US20090216335A1 - Femoral Hip Prosthesis and Method of Implantation - Google Patents

Femoral Hip Prosthesis and Method of Implantation Download PDF

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Publication number
US20090216335A1
US20090216335A1 US12/429,882 US42988209A US2009216335A1 US 20090216335 A1 US20090216335 A1 US 20090216335A1 US 42988209 A US42988209 A US 42988209A US 2009216335 A1 US2009216335 A1 US 2009216335A1
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US
United States
Prior art keywords
prosthesis
femoral
femur
proximal
elongated stem
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.)
Abandoned
Application number
US12/429,882
Inventor
Michael Ries
T. Wade Fallin
Daniel F. Justin
Mark A. Munt
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.)
IMDS Corp
Original Assignee
Smith and Nephew Inc
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
Application filed by Smith and Nephew Inc filed Critical Smith and Nephew Inc
Priority to US12/429,882 priority Critical patent/US20090216335A1/en
Publication of US20090216335A1 publication Critical patent/US20090216335A1/en
Priority to US12/882,399 priority patent/US8157871B2/en
Assigned to RIES, MICHAEL D. reassignment RIES, MICHAEL D. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: SMITH & NEPHEW INC.
Assigned to IMDS CORPORATION reassignment IMDS CORPORATION ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: RIES, MICHAEL D.
Abandoned legal-status Critical Current

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Definitions

  • the present invention relates to a femoral hip prosthesis for replacing a portion of proximal femoral bone during hip replacement and the methods of assembly and use thereof.
  • Total hip arthroplasty using a metallic hip prosthesis has been successfully performed since the early 1960's and is now a routine procedure to address orthopedic diseases such as osteoarthritis, fracture, dislocations, rheumatic arthritis, and aseptic or avascular bone necrosis.
  • the bone is prepared for the prosthesis by removing the damaged articulating end of the bone by resecting a portion of the bone including the femoral head. This exposes the inside, of the metaphaseal region of the intramedullary canal in the proximal femur. The surgeon then drills or reams a cavity in the femur approximately in line with the intramedullary canal.
  • This cavity is used to align other tools such as reamers, broaches and other bone tissue removal instruments to create a roughly funnel shaped bone cavity that is smaller in cross-section as it extends down from the bone resection at the proximal end of the femur into the distal intramedullary canal.
  • This funnel shaped cavity is typically also eccentric with more bone material removed from the medial calcar region of the proximal femur than the region on the lateral side of the canal.
  • a grouting agent commonly referred to as bone cement is then added to the funnel shaped cavity.
  • bone cement is then added to the funnel shaped cavity.
  • the shape of the cavity is prepared to closely match the shape of the external surface of the prosthesis, and the prosthesis is press fit into the cavity without the use of bone cement.
  • These press-fit prostheses typically have a textured bone-ingrowth surfaces place strategically at specific locations on their surface to help facilitate lone-term bone tissue growth into the prosthesis. This bone ingrowth into the porous structure on the implant creates a long lasting secure bond between the prosthesis and the proximal femur.
  • the prosthesis is placed into the bone cavity and is supported directly by internal bone tissue in the case of a press fit implant or indirectly by the bone cement mantle in the case of the cemented implant. Then, the prosthesis is aligned such that the articulating end of the implant articulates with the opposite side of the natural joint in the case of a hemiarthoplasty, or articulates with a corresponding implant replacing the opposite side of the joint in the case of a total joint arthroplasty.
  • proximal femur hip prosthesis have eccentric, non-symmetric cone shaped central body portions.
  • the current methods of implant fixation allow for transfer of axial loads to the proximal femur mainly through shear stresses at the eccentric funnel shaped bone-prosthesis interface.
  • the effective transfer of load is significantly dependent on the three-dimensional shape of funnel shaped cavity, the bone-prosthesis or bone-cement-prosthesis interface as well as physiological loading of the proximal end.
  • these currently available prostheses transmit radial expansion forces on the proximal femoral cavity as the implant is loaded in compression.
  • the funnel shape of the cavity and the matching shape of the implant or bone cement result in circumferential hoop stresses and radial expansion stresses are distributed to the bone as the femoral component is axially loaded. This results in complex axial and shear stresses at the bone-implant interface. Consequently, the distribution of the loads that transmit from the femoral head axially through the proximal femur is altered after THA.
  • a potential cause of failure of currently used prosthesis is associated with the possible resorption of the bone surrounding the implant.
  • the bone resorption can be the result of an altered distribution of shear stresses on the remaining proximal femoral tissue.
  • the lack of adequate stress transfer from the metal stem to the surrounding bone may cause a loss of bone density, resulting in the increased possibility of bone failure or loosening of the bone-prosthesis interface.
  • the gradual loss of bone support in the calcar region of the eccentric cavity increases the bending load that must be borne by the prosthesis. This increase in bending load on the prosthesis can lead to stress shielding by the prosthesis resulting in prosthesis fatigue and potentially to eventual clinical failure.
  • the present invention is directed to a femoral hip prosthesis that satisfies the need for anatomically distributing the dynamic compressive loads on the hip joint to the proximal femoral bone.
  • the femoral hip prosthesis is adapted for implantation against a resected surface on a proximal end of a femur, and also in an intramedullary cavity of the femur.
  • the femoral hip prosthesis comprises femoral head component and a femoral stem component.
  • the femoral stem component comprises a neck portion, a flange portion, a transitional body portion, and an elongated stem portion.
  • the neck portion comprises a proximal male friction fit portion and a distal neck body.
  • the flange portion is distal and adjacent to the neck portion and is attached to the distal neck body.
  • the flange portion comprises an upper portion and a bottom surface.
  • the transitional body region is adjacent to the bottom surface of the flange portion and also extends from the distal neck body.
  • the elongated stem portion extends distally from the transitional body region and is aligned with a longitudinal axis.
  • the longitudinal axis is oriented at an acute angle relative to the bottom surface of the flange portion.
  • the elongated stem portion comprises a uniform envelope that may contain rotation-restricting splines, a tapered portion or a transverse slot.
  • the femoral hip prosthesis may also alternatively contain a rotation-restricting boss that is attached to the bottom of the flange portion.
  • the femoral hip prosthesis also comprises a distal end tip portion on the distal end of the elongated stem portion.
  • FIG. 1 is a perspective view of the show from the anteriomedial direction showing the femoral hip prosthesis including the before it is inserted into the resected proximal femur;
  • FIG. 2 is a perspective view shown form the anterioromedial direction showing the femoral hip prostheses before it is inserted and a cross-sectional view of the resected proximal femur with the intramedullary cavity and the boss cavity prepared;
  • FIG. 3 is a perspective view shown from the posteriorolateral position showing the before it is inserted into the resected proximal femur;
  • FIG. 4 is an anterior side view of the femoral hip prosthesis shown outside of the femur;
  • FIG. 4 a is an embodiment of a substantially circular cross-section of the elongated stem portion
  • FIG. 4 b is an embodiment of a substantially square cross-section of the elongated stem portion
  • FIG. 4 c is an embodiment of a substantially triangular cross-section of the elongated stem portion
  • FIG. 4 d is an embodiment of a substantially hexagonal cross-section of the elongated stem portion
  • FIG. 4 e is an embodiment of a substantially star shaped cross-section of the elongated stem portion
  • FIG. 5 is an isometric view of the medial side of the femoral stem component as it appears outside of the femur;
  • FIG. 6 is a cross-sectional view of the proximal femur from the anterior side showing the positioning of the femoral stem component inside of the proximal femur;
  • FIG. 7 is a medial view of the femoral hip prosthesis inside of the proximal femur.
  • FIGS. 1 through 7 Depicted in FIGS. 1 through 7 are different embodiments of an implantable proximal femoral hip prosthesis 50 and methods of implantation therein. These embodiments of a hip joint replacement procedure and the design of the femoral hip prosthesis 50 that is meant to restore the biomechanical function of the hip joint while maintaining a secure interface with the proximal femur 10 and help to preserve anatomical loading of the remaining bone that surrounds the femoral hip prosthesis 50 once it is implanted. This allows the loads on the hip joint to be distributed optimally to the proximal femur 10 .
  • the femoral hip prosthesis 50 comprises a femoral head component 700 and a femoral stem component 100 .
  • the femoral stem component 100 comprises a neck portion 150 , a flange portion 200 , a transitional body portion 300 , an elongated stem portion 400 , and a distal tip end 500 .
  • the non-eccentric symmetrical shape of the interface between the elongated stem portion 400 of the femoral stem component 100 and a cavity 25 along with the contact at the interface between a proximal resection 20 and the femoral stem component 100 helps to stabilize the femoral hip prosthesis 50 and transfer more anatomic loads from the prosthesis 50 to the bone efficiently.
  • FIG. 1 is a simplified perspective view from the anteriomedial direction showing the proximal femur 10 and the femoral hip prosthesis 50 , showing the femoral head component 700 , the femoral stem component 100 , and the proximal femur 10 .
  • the femoral head component 700 shows the femoral head component 700 .
  • the femoral stem component 100 shows the proximal femur 10 .
  • all of the other tissues necessary to provide function to the hip joint are not shown in this simplified view.
  • the surgeon aligns bone tissue removal tools, such as drills, reamers, or broaches (not shown) with alignment instrumentation (not shown) to form a substantially non-eccentric, symmetric intramedullary cavity 25 in the cancellous bone 3 of the proximal femur 10 that is in longitudinal alignment with the shaft 45 of the proximal femur 10 .
  • the intramedullary cavity 25 is formed with a cross-sectional shape, such as a diameter 46 as shown in an embodiment of the intramedullary cavity 25 shown in FIG. 2 .
  • the diameter 46 is the measurement of the diameter of the maximum circular periphery that encompasses an envelope that the cross-sectional shape of the intramedullary cavity 25 comprises.
  • the shape of the intramedullary cavity 25 can also be substantially non-eccentric, symmetric, non-circular shapes such as a square (not shown), star shape, (not shown), hexagon (not shown), or other parallelogram shape. Matching non-circular shapes of both the femoral stem component 100 and the intramedullary cavity 25 are potentially more efficient at restricting torsional movement between the femoral stem component 100 and the proximal femur 10 than circular cross-sectional shapes.
  • the intramedullary cavity 25 also is formed to a length 47 as also shown in FIG. 2 .
  • the cross-sectional shape, diameter 46 and length 47 of the intramedullary cavity 25 in the proximal femur 10 is dependent on the morphology, structure, and pathology of the patient anatomy and the anticipated biomechanical in vivo loads resulting from the use of the femoral stem component 100 .
  • the intramedullary cavity 25 may have a multiple diameters, or in the case of non-circular cross-sectionally shaped cavities multiple sizes, to approximately match the shape of the femoral stem component 100 .
  • FIG. 2 which illustrates a cross-sectional view of the proximal femur 10 , shows that both a first diameter 46 and a second diameter 48 can form an intramedullary cavity 25 is shown in FIG. 2 .
  • the second diameter 48 in the embodiment of FIG. 2 is smaller than the first diameter 46 .
  • a third, forth, fifth, or more diameters can form the intramedullary cavity 25 .
  • the cavities 2 are circular, resulting in a substantially cylindrical opening.
  • different size or shaped tissue removal tools (not shown) are used to prepare an intramedullary cavity 25 with more than one size diameter 46 .
  • the surgeon may also find it advantageous to form different or alternating shapes of cross-sections in the symmetric, non-eccentric intramedullary cavity 25 .
  • the cavity may be first diameter circular, and then square, then a second diameter circle, then a star shape, then cone shaped, then finally spherically shaped at its deepest, most distal end.
  • instrumentation is used to align cutting guides for bone cutting instruments (not shown) to form a proximal resection 20 on the proximal femur 10 .
  • the proximal resection 20 may have different surfaces such as a calcar resection surface 12 that is formed when the femoral calcar 11 is transverely cut through the proximal femur 10 .
  • the calcar resection surface 12 is cut at an acute angle 22 with respect to the longitudinal axis 21 of the proximal femur 10 . This acute angle is typically between 10° and 80°.
  • proximal resection 20 may be simply one continuous transverse cut that passes from the medial to the lateral side of the proximal femur in the direction and plane defined by a the plane outlined by the dashed line 16 shown in FIG. 1 .
  • This alternative resection 17 is formed by extending the calcar resection 12 from medial to lateral though the entire proximal femur 10 .
  • More bone conserving cuts may also be formed in to the proximal femur 10 as shown in FIG. 1 .
  • These cuts may include a formed concentric region 15 that is larger in size but concentric to or aligned with the intramedullary cavity 25 .
  • These cuts may also include a transverse resection 13 that is cut relatively perpendicular to the intramedullary cavity 25 .
  • the resections shown in FIG. 1 can all be formed by a single reamer (not shown). This reamer has a cutting surface formed in the shape of the combined profile of all of the resection cuts. It can be rotated or oscillated about the longitudinal axis 21 of the intramedullary canal 25 , until the desire bone tissue is removed.
  • the various cuts that together form the proximal resection 20 pass through portions of both the relatively dense cortical bone 44 and the more porous cancellous bone 3 .
  • the cutting surfaces of the tissue removal tools are designed to cut both dense cortical bone 44 and less dense cancellous bone 3 .
  • the femoral stem component 100 can be inserted to mate with the exposed bone surfaces.
  • the femoral stem component 100 comprises a proximal male friction fit portion 150 , a distal neck body 160 , a flange portion 200 , a transitional body portion 300 , an elongated stem portion 400 , and a distal end tip portion 500 . These portions will be discussed in detail below.
  • the femoral stem component 100 has a proximal male friction fit portion 150 on its most proximal end that is shaped to accept partially hemispherical femoral head component 700 .
  • One shape of the proximal male friction fit portion 150 is a cylindrical taper shape with the smaller diameter on the male friction fit portion proximal section 151 , a tapered male friction fit portion 152 distal to the male friction fit portion proximal section 151 , and a larger diameter male friction fit portion taper maximum cross-section bottom end 153 on the distal end of the male friction fit portion 152 .
  • the proximal male friction fit portion 150 could also be a straight cylindrical shape without a taper, or a series of successively larger diameter cylindrical shapes.
  • a femoral head component 700 has a male cavity 720 that is dimensioned to fit over and mate with the friction fit portion 152 of the proximal male friction fit portion 150 when the femoral head component 700 is assembled on the proximal male friction fit portion 150 .
  • the femoral head prosthesis 700 has an external bearing surface portion 710 on its external surface that is substantially on its proximal side when implanted.
  • the external bearing surface portion 710 of the femoral head prosthesis 700 is substantially hemispherical shaped on a portion of its load bearing external bearing surface.
  • This hemispherical shape is designed to mate with either an artificial prosthetic acetabular cup surface (not shown) as is the case for a total hip arthroplasty or a natural acetabular surface as is the case for a hip femoral hemiplasty.
  • the proximal male friction fit portion 150 has a male friction fit portion neck 154 that is distal to the male friction fit portion portion 152 and adjacent to the male friction fit portion taper bottom end 153 .
  • This male friction fit portion neck 154 functions as an undercut relief for the femoral head component 700 when assembled. Because the male friction fit portion neck 154 is smaller in diameter than the male friction fit portion portion 152 , the femoral head component 700 can be pressed onto the proximal male friction fit portion 150 with the only direct contact between the two on the friction fit portion 152 of the femoral stem component 100 and the male friction fit portion 720 of the femoral head component 700 .
  • the male friction fit portion neck 154 is proximal to and attached directly to a more bulky distal neck body 160 .
  • the distal neck body 160 is shaped to distribute the loads transmitted through the proximal male friction fit portion 150 from the femoral head component 700 through a flange portion 200 and a transitional body portion 300 .
  • the shape of the distal neck body 160 transitions from a simple symmetric shape similar to the cross-section of the male friction fit portion neck 154 to a more complex asymmetric shape that is similar to the combined shape of the flange portion 200 and the transitional body portion 300 . In the embodiment shown in FIGS. 1 through FIG.
  • the cross-sectional shape of the distal neck body 160 at the proximal section is round because the male friction fit portion is a conical tapered and the male friction fit portion neck 154 is a cylindrical hourglass shape.
  • the shape of the distal neck body 160 at the proximal section can be other shape to correspond with the shape of the proximal male friction fit portion 150 .
  • the flange portion 200 has an upper portion 210 on its proximal side that contacts at least a part of the distal neck body 160 .
  • the flange portion is angled to match the at the same angle as the calcar resection 12 made by the surgeon on the proximal femur 10 .
  • the angle and the size of the flange portion 200 are dependent on the anatomy of the patient and the morphology of the calcar resection 12 .
  • the flange portion 200 has an anterior-posterior flange portion width 240 that is wide enough to cover at least a portion of the cortical bone tissue 44 that has been resected.
  • the cortical bone tissue 44 is more rigid than the cancellous bone tissue 3 .
  • the compressive loads are transmitted through both the cancellous bone tissue and the cortical bone tissue 44 of the proximal femur 10 . Because the cortical bone tissue 44 is more dense and rigid, and can sustain a higher load per square unit area without fracture than the cancellous bone tissue 3 , cortical bone tissue 44 is a more efficient distributor of compressive loads than cancellous bone tissue 3 .
  • the flanged portion 200 is shaped to cover both the resected cancellous bone 3 and the resected cortical bone 44 so that the compressive loads transmitted through the flange portion 200 are distributed as anatomically close as possible to how they were distributed when the proximal femur 10 was healthy and intact.
  • the flanged portion 200 is less thick than it is wide. As shown in the embodiment of FIG. 4 , the flange portion thickness 221 is between 0.5 millimeters and 12 millimeters. The flange portion 200 is substantially thick enough to transmit loads from the hip joint to the calcar resection surface 12 of both the cancellous bone tissue 3 and the cortical bone tissue 44 . The flange portion 200 is also thin enough to limit the about of bone that must be resected to form the calcar resection 12 .
  • the transitional body region 300 is the portion of the femoral stem component 100 that transitions from the distal neck body 160 and the flange portion 200 to the distal elongated stem portion 400 .
  • the transitional body region 300 is adjacent to both the distal neck body 160 and the flange portion 200 on its proximal side and adjacent to the elongated stem portion 400 on its distal side.
  • the transitional body portion 300 has a maximum height 310 that is the linear distance measured between a plane tangent to the bottom surface 220 of the flange portion 200 and a plane through the most distal part of the transitional body portion 300 . In FIG. 4 , these two planes are shown as lines since this is a side view. In the embodiment of the transitional body portion shown in FIG.
  • the transitional body portion 300 has a curved fillet 330 its medial side. Although this is shown as a round fillet in FIG. 4 , the medial side of the transitional body portion 300 can be a chamfered fillet, a stepped fillet, or any other non-linear or linear shape that transitions from the shape of the elongated stem portion 400 to the shape of portions of the distal neck body 160 or the flange portion 200 .
  • the maximum height 310 of the majority of the transitional body region 300 when measured normal from the bottom surface 220 of the flange portion 200 to any part of the elongated stem portion 400 is less than thirteen millimeters or less. Both the physical structure of the femoral hip prosthesis 50 , and the mechanical properties of the material from which the prosthesis is fabricated, function together to determine the functional strength and elasticity of the femoral stem component 100 .
  • Conventional orthopedic alloys such as cobalt chrome, titanium and stainless steel alloys and orthopedic composite materials have proven to provide reasonable strength and rigidity to orthopedic implants and may also be used to fabricate the femoral stem component 100 .
  • conventional orthopedic alloys or composites are fabricated into the eccentric conical shape of a typical femoral stem component 100 , the resulting implant is more rigid than the proximal femoral 10 that the femoral stem component 100 is replacing. Flexibility of the stem component 100 is necessary to allow the flex and compliance desired to dynamically anatomically load the proximal femur 10 bone during biomechanical loading.
  • transitional body portion 300 allows for more flexion of the flange portion 200 when the proximal male friction fit portion 150 is loaded than is seen with the bulkier conventional eccentric cone shaped femoral prosthesis.
  • the unique shape of the femoral stem component 100 allows for flexibility of the prosthesis even when fabricated from rigid orthopedic alloys such as such as cobalt chrome, titanium and stainless steel alloys.
  • This dynamic flexibility within the transitional portion 300 is desired since it allows the flange portion 200 of the femoral stem component 100 to transmit loads and displacements to the femoral calcar region 11 of the proximal femur 10 .
  • a piezoelectric effect within the tissue simulate the bone cells into further production.
  • This phenomenon sometimes called Wolfs Law, coupled with other physiologic and biochemical principles, helps to keep the bone surrounding the femoral hip prosthesis 50 healthy and vibrant.
  • the femoral stem component 100 is designed to optimize the effects that a flexible, yet strong femoral hip prosthesis 50 will have on the surrounding loaded bone tissue.
  • transitional body portion 300 is relatively flexible and not as bulky and rigid as a conventional femoral hip prosthesis, the transitional body portion 300 allows the femoral stem component 100 to flex and transmit the compressive load to the bone in the calcar region 11 of the proximal femur 10 .
  • loads on the bone may allow the dynamization necessary to keep the tissue surrounding the femoral stem component 100 healthy and help prevent bone resorption in the calcar region 11 of the proximal femur 10 .
  • the elongated stem portion 400 Distal and adjacent to the transitional body portion 300 is the elongated stem portion 400 .
  • the elongated stem portion 400 comprises some or all of the following portions and features; a tapered portion 450 , a splined section 470 , and transverse slot 480 .
  • the elongated stem portion is encompassed within a cylindrically shaped envelope referred to as uniform envelope 410 .
  • the cross-sectional shape and the area of the uniform envelope 410 remains substantially uniform throughout the longitudinal length of the elongated body.
  • the uniform envelope 410 has a circular uniform cross-sectional periphery 902 that is defined by the maximum cross-sectional peripheral diameter 905 of the elongated stem portion 400 .
  • the uniform envelope 410 is the same length as the elongated stem portion.
  • the elongated stem portion is adjacent to the transitional body portion 300 on its proximal end and adjacent to a distal tip portion 500 on its distal end.
  • the elongated stem portion 400 is longitudinally aligned with a longitudinal axis 425 .
  • the longitudinal axis 425 is approximately in alignment with the longitudinal axis 21 of the intramedullary cavity 25 .
  • All the possible features or portions of the elongated stem portion 400 including the tapered portion 450 , the spine section 470 , and the transverse slot 480 have cross-sections perpendicular to the longitudinal axis 425 and are contained within a maximum diameter 905 of a cross-sectional periphery 902 that defines the cross-section of the uniform envelope 410 .
  • FIG. 4 a through FIG. 4 e Representative shapes of cross-sectional areas viewed from a cross-sectional view cut plane 900 are shown in FIG. 4 a through FIG. 4 e. Included in these figures are the cross-sectional periphery 902 and the maximum diameter 905 of the cross-sectional periphery 902 .
  • Material may be removed from the elongated stem portion 400 to created features such as taper portions 450 , splines 460 or the transverse slots 480 .
  • the basic substantial shape of the external periphery of the cross-section of the elongated stem portion 400 remains uniform and circular.
  • the elongated stem portion and the uniform envelope 410 are both substantially symmetric and non-eccentric.
  • the embodiment of the elongated stem portion 400 shown in FIG. 4 is substantially cylindrical in shape 910 .
  • the cross-section of this cylindrically shaped elongated stem portion is shown in FIG. 4 a.
  • the cross-sectional shape of the elongated stem portion 400 can be also non-circular shapes such as substantially square shape 920 , as shown in FIG. 4 b; a substantially triangle shape 930 , as shown in FIG. 4 c; a substantially hexagonal shape 940 , as shown in FIG. 4 c, a substantially star shape 950 as shown in FIG. 4 e , or any other substantially non-eccentric, symmetric shape such as a tube (not shown) that can functionally form the cross-section of the elongated stem portion 400 .
  • the longitudinal axis 425 of the elongated stem portion 400 is a substantially straight axis throughout the length of the elongated stem portion 400 .
  • the longitudinal axis 425 can also be curved.
  • the curve may be in the anterior-posterior plane, the medial-lateral plane or a compound curve that is seen in both the anterior-posterior plane and the medial-lateral plane.
  • a flexible reamer (not shown) could be used to form the curved intramedullary cavity before the prosthesis 10 with a curved longitudinal axis 425 is implanted.
  • the elongated stem portion 400 may include a tapered portion 450 along its length. This is shown in FIG. 2 .
  • This tapered portion 450 may also include splines 460 or transverse slots 480 cut into it.
  • the cross-sectional area of the tapered portion 450 in the embodiments shown decreases linearly along the longitudinal length of the tapered portion 450 as the tapered portion 450 transitions down the length of the elongated stem portion 400 from proximal to distal.
  • the direction of the tapered portion 450 may also be in the opposite direction.
  • the tapered area in the elongated portion 400 allows for greater flexibility in bending along the tapered portion 450 due to the reduced cross-sectional area and reduced cross-sectional bending moment of inertia.
  • the tapered portion 450 also allows for an interference tapered wedge fit between the elongated stem portion 400 and the intramedullary cavity 25 in the proximal femur 10 when the cross-sectional size of the intramedullary canal 25 is less than the maximum diameter 905 of the periphery 902 .
  • the splines 460 are cut into the elongated stem portion 400 for various structural and functional reasons such as to provide additional torsional resistance to the femoral stem component 100 .
  • the splines 460 are evenly spaced around the periphery 902 of the distal elongated stem portion 400 .
  • the splines 460 are cut longitudinal around the periphery 902 of the elongated stem portion 400 . This allows the splines 460 to resist axial rotation between the femoral stem component 100 and the intramedullary cavity 25 .
  • the splines 460 may also provide additional structural flexibility to the distal end of the femoral stem component 100 .
  • an optional longitudinal transverse slot 480 may be cut transversely into the elongated stem portion 400 to provide additional flexibility and potentially additional torsional resistance to the femoral stem component 100 .
  • the embodiment of the slot 480 that is shown is substantially uniform in cross-sectional and in shape though its length.
  • the cross-sectional shape of the slot 480 may also be non-uniform.
  • the cross-sections shape of the slot 480 may also change. For example the sides of the slot 481 may change from parallel planar surfaces to non-parallel or non-planar surfaces as the slot transitions from distal to proximal.
  • the slot 480 also has a fillet 485 that takes the form of a rounded radius shape at its most proximal end.
  • the shape of this fillet 485 may be other shapes that allow a relatively smooth transition from the slot 480 to the non-slotted cross-section.
  • the slot 480 may be keyhole shaped.
  • the distal end tip portion 500 Adjacent and distal to the elongated stem portion is the distal end tip portion 500 .
  • the distal end tip portion 500 has a lead-in section 510 that reduces in cross-sectional area from proximal to distal.
  • the lead-in section may be tapered as in the embodiment of FIG. 3 , or spherical as in the embodiment of FIG. 4 , or any shape that is successively smaller in cross-sectional area from proximal to distal.
  • the distal end tip portion 500 helps to guide the femoral stem component 100 into the intramedullary canal 25 .
  • the relatively smooth shape of the distal end tip portion 500 also functions to reduce the stress on the proximal femoral bone associated with discontinuity of terminating a rigid prosthesis in the intramedullary canal 25 .
  • the load distribution on the proximal femur 10 of an intact hip joint can be essentially resolved into an axial component, a bending moment in the medial and lateral direction, a bending moment in the anterior posterior direction, and a torsional moment with a rotational axis approximately in line with the longitudinal axis 21 of the proximal femur.
  • the distribution of the magnitude and direction of these force components depend upon complex combinations of biomechanical factors such as leg stance, patient weight distribution, and patient gait.
  • the femoral stem component 100 is designed to translate these forces to anatomic loads on the proximal femur 10 .
  • the flange portion 200 helps to translate the compressive loads to the cancellous bone 3 and cortical bone 4 in the calcar region 11 .
  • the elongated stem portion 400 helps to transmit the bending and torsional moments to the intramedullary canal 25 .
  • a rotation-restricting boss 600 helps to transmit some of the torsional moments to the bone in the calcar region 11 of the proximal femur 10 . As shown in FIG. 6 , the boss periphery 630 of the rotation-restricting boss 600 interfaces with the bone surrounding the boss cavity 14 .
  • This structural interference between the femoral stem component 100 and the proximal femur 10 helps to restrict rotation, caused by the above-described resultant torsional moment with approximately in line with the longitudinal axis 21 of the proximal femur 10 , between the femoral stem component 100 and the intramedullary cavity 25 .
  • the size and location of the rotation-restricting boss 600 are factors that affect the amount that the rotation-restricting boss 600 restricts rotational movement of the femoral stem component 100 . Due to greater resistance from a rotation-restricting boss with a larger resultant moment arm, the further that the rotation-restricting boss 600 is located from the longitudinal axis 425 of the elongated stem portion 400 , the more effective it is in transmitting rotational loads and restricting rotational movement of the femoral stem component 100 to the proximal femur 10 . Also, the larger the cross-sectional area of the rotation-restricting boss 600 , the more effective it is in distributing torsion and restricting rotational movement of the femoral stem component 100 .
  • the embodiments of the rotation-restricting boss 600 that are shown by example are circular in cross-section resulting in a cylindrical shaped boss.
  • other cross-sectional shapes such as square, rectangular, triangular or diamond shapes may be more practical to machine or may be better at distributing torsional loads from the femoral hip prosthesis 50 to the proximal femur 10 than the shown cylindrically shaped rotation-restricting boss 600 .
  • the optimized shape of the rotation-restricting boss 600 may be more fin shaped than cylindrical shaped or longer than it is wide. This shape is partially dependent on the mechanical characteristics of the bone tissue where the rotation-restricing boss 600 is inserted.
  • the rotation restricting boss 600 has an axis of protrusion 620 with origin 621 substantially on a plane tangent or coincident with the bottom surface 220 of the flange portion 200 .
  • the boss axis of protrusion origin 621 and the stem portion longitudinal axis 425 are spaced apart by a length this is more than the maximum length 905 of the cross-section of the periphery 902 of the uniform envelope 410 of the elongated stem portion 400 .
  • the rotation-restricting boss 600 in the embodiment of the prosthesis 10 shown in FIG. 3 has an axis of protrusion that is substantially normal to the bottom surface 220 of the flange portion 200 .
  • the rotation-restricting boss in the embodiment of the prosthesis 10 shown in FIG. 4 , FIG. 5 and FIG. 6 has an axis of protrusion 620 that is substantially parallel with the longitudinal axis 425 of the elongated stem portion 400 .
  • the corresponding boss cavity 14 is in line with the axis of protrusion 620 .
  • the flange portion 200 is pressed against a resected surface 20 on the proximal femur 10 , and the elongated stem portion 400 is pressed in the intramedullary cavity 25 aligned with the long axis of the proximal femur 10 .
  • the femoral head 700 is loaded by the hip joint, a substantial component of the axial compressive force is transmitted to the cancellous 3 and cortical 4 bone in the calar region 11 from the flange portion 200 .

Abstract

Implants and methods are presented for surgically repairing a hip joint with a proximal femoral prosthesis that comprises femoral head component and a femoral stem component. The femoral stem component comprises a neck portion, a flange portion, a transitional body region and an elongated stem. The femur is prepared for implantation of the femoral hip prosthesis by resecting the proximal femur and reaming a symmetric intramedullary cavity in the femur. The femoral hip prosthesis is then inserted the on the resected femur and in the intramedullary cavity. The femoral hip prosthesis elastically deforms when loaded during use to apply dynamic compressive loads and displacement to the calcar region of the resected proximal femur.

Description

    CROSS-REFERENCE TO RELATED APPLICATIONS
  • This application is a Continuation of the following:
  • U.S. patent application Ser. No. 10/763,314 filed Jan. 22, 2004 which carries Applicants' docket no. MLI-10 and is entitled FEMORAL HIP PROSTHESIS AND METHOD OF IMPLANTATION.
  • BACKGROUND OF THE INVENTION
  • 1. The Field of the Invention
  • The present invention relates to a femoral hip prosthesis for replacing a portion of proximal femoral bone during hip replacement and the methods of assembly and use thereof.
  • 2. The Relevant Technology
  • Total hip arthroplasty using a metallic hip prosthesis has been successfully performed since the early 1960's and is now a routine procedure to address orthopedic diseases such as osteoarthritis, fracture, dislocations, rheumatic arthritis, and aseptic or avascular bone necrosis. During this procedure, the bone is prepared for the prosthesis by removing the damaged articulating end of the bone by resecting a portion of the bone including the femoral head. This exposes the inside, of the metaphaseal region of the intramedullary canal in the proximal femur. The surgeon then drills or reams a cavity in the femur approximately in line with the intramedullary canal. This cavity is used to align other tools such as reamers, broaches and other bone tissue removal instruments to create a roughly funnel shaped bone cavity that is smaller in cross-section as it extends down from the bone resection at the proximal end of the femur into the distal intramedullary canal. This funnel shaped cavity is typically also eccentric with more bone material removed from the medial calcar region of the proximal femur than the region on the lateral side of the canal.
  • Oftentimes a grouting agent commonly referred to as bone cement is then added to the funnel shaped cavity. Once the prosthesis is inserted into the cavity, this creates a bone cement mantle between the prosthesis and the bone. Sometimes the shape of the cavity is prepared to closely match the shape of the external surface of the prosthesis, and the prosthesis is press fit into the cavity without the use of bone cement. These press-fit prostheses typically have a textured bone-ingrowth surfaces place strategically at specific locations on their surface to help facilitate lone-term bone tissue growth into the prosthesis. This bone ingrowth into the porous structure on the implant creates a long lasting secure bond between the prosthesis and the proximal femur.
  • Once the bone cavity is prepared, the prosthesis is placed into the bone cavity and is supported directly by internal bone tissue in the case of a press fit implant or indirectly by the bone cement mantle in the case of the cemented implant. Then, the prosthesis is aligned such that the articulating end of the implant articulates with the opposite side of the natural joint in the case of a hemiarthoplasty, or articulates with a corresponding implant replacing the opposite side of the joint in the case of a total joint arthroplasty.
  • Current designs of proximal femur hip prosthesis have eccentric, non-symmetric cone shaped central body portions. The current methods of implant fixation allow for transfer of axial loads to the proximal femur mainly through shear stresses at the eccentric funnel shaped bone-prosthesis interface. The effective transfer of load is significantly dependent on the three-dimensional shape of funnel shaped cavity, the bone-prosthesis or bone-cement-prosthesis interface as well as physiological loading of the proximal end. Partly because of the eccentrically shaped cross-section of the central body portion, these currently available prostheses transmit radial expansion forces on the proximal femoral cavity as the implant is loaded in compression. The funnel shape of the cavity and the matching shape of the implant or bone cement result in circumferential hoop stresses and radial expansion stresses are distributed to the bone as the femoral component is axially loaded. This results in complex axial and shear stresses at the bone-implant interface. Consequently, the distribution of the loads that transmit from the femoral head axially through the proximal femur is altered after THA.
  • A potential cause of failure of currently used prosthesis is associated with the possible resorption of the bone surrounding the implant. The bone resorption can be the result of an altered distribution of shear stresses on the remaining proximal femoral tissue. In time, the lack of adequate stress transfer from the metal stem to the surrounding bone may cause a loss of bone density, resulting in the increased possibility of bone failure or loosening of the bone-prosthesis interface. The gradual loss of bone support in the calcar region of the eccentric cavity increases the bending load that must be borne by the prosthesis. This increase in bending load on the prosthesis can lead to stress shielding by the prosthesis resulting in prosthesis fatigue and potentially to eventual clinical failure.
  • SUMMARY
  • The present invention is directed to a femoral hip prosthesis that satisfies the need for anatomically distributing the dynamic compressive loads on the hip joint to the proximal femoral bone. The femoral hip prosthesis is adapted for implantation against a resected surface on a proximal end of a femur, and also in an intramedullary cavity of the femur. The femoral hip prosthesis comprises femoral head component and a femoral stem component. The femoral stem component comprises a neck portion, a flange portion, a transitional body portion, and an elongated stem portion. The neck portion comprises a proximal male friction fit portion and a distal neck body. The flange portion is distal and adjacent to the neck portion and is attached to the distal neck body. The flange portion comprises an upper portion and a bottom surface. The transitional body region is adjacent to the bottom surface of the flange portion and also extends from the distal neck body. The elongated stem portion extends distally from the transitional body region and is aligned with a longitudinal axis. The longitudinal axis is oriented at an acute angle relative to the bottom surface of the flange portion. The elongated stem portion comprises a uniform envelope that may contain rotation-restricting splines, a tapered portion or a transverse slot. The femoral hip prosthesis may also alternatively contain a rotation-restricting boss that is attached to the bottom of the flange portion. The femoral hip prosthesis also comprises a distal end tip portion on the distal end of the elongated stem portion.
  • DESCRIPTION OF THE DRAWINGS
  • Various embodiments of the present invention will now be discussed with reference to the appended drawings. It is appreciated that these drawings depict only typical embodiments of the invention and are therefore not to be considered limiting of its scope.
  • FIG. 1 is a perspective view of the show from the anteriomedial direction showing the femoral hip prosthesis including the before it is inserted into the resected proximal femur;
  • FIG. 2 is a perspective view shown form the anterioromedial direction showing the femoral hip prostheses before it is inserted and a cross-sectional view of the resected proximal femur with the intramedullary cavity and the boss cavity prepared;
  • FIG. 3 is a perspective view shown from the posteriorolateral position showing the before it is inserted into the resected proximal femur;
  • FIG. 4 is an anterior side view of the femoral hip prosthesis shown outside of the femur;
  • FIG. 4 a is an embodiment of a substantially circular cross-section of the elongated stem portion;
  • FIG. 4 b is an embodiment of a substantially square cross-section of the elongated stem portion;
  • FIG. 4 c is an embodiment of a substantially triangular cross-section of the elongated stem portion;
  • FIG. 4 d is an embodiment of a substantially hexagonal cross-section of the elongated stem portion;
  • FIG. 4 e is an embodiment of a substantially star shaped cross-section of the elongated stem portion;
  • FIG. 5 is an isometric view of the medial side of the femoral stem component as it appears outside of the femur;
  • FIG. 6 is a cross-sectional view of the proximal femur from the anterior side showing the positioning of the femoral stem component inside of the proximal femur;
  • FIG. 7 is a medial view of the femoral hip prosthesis inside of the proximal femur.
  • DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
  • Depicted in FIGS. 1 through 7 are different embodiments of an implantable proximal femoral hip prosthesis 50 and methods of implantation therein. These embodiments of a hip joint replacement procedure and the design of the femoral hip prosthesis 50 that is meant to restore the biomechanical function of the hip joint while maintaining a secure interface with the proximal femur 10 and help to preserve anatomical loading of the remaining bone that surrounds the femoral hip prosthesis 50 once it is implanted. This allows the loads on the hip joint to be distributed optimally to the proximal femur 10.
  • The femoral hip prosthesis 50 comprises a femoral head component 700 and a femoral stem component 100. The femoral stem component 100 comprises a neck portion 150, a flange portion 200, a transitional body portion 300, an elongated stem portion 400, and a distal tip end 500. The non-eccentric symmetrical shape of the interface between the elongated stem portion 400 of the femoral stem component 100 and a cavity 25 along with the contact at the interface between a proximal resection 20 and the femoral stem component 100 helps to stabilize the femoral hip prosthesis 50 and transfer more anatomic loads from the prosthesis 50 to the bone efficiently.
  • To prepare the patient for a proximal femoral hip prosthesis 50, the surgeon first makes an incision or incisions near the hip joint, then the surgeon cuts though some of the tissue near the articulating joint, and retracts these tissues apart to visualize and access the diseased bone structures that are to be replaced by the hip joint replacement prostheses. FIG. 1, is a simplified perspective view from the anteriomedial direction showing the proximal femur 10 and the femoral hip prosthesis 50, showing the femoral head component 700, the femoral stem component 100, and the proximal femur 10. For clarification, all of the other tissues necessary to provide function to the hip joint are not shown in this simplified view. The surgeon aligns bone tissue removal tools, such as drills, reamers, or broaches (not shown) with alignment instrumentation (not shown) to form a substantially non-eccentric, symmetric intramedullary cavity 25 in the cancellous bone 3 of the proximal femur 10 that is in longitudinal alignment with the shaft 45 of the proximal femur 10. The intramedullary cavity 25 is formed with a cross-sectional shape, such as a diameter 46 as shown in an embodiment of the intramedullary cavity 25 shown in FIG. 2. The diameter 46 is the measurement of the diameter of the maximum circular periphery that encompasses an envelope that the cross-sectional shape of the intramedullary cavity 25 comprises. The shape of the intramedullary cavity 25 can also be substantially non-eccentric, symmetric, non-circular shapes such as a square (not shown), star shape, (not shown), hexagon (not shown), or other parallelogram shape. Matching non-circular shapes of both the femoral stem component 100 and the intramedullary cavity 25 are potentially more efficient at restricting torsional movement between the femoral stem component 100 and the proximal femur 10 than circular cross-sectional shapes. The intramedullary cavity 25 also is formed to a length 47 as also shown in FIG. 2. The cross-sectional shape, diameter 46 and length 47 of the intramedullary cavity 25 in the proximal femur 10 is dependent on the morphology, structure, and pathology of the patient anatomy and the anticipated biomechanical in vivo loads resulting from the use of the femoral stem component 100.
  • The intramedullary cavity 25 may have a multiple diameters, or in the case of non-circular cross-sectionally shaped cavities multiple sizes, to approximately match the shape of the femoral stem component 100. FIG. 2, which illustrates a cross-sectional view of the proximal femur 10, shows that both a first diameter 46 and a second diameter 48 can form an intramedullary cavity 25 is shown in FIG. 2. The second diameter 48 in the embodiment of FIG. 2 is smaller than the first diameter 46. Additionally, a third, forth, fifth, or more diameters (all not shown) can form the intramedullary cavity 25. For the purposes of clarity of illustration, the cross-section of the intramedullary cavity on FIG. 1 and FIG. 2 are circular, resulting in a substantially cylindrical opening. Correspondingly different size or shaped tissue removal tools (not shown) are used to prepare an intramedullary cavity 25 with more than one size diameter 46. The surgeon may also find it advantageous to form different or alternating shapes of cross-sections in the symmetric, non-eccentric intramedullary cavity 25. For example, the cavity may be first diameter circular, and then square, then a second diameter circle, then a star shape, then cone shaped, then finally spherically shaped at its deepest, most distal end.
  • After the basic intramedullary cavity 25 is formed, instrumentation (not shown) is used to align cutting guides for bone cutting instruments (not shown) to form a proximal resection 20 on the proximal femur 10. The proximal resection 20 may have different surfaces such as a calcar resection surface 12 that is formed when the femoral calcar 11 is transverely cut through the proximal femur 10. The calcar resection surface 12 is cut at an acute angle 22 with respect to the longitudinal axis 21 of the proximal femur 10. This acute angle is typically between 10° and 80°. Although the proximal resection 20 may be simply one continuous transverse cut that passes from the medial to the lateral side of the proximal femur in the direction and plane defined by a the plane outlined by the dashed line 16 shown in FIG. 1. This alternative resection 17 is formed by extending the calcar resection 12 from medial to lateral though the entire proximal femur 10.
  • More bone conserving cuts may also be formed in to the proximal femur 10 as shown in FIG. 1. These cuts may include a formed concentric region 15 that is larger in size but concentric to or aligned with the intramedullary cavity 25. These cuts may also include a transverse resection 13 that is cut relatively perpendicular to the intramedullary cavity 25. To simplify the surgical procedure, the resections shown in FIG. 1 can all be formed by a single reamer (not shown). This reamer has a cutting surface formed in the shape of the combined profile of all of the resection cuts. It can be rotated or oscillated about the longitudinal axis 21 of the intramedullary canal 25, until the desire bone tissue is removed. As shown in FIG. 2, the various cuts that together form the proximal resection 20 pass through portions of both the relatively dense cortical bone 44 and the more porous cancellous bone 3. Thus, the cutting surfaces of the tissue removal tools are designed to cut both dense cortical bone 44 and less dense cancellous bone 3.
  • After the intramedullary cavity 25 and the proximal resection 20, including the calcar resection 12 and when applicable other bone tissue removal cuts are formed, the femoral stem component 100 can be inserted to mate with the exposed bone surfaces. The femoral stem component 100 comprises a proximal male friction fit portion 150, a distal neck body 160, a flange portion 200, a transitional body portion 300, an elongated stem portion 400, and a distal end tip portion 500. These portions will be discussed in detail below.
  • The femoral stem component 100 has a proximal male friction fit portion 150 on its most proximal end that is shaped to accept partially hemispherical femoral head component 700. One shape of the proximal male friction fit portion 150 is a cylindrical taper shape with the smaller diameter on the male friction fit portion proximal section 151, a tapered male friction fit portion 152 distal to the male friction fit portion proximal section 151, and a larger diameter male friction fit portion taper maximum cross-section bottom end 153 on the distal end of the male friction fit portion 152. The proximal male friction fit portion 150 could also be a straight cylindrical shape without a taper, or a series of successively larger diameter cylindrical shapes.
  • A femoral head component 700 has a male cavity 720 that is dimensioned to fit over and mate with the friction fit portion 152 of the proximal male friction fit portion 150 when the femoral head component 700 is assembled on the proximal male friction fit portion 150. The femoral head prosthesis 700 has an external bearing surface portion 710 on its external surface that is substantially on its proximal side when implanted. The external bearing surface portion 710 of the femoral head prosthesis 700 is substantially hemispherical shaped on a portion of its load bearing external bearing surface. This hemispherical shape is designed to mate with either an artificial prosthetic acetabular cup surface (not shown) as is the case for a total hip arthroplasty or a natural acetabular surface as is the case for a hip femoral hemiplasty.
  • The proximal male friction fit portion 150 has a male friction fit portion neck 154 that is distal to the male friction fit portion portion 152 and adjacent to the male friction fit portion taper bottom end 153. This male friction fit portion neck 154 functions as an undercut relief for the femoral head component 700 when assembled. Because the male friction fit portion neck 154 is smaller in diameter than the male friction fit portion portion 152, the femoral head component 700 can be pressed onto the proximal male friction fit portion 150 with the only direct contact between the two on the friction fit portion 152 of the femoral stem component 100 and the male friction fit portion 720 of the femoral head component 700.
  • The male friction fit portion neck 154 is proximal to and attached directly to a more bulky distal neck body 160. The distal neck body 160 is shaped to distribute the loads transmitted through the proximal male friction fit portion 150 from the femoral head component 700 through a flange portion 200 and a transitional body portion 300. The shape of the distal neck body 160 transitions from a simple symmetric shape similar to the cross-section of the male friction fit portion neck 154 to a more complex asymmetric shape that is similar to the combined shape of the flange portion 200 and the transitional body portion 300. In the embodiment shown in FIGS. 1 through FIG. 7, the cross-sectional shape of the distal neck body 160 at the proximal section is round because the male friction fit portion is a conical tapered and the male friction fit portion neck 154 is a cylindrical hourglass shape. However, the shape of the distal neck body 160 at the proximal section can be other shape to correspond with the shape of the proximal male friction fit portion 150.
  • The flange portion 200 has an upper portion 210 on its proximal side that contacts at least a part of the distal neck body 160. In the embodiments shown in FIGS. 1, 2, 3, 6 and 7 the flange portion is angled to match the at the same angle as the calcar resection 12 made by the surgeon on the proximal femur 10. The angle and the size of the flange portion 200 are dependent on the anatomy of the patient and the morphology of the calcar resection 12. The flange portion 200 has an anterior-posterior flange portion width 240 that is wide enough to cover at least a portion of the cortical bone tissue 44 that has been resected. The cortical bone tissue 44 is more rigid than the cancellous bone tissue 3. In a healthy hip joint, the compressive loads are transmitted through both the cancellous bone tissue and the cortical bone tissue 44 of the proximal femur 10. Because the cortical bone tissue 44 is more dense and rigid, and can sustain a higher load per square unit area without fracture than the cancellous bone tissue 3, cortical bone tissue 44 is a more efficient distributor of compressive loads than cancellous bone tissue 3. Thus, the flanged portion 200 is shaped to cover both the resected cancellous bone 3 and the resected cortical bone 44 so that the compressive loads transmitted through the flange portion 200 are distributed as anatomically close as possible to how they were distributed when the proximal femur 10 was healthy and intact.
  • The flanged portion 200 is less thick than it is wide. As shown in the embodiment of FIG. 4, the flange portion thickness 221 is between 0.5 millimeters and 12 millimeters. The flange portion 200 is substantially thick enough to transmit loads from the hip joint to the calcar resection surface 12 of both the cancellous bone tissue 3 and the cortical bone tissue 44. The flange portion 200 is also thin enough to limit the about of bone that must be resected to form the calcar resection 12.
  • The transitional body region 300 is the portion of the femoral stem component 100 that transitions from the distal neck body 160 and the flange portion 200 to the distal elongated stem portion 400. The transitional body region 300 is adjacent to both the distal neck body 160 and the flange portion 200 on its proximal side and adjacent to the elongated stem portion 400 on its distal side. The transitional body portion 300 has a maximum height 310 that is the linear distance measured between a plane tangent to the bottom surface 220 of the flange portion 200 and a plane through the most distal part of the transitional body portion 300. In FIG. 4, these two planes are shown as lines since this is a side view. In the embodiment of the transitional body portion shown in FIG. 4, the transitional body portion 300 has a curved fillet 330 its medial side. Although this is shown as a round fillet in FIG. 4, the medial side of the transitional body portion 300 can be a chamfered fillet, a stepped fillet, or any other non-linear or linear shape that transitions from the shape of the elongated stem portion 400 to the shape of portions of the distal neck body 160 or the flange portion 200. The maximum height 310 of the majority of the transitional body region 300, when measured normal from the bottom surface 220 of the flange portion 200 to any part of the elongated stem portion 400 is less than thirteen millimeters or less. Both the physical structure of the femoral hip prosthesis 50, and the mechanical properties of the material from which the prosthesis is fabricated, function together to determine the functional strength and elasticity of the femoral stem component 100.
  • Conventional orthopedic alloys such as cobalt chrome, titanium and stainless steel alloys and orthopedic composite materials have proven to provide reasonable strength and rigidity to orthopedic implants and may also be used to fabricate the femoral stem component 100. However, when conventional orthopedic alloys or composites are fabricated into the eccentric conical shape of a typical femoral stem component 100, the resulting implant is more rigid than the proximal femoral 10 that the femoral stem component 100 is replacing. Flexibility of the stem component 100 is necessary to allow the flex and compliance desired to dynamically anatomically load the proximal femur 10 bone during biomechanical loading. The relatively small shape of the transitional body portion 300 allows for more flexion of the flange portion 200 when the proximal male friction fit portion 150 is loaded than is seen with the bulkier conventional eccentric cone shaped femoral prosthesis. The unique shape of the femoral stem component 100 allows for flexibility of the prosthesis even when fabricated from rigid orthopedic alloys such as such as cobalt chrome, titanium and stainless steel alloys.
  • This dynamic flexibility within the transitional portion 300 is desired since it allows the flange portion 200 of the femoral stem component 100 to transmit loads and displacements to the femoral calcar region 11 of the proximal femur 10. When bone is loaded and allowed to deform, a piezoelectric effect within the tissue simulate the bone cells into further production. This phenomenon, sometimes called Wolfs Law, coupled with other physiologic and biochemical principles, helps to keep the bone surrounding the femoral hip prosthesis 50 healthy and vibrant. The femoral stem component 100 is designed to optimize the effects that a flexible, yet strong femoral hip prosthesis 50 will have on the surrounding loaded bone tissue. As the hip joint is loaded during clinical use, loads are transmitted through the male friction fit portion 154 and distal neck body 160 to the flange portion 200 and the transitional body portion 300 to the stem. Since the transitional body portion 300 is relatively flexible and not as bulky and rigid as a conventional femoral hip prosthesis, the transitional body portion 300 allows the femoral stem component 100 to flex and transmit the compressive load to the bone in the calcar region 11 of the proximal femur 10. These loads on the bone may allow the dynamization necessary to keep the tissue surrounding the femoral stem component 100 healthy and help prevent bone resorption in the calcar region 11 of the proximal femur 10.
  • Distal and adjacent to the transitional body portion 300 is the elongated stem portion 400. The elongated stem portion 400 comprises some or all of the following portions and features; a tapered portion 450, a splined section 470, and transverse slot 480. The elongated stem portion is encompassed within a cylindrically shaped envelope referred to as uniform envelope 410. The cross-sectional shape and the area of the uniform envelope 410 remains substantially uniform throughout the longitudinal length of the elongated body. The uniform envelope 410 has a circular uniform cross-sectional periphery 902 that is defined by the maximum cross-sectional peripheral diameter 905 of the elongated stem portion 400. The uniform envelope 410 is the same length as the elongated stem portion. The elongated stem portion is adjacent to the transitional body portion 300 on its proximal end and adjacent to a distal tip portion 500 on its distal end.
  • As shown in FIG. 4, the elongated stem portion 400 is longitudinally aligned with a longitudinal axis 425. When the femoral stem component 100 is implanted in the proximal femur 10, the longitudinal axis 425 is approximately in alignment with the longitudinal axis 21 of the intramedullary cavity 25. All the possible features or portions of the elongated stem portion 400, including the tapered portion 450, the spine section 470, and the transverse slot 480 have cross-sections perpendicular to the longitudinal axis 425 and are contained within a maximum diameter 905 of a cross-sectional periphery 902 that defines the cross-section of the uniform envelope 410. Representative shapes of cross-sectional areas viewed from a cross-sectional view cut plane 900 are shown in FIG. 4 a through FIG. 4 e. Included in these figures are the cross-sectional periphery 902 and the maximum diameter 905 of the cross-sectional periphery 902.
  • Material may be removed from the elongated stem portion 400 to created features such as taper portions 450, splines 460 or the transverse slots 480. However, the basic substantial shape of the external periphery of the cross-section of the elongated stem portion 400 remains uniform and circular. Thus, the elongated stem portion and the uniform envelope 410 are both substantially symmetric and non-eccentric. The embodiment of the elongated stem portion 400 shown in FIG. 4 is substantially cylindrical in shape 910. The cross-section of this cylindrically shaped elongated stem portion is shown in FIG. 4 a. However, for other embodiments of the femoral stem component 100, the cross-sectional shape of the elongated stem portion 400 can be also non-circular shapes such as substantially square shape 920, as shown in FIG. 4 b; a substantially triangle shape 930, as shown in FIG. 4 c; a substantially hexagonal shape 940, as shown in FIG. 4 c, a substantially star shape 950 as shown in FIG. 4 e, or any other substantially non-eccentric, symmetric shape such as a tube (not shown) that can functionally form the cross-section of the elongated stem portion 400.
  • In the embodiments shown, the longitudinal axis 425 of the elongated stem portion 400 is a substantially straight axis throughout the length of the elongated stem portion 400. However, to better match the anatomy of the proximal femur 10, the longitudinal axis 425 can also be curved. The curve may be in the anterior-posterior plane, the medial-lateral plane or a compound curve that is seen in both the anterior-posterior plane and the medial-lateral plane. A flexible reamer (not shown) could be used to form the curved intramedullary cavity before the prosthesis 10 with a curved longitudinal axis 425 is implanted.
  • The elongated stem portion 400 may include a tapered portion 450 along its length. This is shown in FIG. 2. This tapered portion 450 may also include splines 460 or transverse slots 480 cut into it. The cross-sectional area of the tapered portion 450 in the embodiments shown decreases linearly along the longitudinal length of the tapered portion 450 as the tapered portion 450 transitions down the length of the elongated stem portion 400 from proximal to distal. The direction of the tapered portion 450 may also be in the opposite direction. The tapered area in the elongated portion 400 allows for greater flexibility in bending along the tapered portion 450 due to the reduced cross-sectional area and reduced cross-sectional bending moment of inertia. The tapered portion 450 also allows for an interference tapered wedge fit between the elongated stem portion 400 and the intramedullary cavity 25 in the proximal femur 10 when the cross-sectional size of the intramedullary canal 25 is less than the maximum diameter 905 of the periphery 902.
  • Features such the splines 460 are cut into the elongated stem portion 400 for various structural and functional reasons such as to provide additional torsional resistance to the femoral stem component 100. In the embodiments shown, the splines 460 are evenly spaced around the periphery 902 of the distal elongated stem portion 400. The splines 460 are cut longitudinal around the periphery 902 of the elongated stem portion 400. This allows the splines 460 to resist axial rotation between the femoral stem component 100 and the intramedullary cavity 25. The splines 460 may also provide additional structural flexibility to the distal end of the femoral stem component 100.
  • At the distal end of the femoral stem component 100, an optional longitudinal transverse slot 480 may be cut transversely into the elongated stem portion 400 to provide additional flexibility and potentially additional torsional resistance to the femoral stem component 100. The embodiment of the slot 480 that is shown is substantially uniform in cross-sectional and in shape though its length. The cross-sectional shape of the slot 480 may also be non-uniform. The cross-sections shape of the slot 480 may also change. For example the sides of the slot 481 may change from parallel planar surfaces to non-parallel or non-planar surfaces as the slot transitions from distal to proximal. The slot 480 also has a fillet 485 that takes the form of a rounded radius shape at its most proximal end. The shape of this fillet 485 may be other shapes that allow a relatively smooth transition from the slot 480 to the non-slotted cross-section. For example the slot 480 may be keyhole shaped.
  • Adjacent and distal to the elongated stem portion is the distal end tip portion 500. The distal end tip portion 500 has a lead-in section 510 that reduces in cross-sectional area from proximal to distal. The lead-in section may be tapered as in the embodiment of FIG. 3, or spherical as in the embodiment of FIG. 4, or any shape that is successively smaller in cross-sectional area from proximal to distal. The distal end tip portion 500 helps to guide the femoral stem component 100 into the intramedullary canal 25. The relatively smooth shape of the distal end tip portion 500 also functions to reduce the stress on the proximal femoral bone associated with discontinuity of terminating a rigid prosthesis in the intramedullary canal 25.
  • The load distribution on the proximal femur 10 of an intact hip joint can be essentially resolved into an axial component, a bending moment in the medial and lateral direction, a bending moment in the anterior posterior direction, and a torsional moment with a rotational axis approximately in line with the longitudinal axis 21 of the proximal femur. The distribution of the magnitude and direction of these force components depend upon complex combinations of biomechanical factors such as leg stance, patient weight distribution, and patient gait. The femoral stem component 100 is designed to translate these forces to anatomic loads on the proximal femur 10. As described above, the flange portion 200 helps to translate the compressive loads to the cancellous bone 3 and cortical bone 4 in the calcar region 11. The elongated stem portion 400 helps to transmit the bending and torsional moments to the intramedullary canal 25. In addition, a rotation-restricting boss 600 helps to transmit some of the torsional moments to the bone in the calcar region 11 of the proximal femur 10. As shown in FIG. 6, the boss periphery 630 of the rotation-restricting boss 600 interfaces with the bone surrounding the boss cavity 14. This structural interference between the femoral stem component 100 and the proximal femur 10 helps to restrict rotation, caused by the above-described resultant torsional moment with approximately in line with the longitudinal axis 21 of the proximal femur 10, between the femoral stem component 100 and the intramedullary cavity 25.
  • The size and location of the rotation-restricting boss 600 are factors that affect the amount that the rotation-restricting boss 600 restricts rotational movement of the femoral stem component 100. Due to greater resistance from a rotation-restricting boss with a larger resultant moment arm, the further that the rotation-restricting boss 600 is located from the longitudinal axis 425 of the elongated stem portion 400, the more effective it is in transmitting rotational loads and restricting rotational movement of the femoral stem component 100 to the proximal femur 10. Also, the larger the cross-sectional area of the rotation-restricting boss 600, the more effective it is in distributing torsion and restricting rotational movement of the femoral stem component 100.
  • The embodiments of the rotation-restricting boss 600 that are shown by example are circular in cross-section resulting in a cylindrical shaped boss. However, other cross-sectional shapes such as square, rectangular, triangular or diamond shapes may be more practical to machine or may be better at distributing torsional loads from the femoral hip prosthesis 50 to the proximal femur 10 than the shown cylindrically shaped rotation-restricting boss 600. The optimized shape of the rotation-restricting boss 600 may be more fin shaped than cylindrical shaped or longer than it is wide. This shape is partially dependent on the mechanical characteristics of the bone tissue where the rotation-restricing boss 600 is inserted.
  • The rotation restricting boss 600 has an axis of protrusion 620 with origin 621 substantially on a plane tangent or coincident with the bottom surface 220 of the flange portion 200. The boss axis of protrusion origin 621 and the stem portion longitudinal axis 425 are spaced apart by a length this is more than the maximum length 905 of the cross-section of the periphery 902 of the uniform envelope 410 of the elongated stem portion 400.
  • The rotation-restricting boss 600 in the embodiment of the prosthesis 10 shown in FIG. 3 has an axis of protrusion that is substantially normal to the bottom surface 220 of the flange portion 200. The rotation-restricting boss in the embodiment of the prosthesis 10 shown in FIG. 4, FIG. 5 and FIG. 6 has an axis of protrusion 620 that is substantially parallel with the longitudinal axis 425 of the elongated stem portion 400. As shown in cross-section of the proximal femur illustrated in FIG. 6, the corresponding boss cavity 14 is in line with the axis of protrusion 620.
  • As shown in FIG. 6 and FIG. 7, after the femoral stem component 100 is implanted in the proximal femur 10, the flange portion 200 is pressed against a resected surface 20 on the proximal femur 10, and the elongated stem portion 400 is pressed in the intramedullary cavity 25 aligned with the long axis of the proximal femur 10. As the femoral head 700 is loaded by the hip joint, a substantial component of the axial compressive force is transmitted to the cancellous 3 and cortical 4 bone in the calar region 11 from the flange portion 200. The principle torsional loads are transmitted to the splines 460, slot 480 and rotational-restricting boss 600 and the principle bending loads are transmitted to the intramedullary canal 25 through the elongated stem portion 400. Collectively, these feature and portions of the femoral hip prosthesis 10 contribute to distribute anatomical loads from hip joint to the remaining proximal femoral bone tissue.
  • While the present invention has been disclosed in its preferred form, the specific embodiments thereof as disclosed and illustrated herein are not to be considered in a limiting sense, as numerous variations are possible. The invention may be embodied in other specific forms without departing from its spirit or essential characteristics. The described embodiments are to be considered in all respects only as illustrative and not restrictive. No single feature, function, element or property of the disclosed embodiments is essential. The scope of the invention is, therefore, indicated by the appended claims rather than by the foregoing description. The following claims define certain combinations and subcombinations that are regarded as novel and non-obvious. Other combinations and subcombinations of features, functions, elements and/or properties may be claimed through amendment of the present claims or presentation of new claims in this or related applications. Such claims, whether they are broader, narrower or equal in scope to the original claims, are also regarded as included within the subject matter of applicant's invention. All changes that come within the meaning and range of equivalency of the claims are to be embraced within their scope.

Claims (18)

1. A prosthesis adapted for implantation against a resected surface on a proximal end of a femur and inside of an intramedullary cavity of the femur, the prosthesis comprising:
a femoral head component comprising an external bearing surface and a femoral stem component comprising:
a neck portion comprising a proximal portion, re-engageable with the femoral head component, and a distal neck body;
a flange portion distal and adjacent to the neck portion, the flange portion comprising a bottom surface;
a transitional body region adjacent to the bottom surface of the flange portion and extending from the distal neck body; and
an elongated stem portion extending distally from the transitional body region and having a longitudinal axis oriented at an acute angle from the bottom surface of the flange portion;
wherein the transitional body region shaped to flex such that, during a normal gait cycle, the bottom surface exerts a significant compressive load on the resected surface of the femur.
2. A prosthesis as is claim 1, wherein the elongated stem portion comprises a uniform envelope with a substantially constant cross-sectional peripheral shape and size.
3. A prosthesis as in claim 1, wherein the elongated stem portion comprises a proximal section having a cross sectional shape that is substantially consistent along a longitudinal length of the proximal section, wherein a minimum displacement between the bottom surface of the flange and the proximal section, measured normal to the bottom surface, is less than thirteen millimeters.
4. A prosthesis as in claim 1, further comprising a rotation-restricting boss, extending from the bottom of the flange portion.
5. A prosthesis as in claim 2, further comprising a rotation-restricting boss, extending from the bottom of the flange portion.
6. A prosthesis as in claim 5, wherein the rotation restricting boss has an axis of protrusion with a boss axis origin near the bottom surface of the flange, the elongated stem also has a stem axis origin near the bottom of the flange, the boss axis origin and the stem axis origin are spaced apart by a length more than the maximum cross-section of the elongated stem portion.
7. A prosthesis as in claim 6, wherein the axis of protrusion and the longitudinal axis are substantially parallel.
8. A prosthesis as in claim 6, wherein the axis of protrusion and the longitudinal axis are not substantially parallel.
9. A prosthesis as in claim 6, wherein the axis of protrusion is normal to the bottom surface of the flange portion.
10. A prosthesis as in claim 1, wherein the elongated stem portion has a distal section with multiple longitudinal flutes, wherein the longitudinal flutes are aligned approximately parallel to the longitudinal axis.
13. A prosthesis as in claim 12, wherein the obtuse angle is between 100° and 170°.
14. A prosthesis as in claim 1, wherein the neck portion has a first end and a second end, wherein the first end is connected to the flange portion and extends proximally therefrom and the second end is shaped to press-fit into the femoral head component.
15. A prosthesis as in claim 14, wherein at least a portion of the outer surface of the femoral head component is hemispherical.
16. A prosthesis as in clam 1, wherein the acute angle ranges from 15° to 80°.
17. A prosthesis as in claim 2, wherein the uniform envelope has a maximum cross-section area measured on a plane perpendicular to the longitudinal axis.
18. A prosthesis adapted for implantation against a resected surface on a proximal end of a femur and inside of a cavity of the femur, comprising:
a femoral head component comprising an external bearing; and
a femoral stem component comprising:
a neck portion shaped to extend substantially outside the cavity of the femur, the neck portion having a proximal portion, engageable with the femoral head component, and a distal neck body;
a flange portion medially and distally projecting from the neck body, the flange portion comprising a bottom surface;
an elongated stem portion shaped to extend substantially inside the cavity of the femur and extending distally from the neck body and having a longitudal axis oriented at an acute angle from the bottom surface of the flange portion
wherein, distally of a medial tip of the flange, each cross sectional shape along substantially an entire length of the elongated stem portion is substantially radially.
19. A prosthesis adapted for implantation against a resected surface on a proximal end of a femur and inside of a cavity of the femur, comprising:
a femoral head component comprising an external bearing surface; and
a femoral stem component comprising:
a neck portion shaped to extending substantially outside the cavity of the femur, the neck portion having a proximal portion, engageable with the femoral head component, and a distal neck body;
a flange portion medially and distally projecting from the neck body, the flange portion comprising a bottom surface;
an elongated stem portion shaped to extend substantially inside the cavity of the femur and extending distally from the neck body and having a longitudinal axis oriented at an acute angle from the bottom surface of the flange portion;
wherein, distally of a medial tip of the flange, substantially an entire length of the elongated stem portion circumscribed by a substantially cylindrical shape.
20. A prosthesis as in claim 1, wherein the elongated stem portion comprises a proximal section having a cross sectional shape that is substantially consistent along a longitudinal length of the proximal section, wherein a minimum displacement between the bottom surface of the flange and the proximal section, measured normal to the bottom surface, is less than a maximum cross sectional width of the elongated stem portion, measured perpendicular to the longitudinal axis.
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US12/429,882 Abandoned US20090216335A1 (en) 2004-01-22 2009-04-24 Femoral Hip Prosthesis and Method of Implantation
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US6592996B1 (en) 1998-02-06 2003-07-15 Nippon Sheet Glass Co., Ltd. Solar-shading light-transmissive panel and solar-shading multi-layer light-transmissive panel using same
GB0207170D0 (en) * 2002-03-26 2002-05-08 Mcminn Derek J W Hip joint prosthesis
US6986792B2 (en) * 2002-09-13 2006-01-17 Smith & Nephew, Inc. Prostheses
US7534271B2 (en) * 2004-01-22 2009-05-19 Smith + Nephew Femoral hip prosthesis and method of implantation
US7842096B2 (en) * 2005-02-22 2010-11-30 Zimmer Technology, Inc. Hip stem prosthesis
JP2008531089A (en) * 2005-02-22 2008-08-14 スミス アンド ネフュー インコーポレーテッド Long sleeve for stem
CA2664425A1 (en) * 2006-09-20 2008-03-27 Smith & Nephew, Inc. Variable stiffness stem for prosthetic implants
US7857859B2 (en) * 2007-06-13 2010-12-28 Zimmer, Gmbh Femur component for a hip joint prosthesis
WO2009009660A1 (en) 2007-07-11 2009-01-15 Daley M D Robert J Methods and apparatus for determining pin placement during hip surgery
US20100125303A1 (en) * 2008-11-20 2010-05-20 Daley Robert J Methods and apparatus for replacing biological joints using bone mineral substance in a suspended state
US20100125335A1 (en) * 2008-11-20 2010-05-20 Daley Robert J Methods and apparatus for replacing biological joints using bone cement in a suspended state
JP2012525942A (en) 2009-05-07 2012-10-25 スミス アンド ネフュー インコーポレーテッド Modular trial prosthesis head
CA2802099A1 (en) 2010-06-08 2011-12-15 Smith & Nephew, Inc. Implant components and methods
US9439781B2 (en) 2011-05-03 2016-09-13 Smith & Nephew, Inc. Patient-matched guides for orthopedic implants
US9101477B2 (en) * 2011-10-17 2015-08-11 Thomas Hatton McCoy Anterior offset component for total hip replacement
CA2858553C (en) 2011-12-07 2019-11-12 Smith & Nephew, Inc. Orthopedic augments having recessed pockets
CA2858559C (en) 2011-12-07 2021-04-20 Smith & Nephew, Inc. Orthopedic implant augments
US8992531B2 (en) 2011-12-16 2015-03-31 Chow Ip, Llc Prosthetic femoral stem for use in high impact hip replacement
US9301765B2 (en) 2011-12-16 2016-04-05 Chow Ip, Llc Prosthetic femoral stem for use in high offset hip replacement
ES2603562T3 (en) * 2012-09-21 2017-02-28 Waldemar Link Gmbh & Co. Kg Joint implant
CN103445885B (en) * 2013-07-02 2015-05-13 刘顺民 Femoral handle fixed through expansion
JP6554166B2 (en) * 2014-04-16 2019-07-31 オッセオインテグレーション ホールディングス プロプライエタリー リミテッド Osseo Integration-capable device
TWI634881B (en) * 2015-04-21 2018-09-11 寶楠生技股份有限公司 Femoral stem with cushion
CN106875489B (en) * 2017-02-20 2023-12-05 影为医疗科技(上海)有限公司 Construction method of individualized femur short handle
USD908880S1 (en) * 2017-11-15 2021-01-26 Joint Innovation Technology, Llc Revision stem and cup
JP1621250S (en) 2017-05-22 2018-12-25
USD881395S1 (en) * 2017-11-15 2020-04-14 Joint Innovation Technology, Llc Revision stem and ball
USD900317S1 (en) * 2017-11-15 2020-10-27 Joint Innovation Technology, Llc Revision stem
USD891615S1 (en) 2017-11-15 2020-07-28 Joint Innovation Technogy, Llc Revision stem
USD895116S1 (en) 2017-11-15 2020-09-01 Joint Innovation Technology, Llc Revision stem and cup
USD888958S1 (en) * 2017-11-15 2020-06-30 Joint Innovation Technology, Llc Revision stem and ball
CA3142938A1 (en) * 2019-06-12 2020-12-17 Government Of The United States Of America As Represented By The Department Of Veterans Affairs Femoral head arthroplasty system
US11364125B2 (en) 2019-07-08 2022-06-21 Howmedica Osteonics Corp. Tapered stem with anti-rotation features
US20220249140A1 (en) * 2021-02-11 2022-08-11 Biomet Manufacturing, Llc Transition region in intramedullary portion of prosthesis
IT202100013841A1 (en) * 2021-05-27 2022-11-27 Mt Ortho S R L Intraosseous tap with triangular section for biomedical applications and fixing kit comprising said tap
CN114112746B (en) * 2021-11-14 2022-07-08 合肥熠品医药科技有限公司 Hip joint femoral stem fatigue test loading device
CN116327451B (en) * 2023-05-26 2023-08-04 北京纳通医疗科技控股有限公司 Femoral stem prosthesis
CN117159234A (en) * 2023-11-03 2023-12-05 北京爱康宜诚医疗器材有限公司 Joint implant

Citations (96)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3512184A (en) * 1968-02-19 1970-05-19 Ned M Grove Hip prosthesis
US3658056A (en) * 1968-04-25 1972-04-25 Arnold H Huggler Hip joint prosthesis
US3782373A (en) * 1972-05-22 1974-01-01 Orthopedic Equipment Co Drill jig for a femoral prosthesis
US3864758A (en) * 1973-08-31 1975-02-11 Sam Savo Yakich Hip joint bearing prosthesis
US3871031A (en) * 1971-12-03 1975-03-18 Ceraver Total hip prosthetic apparatus made of non-porous alumina
US4001897A (en) * 1975-01-31 1977-01-11 Andre Rambert Prosthesis for a joint
US4005495A (en) * 1975-08-09 1977-02-01 Rosenthal Technik Ag Ceramic cap bone prosthesis and method of implantation
US4012796A (en) * 1975-09-24 1977-03-22 Howmedica, Inc. Interpositioning collar for prosthetic bone insert
US4012795A (en) * 1974-10-29 1977-03-22 Feldmuhle Anlagen- Und Produktionsgesellschaft Mit Beschrankter Haftung Artificial head assembly for an articulated joint between two bones
US4021865A (en) * 1974-08-29 1977-05-10 John Charnley Femoral prosthesis
US4080666A (en) * 1976-09-13 1978-03-28 Fixel Irving E Implantable prosthetic bone device
US4187559A (en) * 1975-04-04 1980-02-12 Sybron Corporation Body joint endoprosthesis
US4274164A (en) * 1978-08-04 1981-06-23 Orthoplant Orthopadische Implantate Gmbh & Co. Kg Endoprosthesis for a hip joint, especially for the hip joint of a human being
US4312079A (en) * 1979-04-11 1982-01-26 Feldmuhle Aktiengesellschaft Femur head cap for endoprosthesis
US4314381A (en) * 1980-06-25 1982-02-09 Lord Corporation Hip joint prosthesis
US4645506A (en) * 1983-06-27 1987-02-24 Waldemar Link Gmbh & Co. Hip joint endoprosthesis with a stem to be anchored in the femur
US4661112A (en) * 1984-03-06 1987-04-28 Sulzer Brothers Limited Hip joint prosthesis
US4664668A (en) * 1984-04-14 1987-05-12 Howmedica International, Inc. Hip joint prosthesis
US4718912A (en) * 1985-11-12 1988-01-12 Zimmer Inc. Femoral component and the method of constructing the same
US4718916A (en) * 1985-06-12 1988-01-12 Sulzer Brothers Ltd. Femur head prosthesis
US4728335A (en) * 1986-12-15 1988-03-01 Jurgutis John A Hip prosthesis
US4728334A (en) * 1983-08-29 1988-03-01 Protek Ag Shaft for hip joint prosthesis
US4731088A (en) * 1986-06-02 1988-03-15 Boehringer Mannheim Corp Enclosure member for prosthetic joint
US4795473A (en) * 1987-01-09 1989-01-03 Grimes James B Extramedullary femoral head-neck prosthesis and method of implanting same
US4795472A (en) * 1987-01-28 1989-01-03 Zimmer, Inc. Prosthesis with enhanced surface finish
US4822368A (en) * 1986-06-02 1989-04-18 Boehringer Mannheim Corporation Sugical method of attaching enclosure member for prosthetic joint
US4892551A (en) * 1986-07-03 1990-01-09 Habley Medical Technology Corporation Impact dissipating and load diverting total hip arthroplasty prosthesis
US4904268A (en) * 1988-09-12 1990-02-27 Alfredo Alvarado Prosthetic device
US4904266A (en) * 1988-06-27 1990-02-27 Barber Forrest C Bone joint implant and method
US4908034A (en) * 1983-12-01 1990-03-13 National Research Development Corporation Endoprosthetic bone joint components
US4908036A (en) * 1987-06-15 1990-03-13 Waldemar Link Gmbh & Co. Endoprosthesis
US4911722A (en) * 1986-08-25 1990-03-27 Office Medico Chirurgical International S.A. (O.M.C.I.) Mechanical self locking femoral prosthesis and a method for implementing same
US4986834A (en) * 1988-08-31 1991-01-22 Boehringer Mannheim Corporation Load sharing femoral hip implant
US4995883A (en) * 1989-02-08 1991-02-26 Smith & Nephew Richards Inc. Modular hip prosthesis
US5002579A (en) * 1986-05-16 1991-03-26 Franz Copf Prosthesis component and method for its manufacture
US5002580A (en) * 1988-10-07 1991-03-26 Pfizer Hospital Products Group, Inc. Prosthetic device and method of implantation
US5002578A (en) * 1990-05-04 1991-03-26 Venus Corporation Modular hip stem prosthesis apparatus and method
US5002581A (en) * 1989-11-03 1991-03-26 Dow Corning Wright Corporation Modular hip joint prosthesis with adjustable anteversion
US5004476A (en) * 1989-10-31 1991-04-02 Tulane University Porous coated total hip replacement system
US5007935A (en) * 1985-01-11 1991-04-16 S. A. Manufacture Belge De Gembloux Joint member for a hip prosthesis
US5080685A (en) * 1986-08-15 1992-01-14 Boehringer Mannheim Corporation Modular hip prosthesis
US5087260A (en) * 1989-09-15 1992-02-11 Fixel Irving E Total femoral hip system
US5108451A (en) * 1991-01-31 1992-04-28 Forte Mark R Femoral component of a hip joint prosthesis
US5108452A (en) * 1989-02-08 1992-04-28 Smith & Nephew Richards Inc. Modular hip prosthesis
US5116377A (en) * 1989-04-15 1992-05-26 Bristol-Myers Squibb Company Cementable hip prosthesis
US5116380A (en) * 1991-02-28 1992-05-26 Zimmer, Inc. Prosthetic implant with spacers having tapered trailing edges
US5181928A (en) * 1986-08-15 1993-01-26 Boehringer Mannheim Corporation Modular hip prosthesis
US5197989A (en) * 1987-09-03 1993-03-30 Hinckfuss Bruce W Two stage joint prosthesis
US5197988A (en) * 1989-06-21 1993-03-30 Sulzer Brothers Limited Femoral prosthesis
US5197990A (en) * 1990-05-17 1993-03-30 Howmedica International, Inc. Prosthetic intramedullary femoral prosthesis with preformed sheath
US5201882A (en) * 1989-11-03 1993-04-13 Paxson Robert D Modular hip joint prosthesis with adjustable anteversion
US5201771A (en) * 1989-09-15 1993-04-13 Belykh Sergei I Endoprosthesis of the hip joint
US5314489A (en) * 1991-09-30 1994-05-24 Johnson & Johnson Orthopaedics, Inc. Hip prosthesis
US5387244A (en) * 1988-10-28 1995-02-07 Science Et Medecine (Sem) Artificial hip joint
US5389107A (en) * 1992-05-11 1995-02-14 Antoine A. Nassar Shock absorbent prosthetic hip joint
US5480453A (en) * 1992-11-20 1996-01-02 Burke; Dennis W. Collar for femoral implant and method and apparatus for installation thereof
US5480452A (en) * 1992-05-29 1996-01-02 Intermedics Orthopedics, Inc. Femoral prosthesis with wedge having opposed tapers
US5507814A (en) * 1994-03-30 1996-04-16 Northwestern University Orthopedic implant with self-reinforced mantle
US5514184A (en) * 1993-05-26 1996-05-07 Kabushiki Kaisha Kobe Seiko Sho Artificial joint having porous portion
US5514182A (en) * 1993-08-17 1996-05-07 University Of Utah Prosthetic joint with semipermeable capsule with reinforcing ribs
US5591233A (en) * 1990-06-01 1997-01-07 Depuy Dupont Orthopaedics Metal/composite hybrid orthopedic implants
US5725592A (en) * 1996-10-29 1998-03-10 Hayes Medical, Inc. Modular prosthesis having neck component connected to stem component through cavity in body component
US5725590A (en) * 1993-08-30 1998-03-10 Sulzer Medizinaltechnik Ag Element for temporarily increasing the rigidity of an orthopaedic prosthesis
US5725595A (en) * 1994-11-08 1998-03-10 Orthopaedic Innovations, Inc. Cannulated cementless hip stem prosthesis
US5725593A (en) * 1995-02-22 1998-03-10 Caracciolo; Francesco Total anatomic hip prosthesis
US5725594A (en) * 1994-07-14 1998-03-10 Ortho Development Corporation Proximal conical stem
US5746771A (en) * 1996-09-30 1998-05-05 Wright Medical Technology, Inc. Calcar collar instrumentation
US5755807A (en) * 1996-06-17 1998-05-26 Folsom Metal Products Implant module unit and rotating seal for prosthetic joint
US5858020A (en) * 1995-12-05 1999-01-12 Metagen, Llc Modular prosthesis
US5861042A (en) * 1990-09-17 1999-01-19 Buechel; Frederick F. Prosthesis with biologically inert wear resistant surface
US5876459A (en) * 1996-08-30 1999-03-02 Powell; Douglas Hunter Adjustable modular orthopedic implant
US5888208A (en) * 1997-03-26 1999-03-30 Johnson & Johnson Professional, Inc. Modular hip trial for long stems
US5906644A (en) * 1996-08-30 1999-05-25 Powell; Douglas Hunter Adjustable modular orthopedic implant
US6010535A (en) * 1998-04-30 2000-01-04 Shah; Mrugesh K. Joint replacement system
US6179877B1 (en) * 1992-11-20 2001-01-30 Dennis W. Burke Centering device for femoral implant and method and apparatus for implementation thereof
US6193761B1 (en) * 1995-07-07 2001-02-27 Depuy Orthopaedics, Inc. Implantable prosthesis with metallic porous bead preforms applied during casting
US6197065B1 (en) * 1993-11-01 2001-03-06 Biomet, Inc. Method and apparatus for segmental bone replacement
US6231611B1 (en) * 1996-06-14 2001-05-15 Raphael Mosseri Total hip prosthesis for endo-articular implantation, and ancillary device therefor
US6379390B1 (en) * 1999-06-23 2002-04-30 The University Of Delaware Stemless hip prosthesis
US6383226B1 (en) * 1998-06-09 2002-05-07 The Board Of Trustees Of The Leland Stanford Junior University Prostheses having curvilinear collars
US6383227B1 (en) * 1998-07-30 2002-05-07 Aap Implanters Ag Femoral neck endoprosthesis for an artificial hip joint
US6395004B1 (en) * 1997-11-14 2002-05-28 Sulzer Orthopedics Inc. Orthopedic trial prosthesis and saw guide instrument
US6503281B1 (en) * 2000-08-25 2003-01-07 Thomas H. Mallory Total hip replacement
US20030014123A1 (en) * 2001-05-18 2003-01-16 Peter Copf Cementless hip joint endoprosthesis as a surface replacement for the proximal femur
US6514288B2 (en) * 2001-02-23 2003-02-04 Zimmer, Inc. Prosthetic stem with strengthening rib
US20030033020A1 (en) * 2001-06-01 2003-02-13 Gordon Hunter Prosthetic devices employing contacting oxidized zirconium surfaces
US6524343B2 (en) * 2000-03-27 2003-02-25 Benoist Girard Sas Femoral hip prosthesis
US20030045941A1 (en) * 2001-08-27 2003-03-06 Lewallen David G. Coated prosthetic implant
US20030050704A1 (en) * 2000-01-03 2003-03-13 Ory Keynan Prosthesis
US20030060891A1 (en) * 2001-09-27 2003-03-27 Shah Mrugesh K. Hip replacement system having fat lubricant
US20030065397A1 (en) * 2001-08-27 2003-04-03 Hanssen Arlen D. Prosthetic implant support structure
US20030074079A1 (en) * 1998-04-14 2003-04-17 Osteoimplant Technology, Inc. Differential porosity prosthetic hip system
US20030074080A1 (en) * 1998-04-14 2003-04-17 Murray Ian P. Modular neck for femur replacement surgery
US20030078670A1 (en) * 2001-10-24 2003-04-24 Grimes James B. Prosthesis
US20030088316A1 (en) * 2001-11-05 2003-05-08 Ramin Ganjianpour Modular femoral prosthesis
US7534271B2 (en) * 2004-01-22 2009-05-19 Smith + Nephew Femoral hip prosthesis and method of implantation

Family Cites Families (122)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US171819A (en) * 1876-01-04 Improvement in slide-valves for steam-engines
US3683421A (en) 1970-07-13 1972-08-15 Skf Ind Inc Prosthetic joint assembly
US3848272A (en) 1972-01-13 1974-11-19 United States Surgical Corp Artificial hip joint
CH568753A5 (en) 1973-08-31 1975-11-14 Oscobal Ag
US3916451A (en) 1974-10-25 1975-11-04 Frederick F Buechel Floating center prosthetic joint
DE2514793C3 (en) * 1975-04-04 1980-06-19 Pfaudler-Werke Ag, 6830 Schwetzingen Joint endoprosthesis
CH602091A5 (en) 1976-06-03 1978-07-31 Huggler Arnold
CH612585A5 (en) 1977-05-23 1979-08-15 Sulzer Ag
CH642251A5 (en) 1979-12-22 1984-04-13 Straumann Inst Ag BALL JOINT PROSTHESIS WITH A CAP.
US4454612A (en) 1980-05-07 1984-06-19 Biomet, Inc. Prosthesis formation having solid and porous polymeric components
EP0069252B1 (en) 1981-06-30 1986-10-22 Waldemar Link (GmbH & Co.) Joint endoprosthesis
US4770661A (en) 1982-01-18 1988-09-13 Indong Oh Conversion femoral endoprosthesis
US4549319A (en) 1982-08-03 1985-10-29 United States Medical Corporation Artificial joint fixation to bone
JPS58163355A (en) * 1982-03-20 1983-09-28 有限会社 友信開発 Support material for artificial joint
IE54180B1 (en) * 1982-04-19 1989-07-05 Vitek Inc Articulating joint prostheses
US4851004A (en) 1982-04-19 1989-07-25 Homsy Charles A Implantation of articulating joint prosthesis
US5222985B1 (en) 1982-04-19 2000-10-24 Tranguil Prospects Ltd Implantation of articulating joint prosthesis
US4532661A (en) 1982-05-07 1985-08-06 Halpern Alan A Femoral head remodeling and prosthetic means therefor
FR2529077B1 (en) 1982-06-29 1985-01-18 Lord Gerald NEW BONE PROSTHESIS AND ITS OBTAINMENT
US4530114A (en) 1982-07-16 1985-07-23 Slobodan Tepic Total hip joint prostheses
USRE32488E (en) 1982-09-28 1987-09-01 Hip prosthesis
US4546501A (en) 1982-09-28 1985-10-15 Gustilo Ramon B Hip prosthesis
FR2537868B3 (en) 1982-12-20 1985-10-11 Richards France Sarl PROSTHESIS FOR REPLACING THE HIP JOINT
US4488320A (en) 1983-01-10 1984-12-18 Medical Center Prosthetics, Inc. Prosthetic hip
CA1240101A (en) 1983-05-06 1988-08-09 Michael J. Pappas Multi-component prosthesis with increased wall flexibility facilitating component assembly
US4752296A (en) 1983-05-06 1988-06-21 Buechel Frederick F Prosthesis with interlocking fixation and providing reduction of stress shielding
DE3334058C2 (en) 1983-09-21 1985-07-25 Ulrich Dr.-Ing. 5600 Wuppertal Witzel Thigh section for a hip joint prosthesis
US4608055A (en) 1984-01-12 1986-08-26 Mayo Foundation Femoral component for hip prosthesis
US5047062A (en) 1984-01-26 1991-09-10 Pappas Michael J Femoral stem-type prosthesis
US4846839A (en) 1984-02-09 1989-07-11 Joint Medical Products Corporation Apparatus for affixing a prosthesis to bone
US4840632A (en) 1984-03-16 1989-06-20 Kampner Stanley L Hip prosthesis
GB8409714D0 (en) 1984-04-13 1984-05-23 Finsbury Instr Ltd Hip implant
KR850001814B1 (en) * 1984-04-17 1985-12-23 한국과학기술원 Artificial joints
US4608052A (en) 1984-04-25 1986-08-26 Minnesota Mining And Manufacturing Company Implant with attachment surface
US4686971A (en) 1984-11-19 1987-08-18 Harris William H Method and apparatus for extraction of prostheses
FR2576777B1 (en) 1985-01-31 1987-03-06 Rhenter Jean Luc TOTAL HIP PROSTHESIS WITH PRIMARY FIXING
US4775381A (en) 1985-05-06 1988-10-04 Metripond Merleggyar Hip prosthesis
US4750905A (en) 1985-07-10 1988-06-14 Harrington Arthritis Research Center Beam construction and method
US4738681A (en) 1985-07-10 1988-04-19 Harrington Arthritis Research Center Femoral-joint prosthetic device
US4888024A (en) 1985-11-08 1989-12-19 Powlan Roy Y Prosthetic device and method of fixation within the medullary cavity of bones
DE8611697U1 (en) 1986-04-25 1986-06-19 Mecron Medizinische Produkte Gmbh, 1000 Berlin Kit for a stem prosthesis
US4846841A (en) 1986-04-25 1989-07-11 Indong Oh Femoral Prosthesis
US4681590A (en) 1986-06-18 1987-07-21 John Tansey Femoral stem prosthesis
US4846840A (en) 1986-09-09 1989-07-11 Sylvain Leclercq Joint prosthesis
US4790852A (en) 1986-09-15 1988-12-13 Joint Medical Products Corporation Sleeves for affixing artificial joints to bone
EP0265712A1 (en) 1986-10-16 1988-05-04 Protek AG Acetabular component for a total hip prosthesis
US4778469A (en) 1986-11-04 1988-10-18 Pfizer Hospital Products Group Inc. Method of forming tissue ingrowth surface on surgical implants
US4770660A (en) 1987-01-20 1988-09-13 Osteonics Corp. Femoral prosthesis with selectively removable collar
US4881536A (en) 1987-01-22 1989-11-21 Noble Phillip C Method and apparatus for prosthesis placement
DE8712578U1 (en) 1987-09-17 1987-12-17 Howmedica Gmbh, 2314 Schoenkirchen, De
US4871369A (en) 1987-11-23 1989-10-03 Pfizer Hospital Products Group, Inc. Long stem hip implant
US4888023B1 (en) 1988-01-19 1996-01-23 Osteonics Corp Femoral prosthesis with uncoupled distal tip
US4851008A (en) 1988-02-01 1989-07-25 Orthomet, Inc. Bone implant prosthesis with substantially stress-free outer surface
US4851007A (en) 1988-03-18 1989-07-25 Gray Frank B Femoral component for a hip prosthesis
CA1304889C (en) 1988-05-12 1992-07-14 Peter John Brooks Femoral insert
US4936863A (en) 1988-05-13 1990-06-26 Hofmann Aaron A Hip prosthesis
US5658352A (en) 1988-09-09 1997-08-19 Draenert; Klaus Hip prosthesis and its use
CH676664A5 (en) 1989-01-10 1991-02-28 Sulzer Ag
US4938773A (en) 1989-01-18 1990-07-03 Strand John A Hip joint prosthesis
NL8901526A (en) 1989-06-16 1991-01-16 Ordev Bv SELF-ADJUSTING PROSTHESIS CONFIRMATION.
US4976740A (en) 1989-07-14 1990-12-11 Kleiner Jeffrey B Anchored femoral dome
US5152795A (en) 1990-04-25 1992-10-06 Spire Corporation Surgical implants and method
ATE89991T1 (en) 1989-10-04 1993-06-15 S & G Implants Gmbh FEMUR HIP REPLACEMENT.
US5030234A (en) 1989-12-12 1991-07-09 Pappas Michael J Prosthetic device with modular stem
JP2990531B2 (en) * 1990-07-31 1999-12-13 京セラ株式会社 Hip prosthesis
US5057101A (en) 1990-08-01 1991-10-15 Intermedics Orthopedics, Inc. Femoral prosthesis with centering sleeve
GB9017402D0 (en) 1990-08-08 1990-09-19 Howmedica Total hip replacement femoral component
US5702448A (en) 1990-09-17 1997-12-30 Buechel; Frederick F. Prosthesis with biologically inert wear resistant surface
US5246461A (en) 1990-11-27 1993-09-21 Laboratorium fur experimentelle Chirurgie, Forschungsinstitut, Davos Femoral twin-set for a hip endoprosthesis
AT398529B (en) 1991-01-25 1994-12-27 Winkler Heinz Dr ENDOPROTHESIS, ESPECIALLY THE HIP JOINT
US5163963A (en) 1991-02-28 1992-11-17 Zimmer, Inc. Prosthetic implant with spacers having tapered trailing edges
US5133766A (en) 1991-03-04 1992-07-28 Halpern Alan A Femoral head remodeling and femoral insert and drilling aid therefor
FR2674744B1 (en) * 1991-04-02 1998-11-06 Fabrication Etu Realisa Implan FEMALE RECOVERY ROD.
US5163964A (en) 1991-06-26 1992-11-17 Zimmer, Inc. Orthopaedic prosthesis with access in collar
EP0523926A3 (en) 1991-07-15 1993-12-01 Smith & Nephew Richards Inc Prosthetic implants with bioabsorbable coating
SE9102216D0 (en) 1991-07-23 1991-07-23 Astra Ab HIP JOINT PROSTHESIS
US5156624A (en) 1991-09-06 1992-10-20 Zimmer, Inc. Head adaptor for hip prosthesis
US5201769A (en) * 1991-09-23 1993-04-13 Schutzer Steven F Hip stem with proximal build-up blocks
EP0607287B1 (en) 1991-10-07 1999-01-13 Boehringer Mannheim Corporation Reduced stiffness femoral hip implant
SE9200597D0 (en) 1992-02-28 1992-02-28 Astra Ab HIP JOINT PROSTHESIS II
US5814050A (en) 1992-05-14 1998-09-29 Bentwood Place, Inc. Hip offset-inset apparatus and method
US5954771A (en) 1993-02-16 1999-09-21 Wright Medical Technology, Inc. Dual fixation prosthesis
US5571203A (en) 1993-06-18 1996-11-05 Masini; Michael A. Bone-conserving hip system
US5458654A (en) 1993-07-14 1995-10-17 Ao-Forschungsinstitut Davos Screw-fixed femoral component for hip joint prosthesis
US5376124A (en) 1993-08-03 1994-12-27 Intermedics Orthopedics, Inc. Collared hip prosthesis with revision spacer
US5468243A (en) 1993-10-27 1995-11-21 Halpern; Alan A. Femoral superior neck remodelling means and method
US5376126A (en) 1993-11-12 1994-12-27 Lin; Chih-I Artificial acetabular joint replacing device
US5653764A (en) 1994-02-17 1997-08-05 Murphy; Stephen B. Modular hip prosthesis with discrete selectable angular orientation
US5593451A (en) 1994-06-01 1997-01-14 Implex Corp. Prosthetic device and method of implantation
DE69510675T2 (en) 1994-06-30 2000-04-06 Stryker Technologies Corp MODULAR, FEMURAL HIP JOINT SYSTEM
US5653765A (en) 1994-07-01 1997-08-05 Ortho Development Corporation Modular prosthesis
US6290726B1 (en) 2000-01-30 2001-09-18 Diamicron, Inc. Prosthetic hip joint having sintered polycrystalline diamond compact articulation surfaces
CH689725A5 (en) 1994-09-08 1999-09-30 Franz Dr Sutter Condyle prosthesis.
US5702483A (en) 1994-10-06 1997-12-30 Kwong; Louis M. Debris isolating prosthetic hip joint
US5571195A (en) 1995-05-30 1996-11-05 Johnson; Lanny L. Prothesis for an artificial joint having a wear particle collection capability
US20020143402A1 (en) 1995-09-04 2002-10-03 Limber Ltd. Hip joint prostheses
US20020156536A1 (en) 1996-02-13 2002-10-24 Harris William H. Polyethylene hip joint prosthesis with extended range of motion
WO2000048535A1 (en) 1999-02-19 2000-08-24 Grimes James B Bone prosthesis and method of implantation
US6273915B1 (en) 1996-08-13 2001-08-14 James B. Grimes Femoral head-neck prosthesis and method of implantation
US20020072805A1 (en) 1996-08-21 2002-06-13 Sullivan John Martin Patrick Joint replacement prosthesis
US6413280B1 (en) 1996-10-04 2002-07-02 Frederic C. Feiler Hip joint prosthesis
US6371991B1 (en) * 1996-12-23 2002-04-16 Depuy Orthopaedics, Inc. Alignment guide for fluted prosthetic stems
US6120544A (en) 1997-05-16 2000-09-19 Eska Implants Gmbh & Co. Femur endoprosthesis for articial hip joint
US6428578B2 (en) 1998-03-18 2002-08-06 Sct Incorporated Modular prosthesis and connector therefor
WO2000057820A1 (en) 1999-03-31 2000-10-05 Stocks Gregory W Joint prosthesis assembly and method for installing same
US6284002B1 (en) 1999-05-27 2001-09-04 Nicholas G. Sotereanos Proximal femoral replacement implant and method of implanting the same
US6221074B1 (en) 1999-06-10 2001-04-24 Orthodyne, Inc. Femoral intramedullary rod system
US6488716B1 (en) 1999-07-30 2002-12-03 Guofu Huang Anatomic femoral prosthesis for total hip arthroplasty
EP1106143B1 (en) 1999-12-02 2004-05-26 WALDEMAR LINK GmbH & Co. KG Prosthetic system
US6610095B1 (en) 2000-01-30 2003-08-26 Diamicron, Inc. Prosthetic joint having substrate surface topographical featurers and at least one diamond articulation surface
US6524243B1 (en) * 2000-10-04 2003-02-25 Jordan Technology Inc. Tonometer incorporating an electrical measurement device
NL1016551C2 (en) 2000-11-07 2002-05-14 Erik Leonard Hoffman Fastening element, for hip prosthesis, has plate-shaped supporting element, and hollow pin driven into spongy bone, and secured by fixing plate and openings through which bone can grow
US20020111692A1 (en) 2001-02-15 2002-08-15 Ralph James D. Artificial hip having a femoral stem portion which provides for micromovement
US6616697B2 (en) 2001-03-13 2003-09-09 Nicholas G. Sotereanos Hip implant assembly
US7261741B2 (en) 2001-06-30 2007-08-28 Depuy Products, Inc. Prosthesis with resorbable collar
US6953479B2 (en) 2001-07-16 2005-10-11 Smith & Nephew, Inc. Orthopedic implant extension
ATE376817T1 (en) * 2001-09-10 2007-11-15 Zimmer Gmbh FEMORAL NECK PROSTHESIS
US7247171B2 (en) 2002-03-11 2007-07-24 Sotereanos Nicholas G Modular hip implants
US20040054419A1 (en) 2002-05-09 2004-03-18 Serra Michael A. System for trial implantation of a femoral hip prosthesis
US7931687B2 (en) 2002-05-13 2011-04-26 Articular Engineering, Llc Tissue engineered osteochondral implant
US7935118B2 (en) * 2002-06-21 2011-05-03 Depuy Products, Inc. Prosthesis removal cutting guide, cutting tool and method
FR2856275B1 (en) * 2003-06-19 2006-02-10 Didier Ravet ANATOMIC FEMALE ROD FOR HIP PROSTHESIS

Patent Citations (99)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3512184A (en) * 1968-02-19 1970-05-19 Ned M Grove Hip prosthesis
US3658056A (en) * 1968-04-25 1972-04-25 Arnold H Huggler Hip joint prosthesis
US3871031A (en) * 1971-12-03 1975-03-18 Ceraver Total hip prosthetic apparatus made of non-porous alumina
US3782373A (en) * 1972-05-22 1974-01-01 Orthopedic Equipment Co Drill jig for a femoral prosthesis
US3864758A (en) * 1973-08-31 1975-02-11 Sam Savo Yakich Hip joint bearing prosthesis
US4021865A (en) * 1974-08-29 1977-05-10 John Charnley Femoral prosthesis
US4012795A (en) * 1974-10-29 1977-03-22 Feldmuhle Anlagen- Und Produktionsgesellschaft Mit Beschrankter Haftung Artificial head assembly for an articulated joint between two bones
US4001897A (en) * 1975-01-31 1977-01-11 Andre Rambert Prosthesis for a joint
US4187559A (en) * 1975-04-04 1980-02-12 Sybron Corporation Body joint endoprosthesis
US4005495A (en) * 1975-08-09 1977-02-01 Rosenthal Technik Ag Ceramic cap bone prosthesis and method of implantation
US4012796A (en) * 1975-09-24 1977-03-22 Howmedica, Inc. Interpositioning collar for prosthetic bone insert
US4080666A (en) * 1976-09-13 1978-03-28 Fixel Irving E Implantable prosthetic bone device
US4274164A (en) * 1978-08-04 1981-06-23 Orthoplant Orthopadische Implantate Gmbh & Co. Kg Endoprosthesis for a hip joint, especially for the hip joint of a human being
US4312079A (en) * 1979-04-11 1982-01-26 Feldmuhle Aktiengesellschaft Femur head cap for endoprosthesis
US4314381A (en) * 1980-06-25 1982-02-09 Lord Corporation Hip joint prosthesis
US4645506A (en) * 1983-06-27 1987-02-24 Waldemar Link Gmbh & Co. Hip joint endoprosthesis with a stem to be anchored in the femur
US4728334A (en) * 1983-08-29 1988-03-01 Protek Ag Shaft for hip joint prosthesis
US4908034A (en) * 1983-12-01 1990-03-13 National Research Development Corporation Endoprosthetic bone joint components
US4661112A (en) * 1984-03-06 1987-04-28 Sulzer Brothers Limited Hip joint prosthesis
US4664668A (en) * 1984-04-14 1987-05-12 Howmedica International, Inc. Hip joint prosthesis
US5007935A (en) * 1985-01-11 1991-04-16 S. A. Manufacture Belge De Gembloux Joint member for a hip prosthesis
US4718916A (en) * 1985-06-12 1988-01-12 Sulzer Brothers Ltd. Femur head prosthesis
US4718912A (en) * 1985-11-12 1988-01-12 Zimmer Inc. Femoral component and the method of constructing the same
US5002579A (en) * 1986-05-16 1991-03-26 Franz Copf Prosthesis component and method for its manufacture
US4731088A (en) * 1986-06-02 1988-03-15 Boehringer Mannheim Corp Enclosure member for prosthetic joint
US4822368A (en) * 1986-06-02 1989-04-18 Boehringer Mannheim Corporation Sugical method of attaching enclosure member for prosthetic joint
US4892551A (en) * 1986-07-03 1990-01-09 Habley Medical Technology Corporation Impact dissipating and load diverting total hip arthroplasty prosthesis
US5181928A (en) * 1986-08-15 1993-01-26 Boehringer Mannheim Corporation Modular hip prosthesis
US5286260A (en) * 1986-08-15 1994-02-15 Depuy Inc. Modular hip prosthesis
US5080685A (en) * 1986-08-15 1992-01-14 Boehringer Mannheim Corporation Modular hip prosthesis
US4911722A (en) * 1986-08-25 1990-03-27 Office Medico Chirurgical International S.A. (O.M.C.I.) Mechanical self locking femoral prosthesis and a method for implementing same
US4728335A (en) * 1986-12-15 1988-03-01 Jurgutis John A Hip prosthesis
US4795473A (en) * 1987-01-09 1989-01-03 Grimes James B Extramedullary femoral head-neck prosthesis and method of implanting same
US4998937A (en) * 1987-01-09 1991-03-12 Grimes James B Method of implanting extramedullary femoral head-neck prosthesis
US4795472A (en) * 1987-01-28 1989-01-03 Zimmer, Inc. Prosthesis with enhanced surface finish
US4908036A (en) * 1987-06-15 1990-03-13 Waldemar Link Gmbh & Co. Endoprosthesis
US5197989A (en) * 1987-09-03 1993-03-30 Hinckfuss Bruce W Two stage joint prosthesis
US4904266A (en) * 1988-06-27 1990-02-27 Barber Forrest C Bone joint implant and method
US4986834A (en) * 1988-08-31 1991-01-22 Boehringer Mannheim Corporation Load sharing femoral hip implant
US4904268A (en) * 1988-09-12 1990-02-27 Alfredo Alvarado Prosthetic device
US5002580A (en) * 1988-10-07 1991-03-26 Pfizer Hospital Products Group, Inc. Prosthetic device and method of implantation
US5387244A (en) * 1988-10-28 1995-02-07 Science Et Medecine (Sem) Artificial hip joint
US5507830A (en) * 1989-02-08 1996-04-16 Smith & Nephew Richards Inc. Modular hip prosthesis
US4995883A (en) * 1989-02-08 1991-02-26 Smith & Nephew Richards Inc. Modular hip prosthesis
US5108452A (en) * 1989-02-08 1992-04-28 Smith & Nephew Richards Inc. Modular hip prosthesis
US5116377A (en) * 1989-04-15 1992-05-26 Bristol-Myers Squibb Company Cementable hip prosthesis
US5197988A (en) * 1989-06-21 1993-03-30 Sulzer Brothers Limited Femoral prosthesis
US5201771A (en) * 1989-09-15 1993-04-13 Belykh Sergei I Endoprosthesis of the hip joint
US5087260A (en) * 1989-09-15 1992-02-11 Fixel Irving E Total femoral hip system
US5004476A (en) * 1989-10-31 1991-04-02 Tulane University Porous coated total hip replacement system
US5201882A (en) * 1989-11-03 1993-04-13 Paxson Robert D Modular hip joint prosthesis with adjustable anteversion
US5002581A (en) * 1989-11-03 1991-03-26 Dow Corning Wright Corporation Modular hip joint prosthesis with adjustable anteversion
US5002578A (en) * 1990-05-04 1991-03-26 Venus Corporation Modular hip stem prosthesis apparatus and method
US5197990A (en) * 1990-05-17 1993-03-30 Howmedica International, Inc. Prosthetic intramedullary femoral prosthesis with preformed sheath
US5591233A (en) * 1990-06-01 1997-01-07 Depuy Dupont Orthopaedics Metal/composite hybrid orthopedic implants
US5861042A (en) * 1990-09-17 1999-01-19 Buechel; Frederick F. Prosthesis with biologically inert wear resistant surface
US5108451A (en) * 1991-01-31 1992-04-28 Forte Mark R Femoral component of a hip joint prosthesis
US5116380A (en) * 1991-02-28 1992-05-26 Zimmer, Inc. Prosthetic implant with spacers having tapered trailing edges
US5314489A (en) * 1991-09-30 1994-05-24 Johnson & Johnson Orthopaedics, Inc. Hip prosthesis
US5389107A (en) * 1992-05-11 1995-02-14 Antoine A. Nassar Shock absorbent prosthetic hip joint
US5480452A (en) * 1992-05-29 1996-01-02 Intermedics Orthopedics, Inc. Femoral prosthesis with wedge having opposed tapers
US5480453A (en) * 1992-11-20 1996-01-02 Burke; Dennis W. Collar for femoral implant and method and apparatus for installation thereof
US6179877B1 (en) * 1992-11-20 2001-01-30 Dennis W. Burke Centering device for femoral implant and method and apparatus for implementation thereof
US5514184A (en) * 1993-05-26 1996-05-07 Kabushiki Kaisha Kobe Seiko Sho Artificial joint having porous portion
US5514182A (en) * 1993-08-17 1996-05-07 University Of Utah Prosthetic joint with semipermeable capsule with reinforcing ribs
US5725590A (en) * 1993-08-30 1998-03-10 Sulzer Medizinaltechnik Ag Element for temporarily increasing the rigidity of an orthopaedic prosthesis
US6197065B1 (en) * 1993-11-01 2001-03-06 Biomet, Inc. Method and apparatus for segmental bone replacement
US5507814A (en) * 1994-03-30 1996-04-16 Northwestern University Orthopedic implant with self-reinforced mantle
US5725594A (en) * 1994-07-14 1998-03-10 Ortho Development Corporation Proximal conical stem
US5725595A (en) * 1994-11-08 1998-03-10 Orthopaedic Innovations, Inc. Cannulated cementless hip stem prosthesis
US5725593A (en) * 1995-02-22 1998-03-10 Caracciolo; Francesco Total anatomic hip prosthesis
US6193761B1 (en) * 1995-07-07 2001-02-27 Depuy Orthopaedics, Inc. Implantable prosthesis with metallic porous bead preforms applied during casting
US5858020A (en) * 1995-12-05 1999-01-12 Metagen, Llc Modular prosthesis
US6231611B1 (en) * 1996-06-14 2001-05-15 Raphael Mosseri Total hip prosthesis for endo-articular implantation, and ancillary device therefor
US5755807A (en) * 1996-06-17 1998-05-26 Folsom Metal Products Implant module unit and rotating seal for prosthetic joint
US5876459A (en) * 1996-08-30 1999-03-02 Powell; Douglas Hunter Adjustable modular orthopedic implant
US5906644A (en) * 1996-08-30 1999-05-25 Powell; Douglas Hunter Adjustable modular orthopedic implant
US5746771A (en) * 1996-09-30 1998-05-05 Wright Medical Technology, Inc. Calcar collar instrumentation
US5725592A (en) * 1996-10-29 1998-03-10 Hayes Medical, Inc. Modular prosthesis having neck component connected to stem component through cavity in body component
US5888208A (en) * 1997-03-26 1999-03-30 Johnson & Johnson Professional, Inc. Modular hip trial for long stems
US6395004B1 (en) * 1997-11-14 2002-05-28 Sulzer Orthopedics Inc. Orthopedic trial prosthesis and saw guide instrument
US20030074080A1 (en) * 1998-04-14 2003-04-17 Murray Ian P. Modular neck for femur replacement surgery
US20030074079A1 (en) * 1998-04-14 2003-04-17 Osteoimplant Technology, Inc. Differential porosity prosthetic hip system
US6010535A (en) * 1998-04-30 2000-01-04 Shah; Mrugesh K. Joint replacement system
US6383226B1 (en) * 1998-06-09 2002-05-07 The Board Of Trustees Of The Leland Stanford Junior University Prostheses having curvilinear collars
US6383227B1 (en) * 1998-07-30 2002-05-07 Aap Implanters Ag Femoral neck endoprosthesis for an artificial hip joint
US6379390B1 (en) * 1999-06-23 2002-04-30 The University Of Delaware Stemless hip prosthesis
US20030050704A1 (en) * 2000-01-03 2003-03-13 Ory Keynan Prosthesis
US6524343B2 (en) * 2000-03-27 2003-02-25 Benoist Girard Sas Femoral hip prosthesis
US6503281B1 (en) * 2000-08-25 2003-01-07 Thomas H. Mallory Total hip replacement
US6514288B2 (en) * 2001-02-23 2003-02-04 Zimmer, Inc. Prosthetic stem with strengthening rib
US20030014123A1 (en) * 2001-05-18 2003-01-16 Peter Copf Cementless hip joint endoprosthesis as a surface replacement for the proximal femur
US20030033020A1 (en) * 2001-06-01 2003-02-13 Gordon Hunter Prosthetic devices employing contacting oxidized zirconium surfaces
US20030045941A1 (en) * 2001-08-27 2003-03-06 Lewallen David G. Coated prosthetic implant
US20030065397A1 (en) * 2001-08-27 2003-04-03 Hanssen Arlen D. Prosthetic implant support structure
US20030060891A1 (en) * 2001-09-27 2003-03-27 Shah Mrugesh K. Hip replacement system having fat lubricant
US20030078670A1 (en) * 2001-10-24 2003-04-24 Grimes James B. Prosthesis
US20030088316A1 (en) * 2001-11-05 2003-05-08 Ramin Ganjianpour Modular femoral prosthesis
US7534271B2 (en) * 2004-01-22 2009-05-19 Smith + Nephew Femoral hip prosthesis and method of implantation

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AU2005206852A1 (en) 2005-08-04

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