|Número de publicación||US3868730 A|
|Tipo de publicación||Concesión|
|Fecha de publicación||4 Mar 1975|
|Fecha de presentación||6 Feb 1974|
|Fecha de prioridad||24 Sep 1973|
|Número de publicación||US 3868730 A, US 3868730A, US-A-3868730, US3868730 A, US3868730A|
|Inventores||Kaufer Herbert, Matthews Larry S, Murray Ian P, Sonstegard David A|
|Exportar cita||BiBTeX, EndNote, RefMan|
|Citas de patentes (5), Citada por (94), Clasificaciones (4)|
|Enlaces externos: USPTO, Cesión de USPTO, Espacenet|
United States Patent 1 1 Kaufer et a1.
Mar. 4, 1975 KNEE OR ELBOW PROSTl-IESIS  Assignee: Howmedica, Inc., New York, NY.
 Filed: Feb. 6, 1974  Appl. No.: 440,190
Related U.S. Application Data  Continuation-impart of Ser. No. 400,202. Sept. 24.
 U.S. Cl. 3/1, 128/92 C  Int. Cl. A611 1/24  Field of Search..... 3/1; 128/92 C, 92 CA. 92 R  References Cited UNITED STATES PATENTS 3.638.243 2/1972 Campbell et al 3/1 3.694.821 10/1972 Moritz 3/1 1728.742 4/1973 Averill et al...... 3/1 3760.427 9/1973 Schultz 3/1 1774.244 11/1973 Walker 3/1 FOREIGN PATENTS OR APPLICATIONS 1047.640 7/1953 France 128/92 C 1.215.737 12/1970 Great Britain 128/92 C  ABSTRACT The femoral and tibial components of a knee joint prosthesis are rotatably coupled by a ball and socket connection in which a ball on a connecting rod extending upwardly from the tibial component is engaged up into a high density polyethylene socket insert in the bottom of the femoral component. A pair of spaced substantially parallel spheroidally curved condyle runners straddle the socket opening in the femoral component and have a compound curvature with a larger radius lower portion and a smaller radius upper portion. A slot in the ball retaining socket insert permits the required angular movement of the connecting rod through the angle of flexure, and the connecting rod engages the terminal end of the slot to limit the flexure. The upper edges of the condyle runners are thickened to cause the leading edges of the polyethylene plateau shoes on the tibial component to firmly wedge into them to smoothly arrest flexed tibial movement. The slot is larger than the connecting rod thereby enabling flexure movement. and noninterference with natural rotational and wobbling movement as in a natural knee joint. The concave plateaus substantially correspond with the lower larger radius condyle surfaces to intimately engage them with each other in the extended position for firm extended leg support. The clearance between the plateau and condyle surfaces during flexure is small enough to cause them to interfere after only a slight degree of twisting or wobbling is permitted. This clearance and the associated control of medial and lateral angulation and medial and lateral rotation is maintained by the precise controlled entrapment of the ball in the socket.
15 Claims, 12 Drawing Figures 1 KNEE on ELBOW PRQSTHESIS CROSS-REFERENCE TO RELATED APPLICATION This application is a continuatio'n-in-part of copending application Ser. No. 400,202 filed Sept. 24, 1973, now abandoned.
BACKGROUND OF THE INVENTION concave plateau elements, which more exactly copies natural knee or elbowjointmovement and provides a very high degree of intrinsic stability.
SUMMARY The femoral and tibial components of a knee joint prosthesis are rotatably coupled by a ball and socket connection in which a ball on a connecting rod extending upwardly from the tibial component is engaged up into a socket in the bottom of the femoral component. A pair of spaced substantiallyv parallel spheroidally curved condyle runners straddle the socket opening in the femoral component and have a varying curvature with a larger radius lower portion and a small radius upper portion. A slot in the ball retaining socket insert permits the required angular movement of the connecting rod through the angle of flexure, and the connecting rod engages the terminal end of the slot to limit the flexure. The upperedges of the condyle runners are thickened to cause the leading edges of the polyethylene plateau shoes in the-tibial component to firmly wedge against them to smoothly arrest flexed tibial movement. The slot is larger than the connecting rod to enable a degree of play throughout the flexure movement, thus providing an unencumbered natural rota tional and wobbling movement. The precise geometry of the entrapped ball associated with the controlled clearance and fit between the runners and plateaus or shoes provides intrinsic stability and simulates the natural rotational and wobbling movement of a natural knee joint. The concave plateaus substantially correspo'nd with the lower larger radius condyle surfaces to intimately engage them with each other in the extended position for firm extended leg support. The clearance between the plateau and condyle surfaces during flexure is small enough to cause them to interfere after only a controlled degree of twisting or wobbling is permitted. The socket and sliding shoe surfaces may be effectively provided by organic polymer inserts, suitably composed of high molecular weight polyolefin, e.g, high density polyethylene. The socket insert may be segmented and rotationally locked within the socket cavity in the femoral component to facilitate its replacement and to assure assembled stability.
BRIEF DESCRIPTION OF THE DRAWING Novel features and advantages of the present invention will become apparent to one skilled in the art from a reading'of the following description in conjunction with the accompanying drawings wherein similar reference characters refer to similar parts and in which:
FIG. 1 is a side view in elevation of an embodiment of this invention serving as the knee joint between a femur and tibia, which are shown in phantom outline;
FIG. 2 is a left elevational view of the embodiment shown in FIG. 1 showing the rear of the knee joint;
FIG. 3 is a right elevational view of the embodiment shown in FIG. 1 showing the front of the knee joint;
FIG. 4 isa side elevational view of the embodiment shown in FIG. 1 with the knee joint flexed in the sitting position;
FIG. 5 is an enlarged full-size cross-sectional view taken through FIG.'2, along the line 55;
FIG. 6 is an enlarged full size cross-sectional view taken through FIG. 2 along the line 66;
FIG. 7 is a full size rear view in elevation of the tibial component of the embodiment shown in FIGS. l-5 with the ball of the connecting rod disposed within the plastic socket of the femoral component, which is partly broken away in cross section;
FIG. 8 is an outside view in elevation of the rear portion of the segmented plastic socket;
FIG. 9 is an outside view in elevation of the front portion of the segmented plastic socket;
FIG. 10 is a bottom plan view of the tibial portion of the embodiment shown in FIGS. l-9;
FIG. 11 is a top plan view of the wrench for installing and removing the socket shown in FIGS. 7-9; and
FIG. 12 is a side view in elevation of the wrench shown in FIG. 11.
DESCRIPTION OF THE PREFERRED EMBODIMENT ln FIGS. 1-3 and 5 is shown a knee joint prosthesis 10 in the extended and in the partially flexed positions, respectively, in which the upper and lower portions of the leg represented by femur l2 and tibia 14 are in anatomical alignment with each other. Joint 10 includes a femoral component 16 and a tibial component 18 coupled by ball and socket connection 20. Femoral component 16 has a pair of spaced substantially parallel spheroidally curved condyle runners 22 straddling a hollow central housing 24.
Condyle runners 22 each have a front lower portion 26 having a relatively larger radius of curvature and a rear upper portion 28 having a relatively smaller radius portion. The radius of curvature of front lower portion 26 is, for example, twice as large as the radius of curvature of rear upper portion 28. Femoral attaching stem 30 is attached to the top of hollow central housing 24 and is substantially of square cross-section with slight lateral depressions 32 in each of the sides for facilitating cementing and retention in the femur.
Ball and socket connection 20 in hollow housing 24 includes spherical ball 34 entrapped within segmented plastic socket 36 including front half 36A and rear half 36B, later described in detail. Socket 36 is suitably made of high molecular weight polymer such as high density polyethylene. All other portions of knee joint 10 are made of a strong non-corrosive metal having stable expansion and other physical characteristics. with the exception of shoes 38 which are also made of high molecular weight polymer such as high density polyethylene. The metal portions are advantageously made of metal compatible with the human body such as Vitallium, the trademark of Howmedica Inc. for a cobaltchromium alloy, developed and used for east partial and full dentures, andfor internal application by surgeons. When polished, it is exceedingly smooth and permanently lustrous. Its outstanding qualities are permanent inertness in relation to living tissues, and high resistance to corrosion.
Condyle runners 22 correspond to the condyle portions of a human knee joint and also have a transverse radius of curvature shown in FIG. 3 to make their sur faces substantially spheroidal. Transverse radius of curvature 40 shown in FIG. 3 is preferably substantially equal to the smaller radius of curvature of condyle runner upper rear portions 28.
Shoes 38 shown in FIG. correspond to the plateau portions of the human knee and have a concave surface 42 shown in FIG. 5, which substantially correspond to the shape of lower condyle runner portions 26 to cause these portions to intimately nest with each other in the extended position shown in FIG. 1 and provide firm support for the extended leg shoes 38 have substantially the same transverse radius as curvature 40 shown in FIG. 3. This geometry helps provide the aforementioned stable nesting in the extended position, and provides an interference control of the rotation and wob bling movements facilitated by the ball 34 and socket 36.
Ball 34 is disposed on the top of connecting rod 44, which is mounted on the top of base 46 of tibial component 18. A regularly gouged tibial connecting stem 48 extends downwardly into tibia 14 from the bottom of base 46. Shoes 38 are mounted in recesses 50 in the upper surface of base 46.
FIG. 4 shows the position of joint when femoral component 16 is rotated to a horizontal position, such as when a person is in the sitting position. This engages the upper rear portions 28 of condyle runners 22 with shoes 38. The flexure motion is smoothly arrested by an outward protrusion or slight thickening of the terminal ends 52 of upper rear condyle portions 28 which wedge against the rear ends of shoes 38. This smoothly arrests the flexure movement without any clunking and simulates the normal knee action. The flexure movement of joint 10 is also arrested by the abutment of connecting rod 44 against the rear edge 64 of rear socket portion 368.
The extending movement ofjoint 10 about axis 56 of ball and socket joint 20 is arrested by the nesting of lower larger radius of curvature portions 26 of condyle runners 22 within shoes 38. Smaller radius of curvature condyle portions 28 have a coaxial axis of rotation with ball center 56 in the position shown in FIG. 5. This causes the larger radius of curvature condyle runner portions 26 to firmly engage into the concave surfaces 42 within shoes 38 and thus provide secure abutment and firm support for each other. During movement of joint 10 from the extended position shown in FIG. 1 to the flexed position shown in FIG. 4 through intermediate position 5, smaller radius of curvature portions 28 of condyle runners 22 move slightly free of internal shoe surfaces 42 which thus allows a light wobbling or controlled play within the confines of shoes 38 until the bottoms of condyle runners 22 engage the outer edges 58 of shoes 38 which limit such movement. This simulates the normal rotational inward and outward tilting or wobbling of a normal knee joint throughout the flexed positions and with more restraint in the extended position.
FIGS. 7-10 show the manner in which segmented plastic insert halves 36A and 36B are disposed about ball 34 and inserted within cavity 60 in hollow central housing 24. Rear insert portion 368 has a slot 62 having a relatively lower outer dome 64 relative to higher outer dome 66 of slot 68 in front socket segment 36A. This provides for movement from the extended position shown in FIG. 1 to the flexed position shown in FIg. 4 and accordingly provides the necessary clearance for the relative angular movement of connecting rod 44. Connecting rod 44 is narrower than the width of slots 62 and 68 to insure non-interference with the play or wobbling action throughout the flexed orientation of knee joint 10.
FIG..10 shows the bottom surface 70 of tibial base 46 serrated by spherical pits 72, which help cement base 46 to tibia 14.
FIGS. 11 and 12 show wrench 74 having stem 76 connected to arcuate rod 78 upon which pins 80 are mounted. Pins 80 are inserted into holes 82 in the bottom edges 85 and 86 of rear and front socket segments 36B and 36A for rotating the segments about ball 34, for insertion into and removal from cavity 60 as shown in FIG. 6. Assembled socket segments 36A and B are accordingly inserted into cavity 60 in the position 'shown in FIG. 6 in which flat edge 84 of rear segment 36B clears overhanging edge 87 of cavity 60. After such insertion, rotation of segments 36A and B in the direction of arrow 88 locks the outer circumference 89 of socket segments 36A and B under overhanging edge 87 to lock the segments in place. The locked position is indexed and stabilized by the rotation of indentation 90 in front segment 36A into alignment with detent projection 92 on the wall of cavity 60. Reverse rotation back to the position shown in FIG. 6 allows removal of ball and socket insert 20 from cavity 60.
Knee joint 10 has thefollowing advantages:
1. Ease of surgery: A medical parapatellar incision allows exposure for a single transverse saw cut across the tibia approximately /z cm. below the joint surface. The angled transverse saw cuts across the femur are then made. The medullary spaces are broached. Bone cement is placed in the'femoral broached space and across the osteotomy site. The femoral component is inserted. The tibial component is similarly installed. The knee is flexed, the ball and socket insert snapped into place, the knee extended, and the wound closed.
2-3. Versatility Inherent Stability: Knee joint 10 is an inherently stable prosthesis which enables treatment of joints lacking viable capsules and ligaments in addition to pathologic articular surfaces. both condylar and patellar. Few sizes are needed (three are foreseen).
4. Range of Motion: Design of runner-insert geometrics enables the motion characteristics desired. Flexion-extension from -5 to is readily accomplished. valgusrvarus and rotational freedom is attained by the sloppy though carefully controlled interplay between runners and inserts. Runner-insert track sidewall camming action yields a non-impact but secure arrest of motion.
5. Controlled Decceleration: The camming action arrestment prevents clunk impact loadings at full extension (FIG. 1) and full flexion (FlG. 4).
6. Materials: All components are made of medically accepted metal and high density polyethylene.
7. Load Bearing Areas: The runner-track bearing areas are as large as currently available partial knee configurations. The ball-socket area is a significant additional increase in bearing surface.
8. Prosthesis-Bone Interface: Only metal-cementbone interfaces are used.
9. Replacement of Failed Components: The parts susceptible to wear (two tibial inserts and one socket insert) are readily replaced.
l0. Shear Forces: High density polyethylene is not in contact with cement. Low frictional characteristics of high density polyethylene polished metal bearing surfaces minimize shear forces on both components.
ll. Salvage Possibilities: A knee joint compression arthrodesis is possible as a salvage procedure.
12. In addition to the above, knee joint looks like a knee to surgeon and patient alike, and its functional characteristics are similar to those of the normal knee.
1 A joint prosthesis suitable for a knee or elbow comprising a femoral component, a tibial component, a ball and socket connection coupling said components, said femoral component having a pair of spaced substantially parallel spherodically curved condyle runners straddling a hollow central housing, said condyle runners having a front lower portion with a relatively larger radius of curvature joining a rear upper portion having a relatively smaller radius of curvature as compared to said front lower portion, a slot in the bottom of said housing disposed substantially parallel to said runners, a femoral attaching means in the top of said femoral component, said tibial component having a base, tibial connecting means on the bottom of said base, a pair of spherodially curved spaced parallel concave sliding shoes on said base having upper surfaces substantially corresponding with the front lower portions of said condyle runners for intimately nesting them together when said joint is in the extendedposition, said ball and socket connection including a connecting rod rigidly fixed to and extending upwardly from said base of said tibial component, the ball of said ball and socket connection being disposed on the upper end of said connecting rod, said hollow central housing enclosing the socket portion of said ball and socket connection disposed for entry through its bottom, said ball portion being rotatably engaged in said socket portion, the smaller radius of curvature of said rear upper portions of said runners providing clearance between said shoes and said rear upper portions in flexed posiners whereby a natural degree of controlled joint twisting and wobbling is provided.
2. A joint prosthesis as set forth in claim 1, wherein the upper ends of said rear upper portions of said runners slightly protrude radially outwardly for wedging against said shoes whereby the terminal flexure motion of said shoe is smoothly arrested.
3. A joint prosthesis as set forth in claim 1, wherein said ball and socket connection has an axis of rotation, said rear upper portions of said condyle runners having a center of curvature, and said axis of rotation and'said center of curvature being coaxial with each other.
4. A joint prosthesis as set forth in claim 1, wherein said runners have a transverse radius of curvature substantially equal to said smaller radius of curvature of said rear upper portions of said condyle runners.
5. A joint prosthesis as set forth in claim 1, wherein said concave shoes have a radius of curvature substantially corresponding to said radius of curvature of said front lower portions of said condyle runners.
6. A joint prosthesis asset forth in claim 5, wherein said concave shoes have a transverse radius of curvature substantially corresponding to the transverse radius of curvature of said runners.
7. A joint prosthesis as set forth in claim 1, wherein said tibial connecting means comprises a tibial connecting stem disposed to extend downwardly from said base. 1
8. A joint prosthesis as set forth in claim 1, wherein said femoral attaching means comprises a femoral attaching stem.
9. A joint prosthesis as set forth in claim 1, wherein said socket portion of said ball and socket connection comprises a slotted insert.
10. A joint prosthesis as set forth in claim 9, wherein said slotted insert comprises high molecular weight polymer.
11. A joint prosthesis as set forth in claim 10, wherein said shoes also comprise high molecular weight polymer.
12. A joint prosthesis as set forth in claim 11, wherein said polymer comprises high density polyethylene.
13. A joint prosthesis as set forth in claim 1, wherein said base includes shoe-containing recesses, said shoes being securely mounted in said recesses.
14. A joint prosthesis as set forth in claim 1, wherein said socket portion of said ball and socket connection comprises a segmented inse'rt, said hollow central housing having an inner cavity, said cavity having overhanging edges on portions of its mouth, said segmented insert being keyed with said overhanging edges whereby said insert may be inserted clear of said overhanging edges in one rotational orientation and interlocked with said edges in another rotational orientation.
15. A joint prosthesis as set forth in claim 14, wherein said keying is constructed and arranged to permit insertion of said insert in only one rotational orientation in said cavity and interlocked in said other rotational orientation of said insert in said cavity.
|Patente citada||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US3638243 *||4 May 1970||1 Feb 1972||Univ Ohio State||Surgically implantable prosthetic joint|
|US3694821 *||2 Nov 1970||3 Oct 1972||Moritz Walter D||Artificial skeletal joint|
|US3728742 *||18 Jun 1971||24 Abr 1973||Howmedica||Knee or elbow prosthesis|
|US3760427 *||24 Mar 1972||25 Sep 1973||Schultz R||Surgically implantable prosthetic joint|
|US3774244 *||8 Feb 1972||27 Nov 1973||Relief Ruptured And Crippled S||Knee-joint prosthesis|
|Patente citante||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US3958278 *||22 Abr 1975||25 May 1976||National Research Development Corporation||Endoprosthetic knee joint|
|US4016606 *||14 Jul 1975||12 Abr 1977||Research Corporation||Knee joint prosthesis|
|US4085466 *||4 Ago 1977||25 Abr 1978||National Research Development Corporation||Prosthetic joint device|
|US4094017 *||16 Feb 1977||13 Jun 1978||Larry Stanford Matthews||Knee joint prosthesis with patellar-femoral contact|
|US4106128 *||6 Dic 1976||15 Ago 1978||Greenwald A Seth||Endoprosthetic bone joint|
|US4131956 *||14 Feb 1977||2 Ene 1979||Richards Manufacturing Company, Inc.||Elbow prosthesis|
|US4193140 *||19 Dic 1975||18 Mar 1980||Richards Manufacturing Company, Inc.||Knee prosthesis|
|US4205400 *||4 Dic 1978||3 Jun 1980||Zimmer Usa, Inc.||Metallo-polymeric prosthesis with cavitied interconnection|
|US4209861 *||22 Feb 1978||1 Jul 1980||Howmedica, Inc.||Joint prosthesis|
|US4249270 *||1 Oct 1979||10 Feb 1981||Sulzer Brothers Limited||Endoprosthesis for a knee joint|
|US4268920 *||29 Sep 1978||26 May 1981||GMT Gesellschaft fur med. Technik mbH||Endoprosthesis for a knee joint|
|US4293963 *||14 Feb 1980||13 Oct 1981||Zimmer Usa, Inc.||Unrestrained elbow prosthesis|
|US4301553 *||23 May 1980||24 Nov 1981||United States Surgical Corporation||Prosthetic knee joint|
|US4352212 *||20 Jun 1980||5 Oct 1982||Howmedica, Inc.||Joint prosthesis|
|US4383337 *||22 Oct 1980||17 May 1983||Zimmer Usa, Inc.||Elbow prosthesis|
|US4501031 *||22 Ene 1981||26 Feb 1985||Zimmer, Inc.||Metal and plastic composite tibial component for knee joint|
|US4714473 *||25 Jul 1985||22 Dic 1987||Harrington Arthritis Research Center||Knee prosthesis|
|US4718414 *||7 Ago 1986||12 Ene 1988||Queen's University At Kingston||Instrument for elbow surface replacement arthroplasty|
|US4795468 *||23 Dic 1987||3 Ene 1989||Zimmer, Inc.||Mechanism and method for locking a bearing insert to the base of a prosthetic implant|
|US4950299 *||27 Ene 1989||21 Ago 1990||Joint Medical Products Corporation||Ball and socket bearing for artificial joint|
|US4960427 *||24 Abr 1989||2 Oct 1990||Joint Medical Products Corporation||Ball and socket bearing for artifical joint|
|US4964868 *||27 Ago 1987||23 Oct 1990||Harrington Arthritis Research Center||Knee prosthesis|
|US5133759 *||24 May 1991||28 Jul 1992||Turner Richard H||Asymmetrical femoral condye total knee arthroplasty prosthesis|
|US5139521 *||18 Ene 1991||18 Ago 1992||Ingrid Schelhas||Knee prosthesis|
|US5314484 *||19 Ene 1993||24 May 1994||Huene Donald R||Bi-axial elbow joint replacement|
|US5358529 *||5 Mar 1993||25 Oct 1994||Smith & Nephew Richards Inc.||Plastic knee femoral implants|
|US5376121 *||17 Feb 1993||27 Dic 1994||Techmedica, Inc.||Dual constraint elbow prosthesis|
|US5427586 *||20 Ago 1993||27 Jun 1995||Ingrid Schelhas||Knee-joint endoprosthesis|
|US5556432 *||9 Feb 1993||17 Sep 1996||Joachim Theusner||Artificial joint|
|US5702461 *||18 Ene 1996||30 Dic 1997||Biomedical Engineering Trust I||Prosthesis fixturing device|
|US5713901 *||9 Mar 1994||3 Feb 1998||Tock; Gideon Raphael||Reticulated orthopaedic element to exploit the medullary canal of the long bones|
|US5716361 *||2 Nov 1995||10 Feb 1998||Masini; Michael A.||Bone cutting guides for use in the implantation of prosthetic joint components|
|US5868797 *||17 Ene 1996||9 Feb 1999||Biomedical Engineering Trust I||Prosthesis fixturing device|
|US5885296 *||18 Sep 1997||23 Mar 1999||Medidea, Llc||Bone cutting guides with removable housings for use in the implantation of prosthetic joint components|
|US5897559 *||18 Sep 1997||27 Abr 1999||Medidea, Llc||Bone cutting guides for use in the implantation of prosthetic joint components|
|US5954770 *||21 Feb 1997||21 Sep 1999||Plus Endoprothetik Ag||Endoprosthetic knee joint|
|US6042611 *||18 Abr 1997||28 Mar 2000||Joint Medical Products Corporation||Ball and socket bearing for artificial joint|
|US6102955 *||16 Mar 1998||15 Ago 2000||Mendes; David||Surgical method, surgical tool and artificial implants for repairing knee joints|
|US6117175 *||29 Ago 1997||12 Sep 2000||Bosredon; Jean||Spherical knee joint prosthesis|
|US6187010||17 Sep 1997||13 Feb 2001||Medidea, Llc||Bone cutting guides for use in the implantation of prosthetic joint components|
|US6602259||27 Abr 1999||5 Ago 2003||Medidea, Llc||Bone cutting guides for use in the implantation of prosthetic joint components|
|US6629999 *||6 Mar 2000||7 Oct 2003||Louis A. Serafin, Jr.||Modular joint|
|US6869448||14 Ene 2003||22 Mar 2005||Finsbury (Development) Limited||Prosthesis|
|US7128745||2 Dic 2002||31 Oct 2006||Medidea, Llc||Joint replacement methods and apparatus|
|US7232465 *||25 Jul 2003||19 Jun 2007||Waldemar Link Gmbh & Co. Kg||Knee prosthesis|
|US7419491||15 Oct 2003||2 Sep 2008||Medidea, Llc||Bone-conserving orthopedic instrumentation and appliances|
|US7753960 *||25 Feb 2005||13 Jul 2010||Omni Life Science, Inc.||Modular knee prosthesis|
|US7842093||18 Jul 2006||30 Nov 2010||Biomet Manufacturing Corp.||Method and apparatus for a knee implant|
|US7850737||26 Jun 2007||14 Dic 2010||Mayo Foundation For Medical Education And Research||Prosthetic elbow replacement|
|US7875082 *||9 May 2008||25 Ene 2011||Remi Sciences, Inc.||Ulnar head prosthesis system|
|US7998217||2 Feb 2005||16 Ago 2011||Biomet Manufacturing Corp.||Modular offset stem implants|
|US8052755 *||29 Ene 2009||8 Nov 2011||Remi Sciences, Inc.||Ulnar head prosthesis system|
|US8277513||22 Jun 2010||2 Oct 2012||Omni Life Science, Inc.||Modular knee prosthesis|
|US8313531||28 Abr 2010||20 Nov 2012||Hip Innovation Technology Llc||Interlocking reverse hip prosthesis and method|
|US8398718||16 Feb 2011||19 Mar 2013||Rodney Ian Walter Richardson||Acetabular cup with rotatable bearing member|
|US8449620 *||5 Nov 2008||28 May 2013||Gs Development Ab||Artificial joint|
|US8465549||16 Feb 2011||18 Jun 2013||Rodney Ian Walter Richardson||Acetabular cup with rotatable bearing|
|US8540779||10 Feb 2011||24 Sep 2013||Hip Innovation Technology Llc||Product and methods for interlocking reverse hip and revision prosthesis|
|US8545571||30 Jul 2010||1 Oct 2013||Howmedica Osteonics Corp.||Stabilized knee prosthesis|
|US8840673 *||21 Sep 2012||23 Sep 2014||Linares Medical Devices, Llc||Implantable elbow joint assembly with spherical inter-support|
|US8845743||12 Oct 2012||30 Sep 2014||Hip Innovation Technology, LLC||Interlocking reverse shoulder prosthesis method|
|US8992627||22 Ago 2013||31 Mar 2015||Hip Innovation Technology Llc||Interlocking reverese hip and revision prosthesis and method|
|US9114015||7 Ago 2014||25 Ago 2015||Linares Medical Devices, Llc||Implantable elbow joint assembly with spherical inter-support|
|US9119724||22 Ago 2013||1 Sep 2015||Hip Innovation Technology Llc||Interlocking reverse hip revision prosthesis|
|US9289304||5 Oct 2013||22 Mar 2016||Robert A. Kaufmann||Prosthesis for partial and total joint replacement|
|US9452051||16 Sep 2013||27 Sep 2016||Howmedica Osteonics Corp.||Stabilized knee prosthesis|
|US9636228||11 Feb 2008||2 May 2017||Howmedica Osteonics Corp.||Radial head implant|
|US9655726 *||28 Nov 2006||23 May 2017||Mayo Foundation For Medical Research And Education||Radial-capitellar implant|
|US9765350||3 Sep 2015||19 Sep 2017||Dow Agrosciences Llc||Methods and compositions for recombination a gene-deficient strains of Agrobacterium tumefaciens|
|US20030093079 *||2 Dic 2002||15 May 2003||Masini Michael A.||Joint replacement methods and apparatus|
|US20030139817 *||14 Ene 2003||24 Jul 2003||Finsbury (Development) Limited||Prosthesis|
|US20040078042 *||15 Oct 2003||22 Abr 2004||Masini Michael A.||Bone-conserving orthopedic instrumentation and appliances|
|US20040078043 *||14 Oct 2003||22 Abr 2004||Masini Michael A.||Joint replacement methods and apparatus|
|US20050203629 *||25 Feb 2005||15 Sep 2005||George Cipolletti||Modular knee prosthesis|
|US20050246029 *||25 Jul 2003||3 Nov 2005||Waldemar Link||Knee prosthesis|
|US20060161259 *||18 Ene 2005||20 Jul 2006||Cheng-Kung Cheng||Knee joint prosthesis|
|US20070073409 *||28 Nov 2006||29 Mar 2007||Mayo Foundation For Medical Research And Education||Radial-capitellar implant|
|US20080021566 *||18 Jul 2006||24 Ene 2008||Biomet Manufacturing Corp.||Method and apparatus for a knee implant|
|US20090281631 *||9 May 2008||12 Nov 2009||Remi Sciences, Inc.||Ulnar head prosthesis system|
|US20090281632 *||29 Ene 2009||12 Nov 2009||Remi Sciences, Inc.||Ulnar head prosthesis system|
|US20090312840 *||26 Jun 2007||17 Dic 2009||Morrey Bernard F||Prosthetic elbow replacement|
|US20100256770 *||5 Nov 2008||7 Oct 2010||Gs Development Ab||Artificial joint|
|US20100262253 *||22 Jun 2010||14 Oct 2010||Omni Life Science, Inc.||Modular Knee Prosthesis|
|US20110218637 *||28 Abr 2010||8 Sep 2011||Zafer Termanini||Interlocking reverse hip prosthesis|
|US20110218638 *||10 Feb 2011||8 Sep 2011||Zafer Termanini||Interlocking Reverse Hip and Revision Prosthesis|
|US20130103158 *||21 Sep 2012||25 Abr 2013||Linares Medical Devices, Llc||Implantable elbow joint assembly with spherical inter-support|
|USRE38409||6 May 1988||27 Ene 2004||Joint Medical Products Corporation||Ball and socket bearing for artificial joint|
|CN105636554A *||25 Sep 2014||1 Jun 2016||扎菲尔·特曼尼尼||反转膝部假体|
|DE2631351A1 *||13 Jul 1976||10 Feb 1977||Research Corp||Kniegelenkprothese|
|DE2906458A1 *||20 Feb 1979||23 Ago 1979||Howmedica||Gelenkprothese|
|EP0021421A1 *||25 Jun 1980||7 Ene 1981||Biomedical Engineering Corp.||Prosthetic joint|
|EP0639358A1 *||20 Ago 1993||22 Feb 1995||Societe Civile Essor||Knee prosthesis with ball joint|
|WO2001013825A1 *||23 Ago 2000||1 Mar 2001||Woodcraft, David, Charles||Linked condylar total knee replacement|
|WO2015048273A1 *||25 Sep 2014||2 Abr 2015||Zafer Termanini||Reverse knee prosthesis|
|Clasificación de EE.UU.||623/20.22|