in this area can form provides the necessary structural strength and a be very large as indicated by estimated forces of up to film of adhered bone particles provides a base for joinfour times the weight of the body and, consequently, ing the form to the living bone. the prosthesis to be inserted has to be very strong as A further object of this invention is to provide a proswell as resistant to corrosion, stress corrosion, and fathesisfor use in areas of large stresses and to which is tigue. Some advances in bone replacement in this area adhered a coating of bone particles to promote bone include the use of cobalt-chromium-molybdenum algrowth and attachment to living bone. loy, Vitallium, which has proved to be generally satis- Other objects, advantages and novel features of the factory and has an apparent advantage of case-hardeninvention will become apparent from the following deing with use. This alloy provides a structurally sound tailed description thereof. answer to the mechanical wearing problem between Bone material has been successfully deposited on mithe acetabulum, or hip-cup, and the femoral head proscroscope slides and pieces of aluminum and stainless thesis. in addition, high density polyethylene has been steel by rfsputtering. The rf sputtering process used infound to be suitable as a lubricant between these workvolved the ionized gas bombardment of an electrode to ing parts since it has a low wearing rate, is resistant to emit atoms or molecules of that electrode at high encreep, and has no toxic effects. Thus, some of the eleergy levels for deposit on a substrate. Sputtering was ments for forming a highly satisfactory metallic, prosconducted at low power densities to the target, 0.19 thesis exist. However, the overall problem is not comwatts/cm to 0.81 watts/cm to prevent thermal depletely solved since it is believed that both 316 stainless composition of the bone. Spark source mass spectrosteel and cobalt-chromium-molybdenum implants may metric analysis and X-ray analysis verify that the sputbe carcinogenic in rats. tered films have the same atomic composition as pure In addition to the suspected deficiencies in stainless bone target material. Scanning electron micrographs steel and the cobalt-chromium-molybdenum alloy, the indicate that the films are amorphous in character. Debone and pin inserts occasionally lose intimate contact tails of the procedures are now presented. due to the large forces acting on the femur around the intramedullary pin of the hip bone prosthesis. This loss EXPERIMENTS of contact leads tofailure of the prosthetic device and Bone chips obtained from steer bone were used as presents a need for a method and/or means for encourthe target, or cathode, in the sputtering system. The aging bone attachment to the implant. 4O bone was first boiled in lye to remove muscle and fatty The deficiencies associated with hip bone replacetissues and then cleaned in boiling water. Next, small ment also exist in relation to replacement of bone in rebone chips were machined for use as a powder-type tarpairing the damage sustained in such instances as gunget and then heated at 120C for 60 hours to remove shot wounds and vehicle accidents. Here there has moisture and .to outgas the target material. The dried been less success since the bone does not appear to albone chips were placed on an aluminum backing plate ways grow along the-prosthesis fillingthe gap-This efand held by an aluminum oxide retaining ring, the tarfect may be due to the prosthesis itself, but could also get size being 12.2 cm dia X 0.4 cm height. Further outbe due to thetraumatized tissue in the injured area. gassing was accomplished by pumping under high vac- This kind of woundis of particular concern to the uum for approximately 15 hours, and the target was armed services. Necrosis, i.e. failure of bone to grow presputtered for a minimum of 40 minutes at 1.63 and unite around the break therein, is'not uncommon watts/cm? in these accidents. The present invention provides a The substrates used for bone deposition were either method whereby bone may be deposited on any prosactual implant materials such as 316 L stainless steel, thesis and, by virtue of the presence of the deposited impervious A1 0 porous A1 0 and a composite porbone, living bone is encouraged to grow around the ous-impervious A1 0 or glass microscope slides for prosthetic implant and to reunite about the implant. rate determination runs, procedure limitation experi- According to the present invention, prostheses may ments and thickness measurements. All substrates were be formed by coating metallic substrates'with bone parcleaned with methyl alcohol and air dried in an enviticles by means of rf sputtering in a vacuum. One rf ronmental hood prior to insertion into the vacuum sputtering process may be that of ionized inert gas chamber. bombardment of an electrode to emit atoms of the Sputtering parameters were as follows:
Most of the runs were left under a Pump Down:
high vacuum overnight (-15 hours) to remove moisture and outgas the target. Some low power level runs could be sufficiently outgassed in as little as three hours.
-continued Blank Off Pressure:
Argon Flow Rate: 45 cc/min of gettered argon Cathode-Anode Distance: -2 inches Presputter: 40 minutes at 1.63 watts/cm Substrate Temperatures: 210C at 1.08 watts/cm 375C at 3.26 watts/cm Sputtering Run Times: l-ll hours Procedure Limitations:
The upper power level was determined by the temperature limitation of the rubber hoot gaskets and O-ring used as vacuum seals on the sputtering chamber. [f the target material is sufficiently outgassed. the bone target may be run at power densities exceeding 3.85 watts/cm provided the vacuum system has metal seals.
water-cooled chamber. and end plates.
The color of the sputtered films obtained from the experiments ranged from a transparent light brown on glass and stainless steel, and beige, to almost black on A1 The films on A1 0 tended to be darker in color as thickness increased.
All of the sputtered coatings exhibited excellent adherence to each of the substrate materials. All samples passed the Scotch tape adherence test performed by ripping a piece of pressed-on Scotch tape from the coated substrate. The films could hardly be removed by scraping with a knife.
Sputtering rates and corresponding. substrate temperatures were determined for rf power input to the target ranging from 1.08 watts/cm to 3.26 watts/cm Deposition rates were determined on masked glass substrates in a four hour sputtering run. Film thickness was measured on a Rank, Taylor, Hobson Tallystep 1 machine and deposition temperatures were monitored usinga PT/PT RH thermocouple located in good thermal.
contact on the substrate holder. Deposition rates ranged from 375A/hr at 1.08 watts/cm to 2370A/hr at 3.26 watts/cm? Substrate temperatures ranged from 210C at 1.08 watts/cm to 375C at 3.26 watts/cm? Specular reflectance analysis and transmission spectrums were performed on coated glass, stainless steel, and A1 0 substrates. Although no definite identification of the coatings on the glass substrates could be made at power densities up to 3.85 watts/cm the films sputtered onto A1 0 and stainless steel at power densi ties up to 1.63 watts/cm were shown by spectrographic analysis to have the same molecular composition as the original bone material. In addition, it was shown that material taken from the target was identical to the original bone.
The following materials were covered with bone for in vivo evaluation.
1. Impervious A1 0 2. Porous A1 0 3. A1 0 composite having an impervious inner core and a porous skin.
The substrates were cleaned in methyl alcohol and air dried in an environmental hood. They were then mounted, i.e. wire held, on a substrate holder along 1.0 X 10" mm Hg to 6,5 X10 mm Hg (as measured on a Bayard-Alpert Type 3.4 X 10" mm Hg (as measured with a with a sample for analysis, a masked glass slidefor thickness measurements, and a PT/PT 10% RH thermocouple. The specimens were coated on two side, re-- quiring two runs. The sputtering power density was 2.17 watts/cm and deposition temperatures were 374C and 362C. Resulting film thickness were 8500A and 9000A, i.e. an average deposition rate of l250A/hr- Although the results do not conclusively show that the material transferred on sputtering is identical to actual bone, spectrographic analysis shows that the chemical composition is virtually identical to the original bone, and other analysis shows that the same molecular bondingis present. The primary difference between the two is that the sputtered material is amorphous as opposed to the original crystalline structure.
Films applied by the system of the present invention.
have been subjected to spark source mass spectrometric analysis and scanning electron microscope analysis with X-ray analysis. Results of the spark source mass.
spectrometric analysis indicate that not only are the major components of the film the same as original bone, but also some characteristic lines of the structure are reproduced in the spectra of the deposit.
There isthus provided a system for coating prosthetic devices with material which will enhance healing at a 1 bone implant as well as promote bone growth and attachment to the implant. Prosthetic devices made according to the present invention are structurally capable of withstanding even the very large forces which act on the femur in hip bone replacement. In constrast with prior methods and devices, prostheses may now be coated with a bone substance which has been found to adhere to structural forms by impingement through the rf sputtering process. Such a coating formed in such a manner assures that virtually any shape of the strut tural form will receive a uniform coating over its entire surface. Where necessary, the structural form or prosthesis may be rotated during the sputtering process to assure uniform distribution of bone particles over the entire exterior surface of the prosthesis.
The present invention demonstrates that bone particles as well as phosphosilicate glass, dielectric material,
etc. may be if sputtered on a target. Not only may such a natural substance be deposited on a target, but under proper conditions of temperature and voltage the bone particles may be made to impinge upon and adhere to the target. The prostheses particularly adapted to the present system are ones which require substantial strength such as those for use in hip joint repair. However, the bone material may be made to adhere on forms having less strength, i.e. those made of sub stances such as metallic ceramics, glass and similar materials.
This adaptability of bone particles to adhere to metal surfaces leads to the formation of prosthetic devices in which the coating performs two important functions, one being that of covering the metallic base with a medium that is both non-toxic and will also induce bone growth, and the other being to provide a coating of a natural bone material. Even though this bone material coating is a foreign substance, it should not be rejected by the body in which the device is implanted since ivory which is also a foreign body is not rejected and, in fact, has been used successfully as an implant. Sputtered bone, therefore, when implanted in a human should behave the same as ivory implants have, i.e. be adaptable to being built upon by bone formed by body processes.
It has been determined that a coating thickness of substantially 1 micron is preferable to induce new bone growth and enhance the healing of a simple fracture or other bone damage. Such a thickness is also compatible with the present procedure for impinging bone particles on a metallic prosthesis in that appreciably thicker coatings tend to crack and break off when the prosthesis cools down. That is, the metallic prosthesis is raised to temperatures on the order of 350C to 400C by the impinging particles. In cooling down thereafter, a metallic substrate contracts more than the bone coating and partial separation can occur if the coating is too thick.
Sputtered-bone-coated prostheses made according to the present invention first induce living bone to grow on the implant and then to absorb and replace the implant coating over an extended period of time. This bone replacement process occurs on a non-toxic substrate or structural material which is implicitly in contact with the bone part of the body. The new bone growth promoted by the sputtered bone coating also results in the elimination of secondary grafting operations wherein bone is removed from the host and reintroduced in the area where bone is missing, e.g. in gunshot wounds. Two important areas for strengthening by prostheses coated according to the present invention thus are along the intramedullary pin of a hip-prostheses and in and around prostheses used for bone replacement in gunshot wounds where necrosis is particularly prevalent.
Obviously many modifications and variations of the present invention are possible in the light of the above teachings.
What is claimed is:
l. A prosthesis for use as a bone implant comprising:
to be replaced; and a coating of bone material impinged upon and adhered to said prosthesis by rf sputtering,
whereby said bone material will induce living bone growth around the implant and. additionally, will eliminate the necessity for bone grafting.
2. The prosthesis as defined in claim 1 wherein the material of said metallic base is selected from the nontoxic group consisting of stainless steel, cobalt-chromium-molybdenum alloy, titanium and titanium alloys and said coating is formed by an rf sputtering process.
3. The prosthesis as defined in claim 2 wherein the bone implant is presputtered for substantially 40 minutes at a power density on the order of 1.63 watts per cm 4. The prosthesis as defined in claim 3 wherein sputtering is conducted at power densities to the target in the range of from 0.19 watts per cm to 0.81 watts per cm to avoid thermal decomposition of the bone particles.
5. The prosthesis as defined in claim 4 wherein said bone material forming said coating is animal bone ground in part to a 125 mesh and in part in pieces of substantially greater size,
said bone material baked at substantially 125C for substantially 18 hours prior to presputtering to evaporate moisture from the bone,
said coating having a thickness of substantially 1 micron.
6. A method of forming a bone replacement or bone repair prosthesis comprising adhering bone particles to a prosthetic form by rf sputtering.
7. The method of claim 6 wherein the prosthetic form is positioned at the cathode of the rf sputtering means at a distance of substantially 2 inches from the anode thereof.
8. The method of claim 7 wherein the sputtering is conducted at power densities to the target in the range of from 0.19 watts per cm to 0.81 watts per cm to avoid thermal decomposition of the bone particles.
9. The method of claim 8 wherein the prosthetic form is presputtered for substantially 40 minutes at a power density of substantially 1.63 watts per cm 10. The method of claim 9 wherein sputtering is performed at an operating pressure of substantially 3.5 X 10 mm Hg and said bone particles are applied to a coating thickness of substantially 1 micron.
11. The method of claim 10 wherein the bone particles are derived from ground animal bone having a consistency in part of substantially 125 mesh and in part of substantially larger pieces,
said bone particles baked at substantially 125C for substantially 18 hours to evaporate moisture therefrom.
12. The method of claim 10 wherein the bone particles are obtained by machining bone chips to a powder form and heating the powder to substantially C for substantially 60 hours to remove moisture and gases therefrom.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US2239642 *||May 21, 1937||Apr 22, 1941||Bernhard Berghaus||Coating of articles by means of cathode disintegration|
|US2537070 *||Dec 27, 1948||Jan 9, 1951||Puy Mfg Company Inc De||Surgical appliance and method for fixation of bone fragments|
|US3593342 *||Jan 27, 1969||Jul 20, 1971||Cutter Lab||Prosthetic joint|
|US3605123 *||Apr 29, 1969||Sep 20, 1971||Melpar Inc||Bone implant|
|US3609867 *||Mar 10, 1969||Oct 5, 1971||Research Corp||Plastic bone composition|
|US3635811 *||Nov 6, 1967||Jan 18, 1972||Warner Lambert Co||Method of applying a coating|
|US3789029 *||Oct 4, 1971||Jan 29, 1974||Research Corp||Plastic bone composition and method of making same|
|US3790507 *||Jul 6, 1970||Feb 5, 1974||Research Corp||Plastic bone composition|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US4146936 *||Dec 29, 1976||Apr 3, 1979||Sumitomo Chemical Company Limited||Implants for bones, joints and tooth roots|
|US4186486 *||Nov 4, 1977||Feb 5, 1980||Maurice Gordon||Dental prosthesis|
|US4202055 *||May 12, 1977||May 13, 1980||Battelle-Institut E.V.||Anchorage for highly stressed endoprostheses|
|US4259072 *||Jul 25, 1979||Mar 31, 1981||Kyoto Ceramic Co., Ltd.||Ceramic endosseous implant|
|US4291013 *||Oct 9, 1979||Sep 22, 1981||Merck Patent Gesellschaft Mit Beschrankter Haftung||Medicinally useful, shaped mass of collagen resorbable in the body|
|US4322398 *||Feb 21, 1979||Mar 30, 1982||Battelle Institut E.V.||Implantable drug depot and process for the production thereof|
|US4338926 *||Nov 21, 1980||Jul 13, 1982||Howmedica, Inc.||Bone fracture prosthesis with controlled stiffness|
|US4347234 *||Jun 15, 1981||Aug 31, 1982||Merck Patent Gesellschaft Mit Beschrankter Haftung||Medicinally useful, shaped mass of collagen resorbable in the body|
|US4366183 *||Jun 10, 1981||Dec 28, 1982||Societe Europeene De Propulsion||Process for making bioactive coatings on osseous prostheses, and prostheses thus obtained|
|US4521192 *||Jul 21, 1983||Jun 4, 1985||Linkow Leonard I||Oral implant for oversized dental support openings|
|US4596574 *||May 14, 1984||Jun 24, 1986||The Regents Of The University Of California||Biodegradable porous ceramic delivery system for bone morphogenetic protein|
|US4743229 *||Sep 29, 1986||May 10, 1988||Collagen Corporation||Collagen/mineral mixing device and method|
|US4789663 *||Jul 5, 1985||Dec 6, 1988||Collagen Corporation||Methods of bone repair using collagen|
|US4908030 *||Apr 29, 1987||Mar 13, 1990||Vent-Plant Corporation, Inc.||Method of manufacturing synthetic bone coated surgical implants|
|US5015256 *||Mar 30, 1988||May 14, 1991||Ab Idea||Method and means for fixing a joint prosthesis|
|US5035711 *||Sep 5, 1990||Jul 30, 1991||Kabushiki Kaisya Advance Kaihatsu Kenkyujo||Transcutaneously implantable element|
|US5061286 *||Aug 18, 1989||Oct 29, 1991||Osteotech, Inc.||Osteoprosthetic implant|
|US5108436 *||Nov 23, 1988||Apr 28, 1992||Collagen Corporation||Implant fixation|
|US5143730 *||Jul 25, 1989||Sep 1, 1992||Henkel Kommanditgesellschaft Auf Aktien||Resorbable bone wax|
|US5217496 *||Sep 30, 1992||Jun 8, 1993||Ab Idea||Implant and method of making it|
|US5258029 *||May 23, 1990||Nov 2, 1993||Collagen Corporation||Method for improving implant fixation|
|US5697932 *||Nov 9, 1994||Dec 16, 1997||Osteonics Corp.||Bone graft delivery system and method|
|US6045555 *||Dec 10, 1997||Apr 4, 2000||Osteonics Corp.||Bone graft delivery system and method|
|US6142998 *||Jan 3, 2000||Nov 7, 2000||Howmedica Osteonics Corp.||Bone graft delivery surgical instruments|
|US6296645||Apr 9, 1999||Oct 2, 2001||Depuy Orthopaedics, Inc.||Intramedullary nail with non-metal spacers|
|US6309395||Apr 25, 2000||Oct 30, 2001||Howmedica Osteonics Corp.||Bone graft delivery surgical instruments|
|US6371988||Jan 18, 2000||Apr 16, 2002||Sdgi Holdings, Inc.||Bone grafts|
|US6379385||Jan 6, 2000||Apr 30, 2002||Tutogen Medical Gmbh||Implant of bone matter|
|US6709436||May 22, 2000||Mar 23, 2004||Depuy Orthopaedics, Inc.||Non-metal spacers for intramedullary nail|
|US6783529||Oct 19, 2001||Aug 31, 2004||Depuy Orthopaedics, Inc.||Non-metal inserts for bone support assembly|
|US6786908||Aug 2, 2001||Sep 7, 2004||Depuy Orthopaedics, Inc.||Bone fracture support implant with non-metal spacers|
|US6808527||Mar 25, 2002||Oct 26, 2004||Depuy Orthopaedics, Inc.||Intramedullary nail with snap-in window insert|
|US7276081||Nov 23, 1999||Oct 2, 2007||Warsaw Orthopedic, Inc.||Bone grafts|
|US7410488||Feb 18, 2005||Aug 12, 2008||Smith & Nephew, Inc.||Hindfoot nail|
|US7655009||Nov 30, 2004||Feb 2, 2010||Smith & Nephew, Inc.||Humeral nail|
|US7892261||Jan 13, 2004||Feb 22, 2011||P Tech, Llc||Spinal implant and methods for changing spatial relationships between vertebrae|
|US7981156||Feb 18, 2004||Jul 19, 2011||Warsaw Orthopedic, Inc.||Bone grafts|
|US8486066 *||May 15, 2003||Jul 16, 2013||Bonutti Skeletal Innovations Llc||Spacer|
|US8795363||Mar 19, 2013||Aug 5, 2014||Bonutti Skeletal Innovations Llc||Wedge apparatus for use in operating on a bone|
|US8956417||Jan 18, 2013||Feb 17, 2015||Bonutti Skeletal Innovations Llc||Joint spacer|
|US9044322||Jul 29, 2014||Jun 2, 2015||Bonutti Skeletal Innovations Llc||Method and apparatus for use in operating on a bone|
|US9044341||Jan 13, 2004||Jun 2, 2015||Bonutti Skeletal Innovations Llc||Joint spacer|
|US9050152||Dec 17, 2014||Jun 9, 2015||Bonutti Skeletal Innovations Llc||Method and apparatus for use in operating on a bone|
|US20040153072 *||Jan 13, 2004||Aug 5, 2004||Bonutti Peter M.||Spinal spacer|
|US20040254582 *||Jan 13, 2004||Dec 16, 2004||Bonutti Peter M.||Joint spacer|
|US20050004672 *||Feb 18, 2004||Jan 6, 2005||John Pafford||Bone grafts|
|US20050098237 *||Nov 10, 2003||May 12, 2005||Medlin Dana J.||Case hardened orthopedic implant|
|USRE44501||Aug 12, 2010||Sep 17, 2013||Smith & Nephew, Inc.||Hindfoot nail|
|DE2620907A1 *||May 12, 1976||Nov 17, 1977||Battelle Institut E V||Verankerung fuer hochbelastete endoprothesen|
|DE3447583A1 *||Dec 28, 1984||Jul 10, 1986||Battelle Institut E V||Verfahren zur herstellung implantierbarer knochenersatzwerkstoffe|
|EP0022724A1 *||Jul 11, 1980||Jan 21, 1981||ANVAR Agence Nationale de Valorisation de la Recherche||Biodegradable implant, usable as bone prosthesis|
|EP0130916A1 *||Jun 29, 1984||Jan 9, 1985||SOCIETE EUROPEENNE DE PROPULSION (S.E.P.) Société Anonyme dite:||Method of producing bioactive calcium phosphate deposits, and products so obtained|
|EP0149425A1 *||Dec 14, 1984||Jul 24, 1985||Mathys Co Robert||Glenoid cavity made of plastics|
|EP0470305A1 *||Aug 7, 1990||Feb 12, 1992||Osteotech, Inc.,||Osteoprosthetic implant|
|EP0501595A1 *||Mar 30, 1988||Sep 2, 1992||Ab Idea||Method and means for fixing a joint prosthesis|
|EP0688194A1 *||Jan 12, 1994||Dec 27, 1995||Etex Corporation||Methods of coating implants with bony structure|
|WO1988007355A1 *||Mar 30, 1988||Oct 6, 1988||Idea Ab||Method and means for fixing a joint prosthesis|
|WO1989012472A1 *||Jun 13, 1989||Dec 28, 1989||Idea Ab||Implant and method of making it|
|U.S. Classification||128/898, 623/923, 606/76, 204/192.15|
|International Classification||A61L27/36, A61F2/30, A61F2/00|
|Cooperative Classification||Y10S623/923, A61F2310/00023, A61F2310/00029, A61F2310/00958, A61F2310/00017, A61L27/3608, A61L27/365, A61F2/30767|
|European Classification||A61L27/36B2, A61L27/36F2B, A61F2/30L|