Patent Grant
9539099
The present disclosure relates generally to orthopaedic prostheses, and particularly to orthopaedic prostheses for use in knee replacement surgery.
Joint arthroplasty is a well-known surgical procedure by which a diseased and/or damaged natural joint is replaced by a prosthetic joint. A typical knee prosthesis includes a tibial tray, a femoral component, and a polymer insert or bearing positioned between the tibial tray and the femoral component. Depending on the severity of the damage to the patient's joint, orthopaedic prostheses of varying mobility may be used. For example, the knee prosthesis may include a “fixed” tibial bearing in cases wherein it is desirable to limit the movement of the knee prosthesis, such as when significant soft tissue loss or damage is present. Alternatively, the knee prosthesis may include a “mobile” tibial bearing in cases wherein a greater degree of freedom of movement is desired. Additionally, the knee prosthesis may be a total knee prosthesis designed to replace the femoral-tibial interface of both condyles of the patient's femur or a uni-compartmental (or uni-condylar) knee prosthesis designed to replace the femoral-tibial interface of a single condyle of the patient's femur.
The type of orthopedic knee prosthesis used to replace a patient's natural knee may also depend on whether the patient's posterior cruciate ligament is retained or sacrificed (i.e., removed) during surgery. For example, if the patient's posterior cruciate ligament is damaged, diseased, and/or otherwise removed during surgery, a posterior stabilized knee prosthesis may be used to provide additional support and/or control at later degrees of flexion. Alternatively, if the posterior cruciate ligament is intact, a cruciate retaining knee prosthesis may be used.
Typical orthopaedic knee prostheses are generally designed to duplicate the natural movement of the patient's joint. As the knee is flexed and extended, the femoral and tibial components articulate and undergo combinations of relative anterior-posterior motion and relative internal-external rotation. However, the patient's surrounding soft tissue also impacts the kinematics and stability of the orthopaedic knee prosthesis throughout the joint's range of motion. That is, forces exerted on the orthopaedic components by the patient's soft tissue may cause unwanted or undesirable motion of the orthopaedic knee prosthesis. For example, the orthopaedic knee prosthesis may exhibit an amount of unnatural (paradoxical) anterior translation as the femoral component is moved through the range of flexion.
In a typical orthopaedic knee prosthesis, paradoxical anterior translation may occur at nearly any degree of flexion, but particularly at mid to late degrees of flexion. Paradoxical anterior translation can be generally defined as an abnormal relative movement of a femoral component on a tibial bearing wherein the contact “point” between the femoral component and the tibial bearing “slides” anteriorly with respect to the tibial bearing. This paradoxical anterior translation may result in loss of joint stability, accelerated wear, abnormal knee kinematics, and/or cause the patient to experience a sensation of instability during some activities.
According to one aspect, an orthopaedic knee prosthesis may include a femoral component and a tibial bearing. The femoral component may have a condyle surface curved in the sagittal plane. The tibial bearing may be a bearing surface configured to articulate with the condyle surface of the femoral component. The condyle surface of the femoral component may be configured to contact the bearing surface at a first contact point on the condyle surface at a first degree of flexion less than about 30 degrees. The condyle surface of the femoral component may be also be configured to contact the bearing surface at a second contact point on the condyle surface at a second degree of flexion greater than about 45 degrees. Additionally, the condyle surface of the femoral component may be configured to contact the bearing surface at a third contact point on the condyle surface at a third degree of flexion greater than the second degree of flexion. In some embodiments, the first degree of flexion may be in the range of 0 degrees to 10 degrees, the second degree of flexion may be in the range of 60 degrees to 70 degrees, and the third degree of flexion may be in the range of 80 degrees to 110 degrees. For example, in one particular embodiment, the first degree of flexion is about 5 degrees, the second degree of flexion is about 65 degrees, and the third degree of flexion is about 90 degrees.
The condyle surface in the sagittal plane may have a first radius of curvature at the first contact point, a second radius curvature at the second contact point, and a third radius of curvature at the third contact point. In some embodiments, the third radius of curvature may be greater than the second radius of curvature by at least 0.5 millimeters. Additionally, the condyle surface in the sagittal plane between the first contact point and the second contact point may include a plurality of curved surface sections. Each curved surface section may have a different radius of curvature.
The plurality of curved surface sections may include an anterior-most curved surface section. In some embodiments, the radius of curvature of the anterior-most curved surface section may have a length greater than the radius of curvature of any other curved surface section of the plurality of curved surface sections. Additionally, in some embodiments, the length of the radius of curvature of each curved surface section posterior to the anterior-most curved surface section may be less than the length of the radius of curvature of an anteriorly-adjacent curved surface section. For example, in some embodiments, the length of the radius of curvature of each curved surface section posterior to the anterior-most curved surface section is less than the length of the radius of curvature of an anteriorly-adjacent curved surface section by a distance in the range of 0.1 millimeters to 5 millimeters, in the range of 1 millimeters to 3 millimeters, and/or about 1 millimeter.
Each of the plurality of curved surface sections may subtend a corresponding angle. In some embodiments, each angle subtended by the plurality of curved surface sections being approximately equal. In other embodiments, the angle subtended by each of the curved surface sections posterior to the anterior-most curved surface section may be less than the angle subtended by an anteriorly-adjacent curved surface section. For example, in some embodiments, the angle subtended by each of the curved surface sections posterior to the anterior-most curved surface section may be less than the angle subtended by the anteriorly-adjacent curved surface section by an amount in the range of 0.5 degrees to 5 degrees. Additionally, in other embodiments, the angle subtended by each of the curved surface sections posterior to the anterior-most curved surface section may be greater than the angle subtended by an anteriorly-adjacent curved surface section. For example, in some embodiments, the angle subtended by each of the curved surface sections posterior to the anterior-most curved surface section may be greater than the angle subtended by the anteriorly-adjacent curved surface section by an amount in the range of 0.5 degrees to 5 degrees.
According to another aspect, an orthopaedic knee prosthesis may include a femoral component and a tibial bearing. The femoral component may have a condyle surface curved in the sagittal plane. The tibial bearing may be a bearing surface configured to articulate with the condyle surface of the femoral component. The condyle surface of the femoral component may be configured to contact the bearing surface at a first contact point on the condyle surface at a first degree of flexion in the range of 0 to about 30 degrees. The condyle surface of the femoral component may be also be configured to contact the bearing surface at a second contact point on the condyle surface at a second degree of flexion in the range of 45 degrees to 90 degrees. The condyle surface in the sagittal plane between the first contact point and the second contact point may include at least five curved surface sections. Each curved surface section may have a radius of curvature having a length different from any other curved surface section.
The plurality of curved surface sections may include an anterior-most curved surface section. The radius of curvature of the anterior-most curved surface section may have a length greater than the radius of curvature of any other curved surface section of the plurality of curved surface sections. Additionally, the length of the radius of curvature of each curved surface section posterior to the anterior-most curved surface section may be less than the length of the radius of curvature of an anteriorly-adjacent curved surface section. For example, the length of the radius of curvature of each curved surface section posterior to the anterior-most curved surface section maybe less than the length of the radius of curvature of an anteriorly-adjacent curved surface section by a distance in the range of 1 millimeters to 3 millimeters.
Each of the plurality of curved surface sections may subtend a corresponding angle. In some embodiments, the angle subtended by each of the curved surface sections posterior to the anterior-most curved surface section may be less than the angle subtended by an anteriorly-adjacent curved surface section. In other embodiments, the angle subtended by each of the curved surface sections posterior to the anterior-most curved surface section may be greater than the angle subtended by an anteriorly-adjacent curved surface section.
According to another aspect, an orthopaedic knee prosthesis may include a femoral component and a tibial bearing. The femoral component may have a condyle surface curved in the sagittal plane. The tibial bearing may be a bearing surface configured to articulate with the condyle surface of the femoral component. The condyle surface of the femoral component may be configured to contact the bearing surface at a first contact point on the condyle surface at a first degree of flexion in the range of 0 to about 30 degrees. The condyle surface of the femoral component may be also be configured to contact the bearing surface at a second contact point on the condyle surface at a second degree of flexion in the range of 45 degrees to 90 degrees. The condyle surface in the sagittal plane between the first contact point and the second contact point may include at least five curved surface sections. Each curved surface section may subtend a corresponding, substantially equal angle and may have a radius of curvature different from any other curved surface section.
The detailed description particularly refers to the following figures, in which:
While the concepts of the present disclosure are susceptible to various modifications and alternative forms, specific exemplary embodiments thereof have been shown by way of example in the drawings and will herein be described in detail. It should be understood, however, that there is no intent to limit the concepts of the present disclosure to the particular forms disclosed, but on the contrary, the intention is to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the invention as defined by the appended claims.
Terms representing anatomical references, such as anterior, posterior, medial, lateral, superior, inferior, etcetera, may be used throughout this disclosure in reference to both the orthopaedic implants described herein and a patient's natural anatomy. Such terms have well-understood meanings in both the study of anatomy and the field of orthopaedics. Use of such anatomical reference terms in the specification and claims is intended to be consistent with their well-understood meanings unless noted otherwise.
Referring now to
As discussed in more detail below, the femoral component 12 is configured to articulate with the tibial bearing 14, which is configured to be coupled with the tibial tray 16. In the illustrative embodiment of
The tibial tray 16 is configured to be secured to a surgically-prepared proximal end of a patient's tibia (not shown). The tibial tray 16 may be secured to the patient's tibia via use of bone adhesive or other attachment means. The tibial tray 16 includes a platform 18 having a top surface 20 and a bottom surface 22. Illustratively, the top surface 20 is generally planar and, in some embodiments, may be highly polished. The tibial tray 16 also includes a stem 24 extending downwardly from the bottom surface 22 of the platform 18. A cavity or bore 26 is defined in the top surface 20 of the platform 18 and extends downwardly into the stem 24. The bore 26 is formed to receive a complimentary stem of the tibial insert 14 as discussed in more detail below.
As discussed above, the tibial bearing 14 is configured to be coupled with the tibial tray 16. The tibial bearing 14 includes a platform 30 having an upper bearing surface 32 and a bottom surface 34. In the illustrative embodiment wherein the tibial bearing 14 is embodied as a rotating or mobile tibial bearing, the bearing 14 includes a stem 36 extending downwardly from the bottom surface 32 of the platform 30. When the tibial bearing 14 is coupled to the tibial tray 16, the stem 36 is received in the bore 26 of the tibial tray 16. In use, the tibial bearing 14 is configured to rotate about an axis defined by the stem 36 relative to the tibial tray 16. In embodiments wherein the tibial bearing 14 is embodied as a fixed tibial bearing, the bearing 14 may or may not include the stem 22 and/or may include other devices or features to secure the tibial bearing 14 to the tibial tray 16 in a non-rotating configuration.
The upper bearing surface 32 of the tibial bearing 14 includes a medial bearing surface 42 and a lateral bearing surface 44. The medial and lateral bearing surfaces 42, 44 are configured to receive or otherwise contact corresponding medial and lateral condyles of the femoral component 12 as discussed in more detail below. As such, each of the bearing surface 42, 44 has a concave contour.
The femoral component 12 is configured to be coupled to a surgically-prepared surface of the distal end of a patient's femur (not shown). The femoral component 12 may be secured to the patient's femur via use of bone adhesive or other attachment means. The femoral component 12 includes an outer, articulating surface 50 having a pair of medial and lateral condyles 52, 54. The condyles 52, 54 are spaced apart to define an intracondyle opening 56 therebetween. In use, the condyles 52, 54 replace the natural condyles of the patient's femur and are configured to articulate on the corresponding bearing surfaces 42, 44 of the platform 30 of the tibial bearing 14.
The illustrative orthopaedic knee prosthesis 10 of
In such embodiments, the tibial bearing 14 is embodied as a posterior stabilizing tibial bearing and includes a spine 60 extending upwardly from the platform 30. The spine 60 is positioned between the bearing surfaces 42, 44 and includes an anterior side 62 and a posterior side 64 having a cam surface 66. In the illustrative embodiment, the cam surface 66 has a substantially concave curvature. However, spines 60 including cam surfaces 66 having other geometries may be used in other embodiments. For example, a tibial bearing including a spine having a substantially “S”-shaped cross-sectional profile, such as the tibial bearing described in U.S. patent application Ser. No. 12/165,582, entitled “Posterior Stabilized Orthopaedic Prosthesis” by Joseph G. Wyss, et al., which is hereby incorporated by reference, may be used in other embodiments.
Additionally, in such embodiments, the femoral component 12 is embodied as a posterior stabilized femoral component and includes an intracondyle notch or recess 57 (rather than an opening 56). A posterior cam 80 (shown in phantom) and an anterior cam 82 are positioned in the intracondyle notch 57. The posterior cam 80 is located toward the posterior side of the femoral component 12 and includes a cam surface 86 configured to engage or otherwise contact the cam surface 66 of the spine 60 of the tibial bearing 14 during flexion.
It should be appreciated that although the orthopaedic knee prosthesis 10 may be embodied as either a posterior cruciate-retaining or a cruciate-sacrificing knee prosthesis, the femoral component 12 and the tibial bearing 14 of the knee prosthesis 10 are discussed below, and illustrated in the remaining figures, in regard to a posterior cruciate-retaining knee prosthesis with the understanding that such description is equally applicable to those embodiments wherein the orthopaedic knee prosthesis 10 is embodied as a posterior cruciate-sacrificing (posterior stabilized) orthopaedic knee prosthesis.
It should be appreciated that the illustrative orthopaedic knee prosthesis 10 is configured to replace a patient's right knee and, as such, the bearing surface 42 and the condyle 52 are referred to as being medially located; and the bearing surface 44 and the condyle 54 are referred to as being laterally located. However, in other embodiments, the orthopaedic knee prosthesis 10 may be configured to replace a patient's left knee. In such embodiments, it should be appreciated that the bearing surface 42 and the condyle 52 may be laterally located and the bearing surface 44 and the condyle 54 may be medially located. Regardless, the features and concepts described herein may be incorporated in an orthopaedic knee prosthesis configured to replace either knee joint of a patient.
Referring now to
Additionally, as the orthopaedic knee prosthesis 10 is articulated through the middle degrees of flexion, the femoral component 12 contacts the tibial bearing 14 at one or more contact points on the condyle surface 100. For example, in one embodiment as illustrated in
The orthopaedic knee prosthesis 10 is configured such that the amount of paradoxical anterior translation of the femoral component 12 relative to the tibial bearing 14 may be reduced or otherwise delayed to a later (i.e., larger) degree of flexion. In particular, as discussed in more detail below, the condyle surface 100 of one or both of the condyles 52, 54 has particular geometry or curvature configured to reduce and/or delay anterior translations and, in some embodiments, promote “roll-back” or posterior translation, of the femoral component 12. It should be appreciated that by delaying the onset of paradoxical anterior translation of the femoral component 12 to a larger degree of flexion, the overall occurrence of paradoxical anterior translation may be reduced during those activities of a patient in which deep flexion is not typically obtained.
In a typical orthopaedic knee prosthesis, paradoxical anterior translation may occur whenever the knee prosthesis is positioned at a degree of flexion greater than zero degrees. The likelihood of anterior translation generally increases as the orthopaedic knee prosthesis is articulated to larger degrees of flexion, particularly in the mid-flexion range. In such orientations, paradoxical anterior translation of the femoral component on the tibial bearing can occur whenever the tangential (traction) force between the femoral component and the tibial bearing fails to satisfy the following equation:
T<μN (1)
wherein “T” is the tangential (traction) force, “μ” is the coefficient of friction of the femoral component and the tibial bearing, and “N” is the normal force between the femoral component and the tibial bearing. As a generalization, the tangential (traction) force between the femoral component and the tibial bearing can be defined as
T=M/R (2)
wherein “T” is the tangential (traction) force between the femoral component and the tibial bearing, “M” is the knee moment, and “R” is the radius of curvature in the sagittal plane of the condyle surface in contact with the tibial bearing at the particular degree of flexion. It should be appreciated that equation (2) is a simplification of the governing real-world equations, which does not consider such other factors as inertia and acceleration. Regardless, the equation (2) provides insight that paradoxical anterior translation of an orthopaedic knee prosthesis may be reduced or delayed by controlling the radius of curvature of the condyle surface of the femoral component. That is, by controlling the radius of curvature of the condyle surface (e.g., increasing or maintaining the radius of curvature), the right-hand side of equation (2) may be reduced, thereby decreasing the value of the tangential (traction) force and satisfying the equation (1). As discussed above, by ensuring that the tangential (traction) force satisfies equation (1), paradoxical anterior translation of the femoral component on the tibial bearing may be reduced or otherwise delayed to a greater degree of flexion.
Based on the above analysis, to reduce or delay the onset of paradoxical anterior translation, the geometry of the condyle surface 100 of one or both of the condyles 52, 54 of the femoral component 12 is controlled. For example, in some embodiments, the radius of curvature of the condyle surface 100 is controlled such that the radius of curvature is held constant over a range of degrees of flexion and/or is increased in the early to mid flexion ranges. Comparatively, typical femoral components have decreasing radii of curvatures beginning at the distal radius of curvature (i.e., at about 0 degrees of flexion). However, it has been determined that by maintaining a relatively constant radius of curvature (i.e., not decreasing the radius of curvature) over a predetermined range of degrees of early to mid-flexion and/or increasing the radius of curvature over the predetermined range of degrees of flexion may reduce or delay paradoxical anterior translation of the femoral component 12.
Additionally, in some embodiments, the condyle surface 100 is configured or designed such that the transition between discrete radii of curvature of the condyle surface 100 is gradual. That is, by gradually transitioning between the discrete radii of curvature, rather than abrupt transitions, paradoxical anterior translation of the femoral component 12 may be reduced or delayed. Further, in some embodiments, the rate of change in the radius of curvature of the condyle surface in the early to mid flexion ranges (e.g., from about 0 degrees to about 90 degrees) is controlled such that the rate of change is less than a predetermined threshold. That is, it has been determined that if the rate of change of the radius of curvature of the condyle surface 100 is greater than the predetermined threshold, paradoxical anterior translation may occur.
Accordingly, in some embodiments as illustrated in
For example, the graph 200 illustrated in
In the graphs 200, 300, 400, 500, the condylar lowest or most distal points (CLP) of the medial condyle (“med”) and the lateral condyle (“lat”) of the femoral component are graphed as a representation of the relative positioning of the femoral component to the tibial bearing. As such, a downwardly sloped line represents roll-back of the femoral component on the tibial bearing and an upwardly sloped line represents anterior translation of the femoral component on the tibial bearing.
As illustrated in the graphs 200, 300, 400, 500, anterior sliding of the femoral component was delayed until after about 100 degrees of flexion in each of the embodiments; and the amount of anterior translation was limited to less than about 1 millimeter. In particular, “roll-back” of the femoral component on the tibial bearing was promoted by larger increases in the radius of curvature of the condyle surface at earlier degrees of flexion. Of course, amount of increase in the radius of curvature and the degree of flexion at which such increase is introduced is limited by other factors such as the anatomical joint space of the patient's knee, the size of the tibial bearing, and the like. Regardless, based on the simulations reported in the graphs 200, 300, 400, 500, paradoxical anterior translation of the femoral component on the tibial bearing can be reduced or otherwise delayed by increasing the radius of curvature of the condyle surface of the femoral component during early to mid flexion.
Accordingly, referring back to
As discussed above, the condyle surface 100 of the femoral component 12 is configured such that the radius of curvature R3 of the curved surface section 106 is greater than the radius of curvature R2 of the curved surface section 104. In one embodiment, the radius of curvature R3 is greater than the radius of curvature R2 by 0.5 millimeters or more. In another embodiment, the radius of curvature R3 is greater than the radius of curvature R2 by 2 millimeters or more. In another embodiment, the radius of curvature R3 is greater than the radius of curvature R2 by 2 millimeters or more. In a particular embodiment, the radius of curvature R3 is greater than the radius of curvature R2 by at least 5 millimeters or more. It should be appreciated, however, that the particular increase of radius of curvature between R2 and R3 may be based on or scaled to the particular size of the femoral component 12 in some embodiments.
Each of the curved surface sections 102, 104, 106, 108 contacts the bearing surface 42 (or 44) of the tibial bearing 14 through different ranges of degrees of flexion. For example, the curved surface section 102 extends from an earlier degree of flexion θ1 to a later degree of flexion θ2. The curved surface section 104 extends from the degree of flexion θ2 to a later degree of flexion θ3. The curved surface section 106 extends from the degree of flexion θ3 to a later degree of flexion θ4.
For example, in one embodiment, the curved surface section 102 may extend from a degree of flexion θ1 of about −10 degrees (i.e., 10 degrees of hyperextension) to a degree of flexion θ2 of about 5 degrees of flexion. The curved surface section 104 extends from the degree of flexion θ2 of about 5 degrees of flexion to a degree of flexion θ3 of about 65 degrees of flexion. The curved surface section 106 extends from the degree of flexion θ3 of about 65 degrees of flexion to a degree of flexion θ4 of about 90 degrees of flexion and the curved surface section 108 extends from the degree of flexion θ4 of about 90 degrees of flexion to a degree of flexion θ5 of about 104 degrees of flexion.
It should be appreciated, however, that each of the curved surface sections 102, 104, 106, 108 may extend from degrees of flexion different from those discussed above. For example, the particular degrees of flexion through which the curved surface sections 102, 104, 106, 108 extend may be based or otherwise determined based on the type of femoral component 12 (e.g., cruciate-retaining or posterior stabilized), the size of the femoral component 12, and/or the like.
As discussed above, the curved surface section 104 is designed to gradually transition from the radius of curvature R1 to the radius of curvature R2. To do so, in one embodiment as illustrated in
Each of the curved surface sections 110 of the condyle surface 100 contacts the bearing surface 42 (or 44) of the tibial bearing 14 through different ranges of degrees of flexion. For example, the curved surface section 110A extends from the degree of flexion θ2 to a later degree of flexion θC1, the curved surface section 110B extends from the degree of flexion θC1 to a later degree of flexion θC2, the curved surface section 110C extends from the degree of flexion θC2 to a later degree of flexion θC3, the curved surface section 110D extends from the degree of flexion θC3 to a later degree of flexion θC4, the curved surface section 110E extends from the degree of flexion θC4 to a later degree of flexion θC5, and the curved surface section 110F extends from the degree of flexion θC5 to the later degree of flexion θ3.
In the illustrative embodiment of
Each of the curved surface sections 110 is defined by a radius of curvature R5. That is, the curved surface section 110A is defined by a radius of curvature R5A, the curved surface section 110B is defined by a radius of curvature R5B, the curved surface section 110C is defined by a radius of curvature R5C, the curved surface section 110D is defined by a radius of curvature R5D, the curved surface section 110E is defined by a radius of curvature R5E, and the curved surface section 110F is defined by a radius of curvature R5F. Each radius of curvature R5 is smaller (i.e., has a shorter length) than the anteriorly-adjacent radius of curvature R5. That is, R5F is smaller than R5E, R5E is smaller than R5D, R5D is smaller than R5C, R5C is smaller than R5B, and R5B is smaller than R5A. For example, in one embodiment, each radius of curvature R5 may have a length shorter than the anteriorly-adjacent radius of curvature R5 by an amount in the range of about 0.1 millimeters to about 5 millimeters. However, in other embodiments, each radius of curvature R5 may have a length shorter than the anteriorly-adjacent radius of curvature R5 by an amount greater or less than such values. The particular length of each radius of curvature R5 may be determined based on the particular application, the length of the curved surface section 104, an defined equation, and/or the like.
Referring now to
As discussed above, each of the curved surface sections 120 extend different degrees of flexion. That is, the degrees of flexion between θ2 and θC1, θC1 and θC2, between θC2 and θC3, between θC3 and θC4, between θC4 and θC5, between θC5 and θC6, between θC6 and θC7, between θC7 and θC8, between θC8 and θC9, and between θC9 and θ3 are different from each other. In some embodiments, each curved surface section 120 subtends an angle that is less than the angle subtended by the anteriorly-adjacent section 120. For example, in the illustrative embodiment of
Although each curved surface section 120 subtends an angle 1 degree less than the anteriorly-adjacent section 120 in the illustrative embodiment of
The overall shape and design of the condyle surface 100 of the femoral component 12 has been described above in regard to a single condyle 52, 54 of the femoral component 12. It should be appreciated that in some embodiments both condyles 52, 54 of the femoral component 12 may be symmetrical and have similar condyle surfaces 100. However, in other embodiments, the condyles 52, 54 of the femoral component 12 may be asymmetrical. That is, each condyle 52, 54 may have a condyle surface 100 having the features described herein but being asymmetrical to the other condyle 52, 54.
While the disclosure has been illustrated and described in detail in the drawings and foregoing description, such an illustration and description is to be considered as exemplary and not restrictive in character, it being understood that only illustrative embodiments have been shown and described and that all changes and modifications that come within the spirit of the disclosure are desired to be protected.
There are a plurality of advantages of the present disclosure arising from the various features of the devices and assemblies described herein. It will be noted that alternative embodiments of the devices and assemblies of the present disclosure may not include all of the features described yet still benefit from at least some of the advantages of such features. Those of ordinary skill in the art may readily devise their own implementations of the devices and assemblies that incorporate one or more of the features of the present invention and fall within the spirit and scope of the present disclosure as defined by the appended claims.
This application claims priority under 35 U.S.C. §120 to U.S. patent application Ser. No. 13/540,177, now U.S. Pat. No. 8,795,380, and entitled “Orthopaedic Knee Prosthesis Having Controlled Condylar Curvature,” by Joseph G. Wyss et al., which was filed on Jul. 2, 2012 and claimed priority to U.S. patent application Ser. No. 12/488,107, now U.S. Pat. No. 8,236,061, entitled “Orthopaedic Knee Prosthesis Having Controlled Condylar Curvature,” by Joseph G. Wyss et al., which was filed on Jun. 19, 2009 and claimed priority under 35 U.S.C. §119(e) to U.S. Provisional Patent Application Ser. No. 61/077,124 entitled “Orthopaedic Knee Prosthesis Having Controlled Condylar Curvature,” by Joseph G. Wyss et al., which was filed on Jun. 30, 2008. The entirety of each of those applications is hereby incorporated by reference. Cross-reference is also made to U.S. Utility patent application Ser. No. 12/165,579, entitled “Orthopaedic Femoral Component Having Controlled Condylar Curvature” by John L. Williams et al., which was filed on Jun. 30, 2008; to U.S. Utility patent application Ser. No. 12/165,574, now U.S. Pat. No. 8,192,498, entitled “Posterior Cruciate-Retaining Orthopaedic Knee Prosthesis Having Controlled Condylar Curvature” by Christel M. Wagner, which was filed on Jun. 30, 2008; to U.S. Utility patent application Ser. No. 12/165,575, now U.S. Pat. No. 8,187,335, entitled “Posterior Stabilized Orthopaedic Knee Prosthesis Having Controlled Condylar Curvature” by Joseph G. Wyss, which was filed on Jun. 30, 2008; and to U.S. Utility patent application Ser. No. 12/165,582, now U.S. Pat. No. 8,206,451, entitled “Posterior Stabilized Orthopaedic Prosthesis” by Joseph G. Wyss, which was filed on Jun. 30, 2008; the entirety of each of which is incorporated herein by reference.
| Number | Name | Date | Kind |
|---|---|---|---|
| 3765033 | Goldberg et al. | Oct 1973 | A |
| 3840905 | Deane | Oct 1974 | A |
| 3852045 | Wheeler | Dec 1974 | A |
| 3855638 | Pilliar | Dec 1974 | A |
| 3869731 | Waugh et al. | Mar 1975 | A |
| 4081866 | Upshaw et al. | Apr 1978 | A |
| 4156943 | Collier | Jun 1979 | A |
| 4206516 | Pilliar | Jun 1980 | A |
| 4209861 | Walker et al. | Jul 1980 | A |
| 4215439 | Gold et al. | Aug 1980 | A |
| 4249270 | Bahler et al. | Feb 1981 | A |
| 4257129 | Volz | Mar 1981 | A |
| 4262368 | Lacey | Apr 1981 | A |
| 4340978 | Buechel et al. | Jul 1982 | A |
| 4470158 | Pappas et al. | Sep 1984 | A |
| 4612160 | Donlevy | Sep 1986 | A |
| 4673407 | Martin | Jun 1987 | A |
| 4714474 | Brooks, Jr. | Dec 1987 | A |
| 4795468 | Hodorek | Jan 1989 | A |
| 4808185 | Penenberg et al. | Feb 1989 | A |
| 4822362 | Walker | Apr 1989 | A |
| 4838891 | Branemark | Jun 1989 | A |
| 4888021 | Forte et al. | Dec 1989 | A |
| 4938769 | Shaw | Jul 1990 | A |
| 4944757 | Martinez | Jul 1990 | A |
| 4944760 | Kenna | Jul 1990 | A |
| 4950298 | Gustilo et al. | Aug 1990 | A |
| 4963152 | Hofmann et al. | Oct 1990 | A |
| 4990163 | Ducheyne | Feb 1991 | A |
| 5007933 | Sidebotham et al. | Apr 1991 | A |
| 5011496 | Forte et al. | Apr 1991 | A |
| 5019103 | Van Zile | May 1991 | A |
| 5037423 | Kenna | Aug 1991 | A |
| 5071438 | Jones et al. | Dec 1991 | A |
| 5080675 | Lawes | Jan 1992 | A |
| 5104410 | Chowdhary | Apr 1992 | A |
| 5108442 | Smith | Apr 1992 | A |
| 5116375 | Hofmann | May 1992 | A |
| 5133758 | Hollister | Jul 1992 | A |
| 5147405 | Van Zile et al. | Sep 1992 | A |
| 5171283 | Pappas | Dec 1992 | A |
| 5201766 | Georgette | Apr 1993 | A |
| 5219362 | Tuke et al. | Jun 1993 | A |
| 5236461 | Forte | Aug 1993 | A |
| 5251468 | Lin | Oct 1993 | A |
| 5258044 | Lee | Nov 1993 | A |
| 5271737 | Baldwin | Dec 1993 | A |
| 5282861 | Kaplan | Feb 1994 | A |
| 5308556 | Bagley | May 1994 | A |
| 5309639 | Lee | May 1994 | A |
| 5326361 | Hollister | Jul 1994 | A |
| 5330533 | Walker | Jul 1994 | A |
| 5330534 | Herrington et al. | Jul 1994 | A |
| 5344460 | Turanyi et al. | Sep 1994 | A |
| 5344461 | Phlipot | Sep 1994 | A |
| 5344494 | Davidson | Sep 1994 | A |
| 5358527 | Forte | Oct 1994 | A |
| 5368881 | Kelman | Nov 1994 | A |
| 5370699 | Hood et al. | Dec 1994 | A |
| 5387240 | Pottenger et al. | Feb 1995 | A |
| 5395401 | Bahler | Mar 1995 | A |
| 5405396 | Heldreth et al. | Apr 1995 | A |
| 5413604 | Hodge | May 1995 | A |
| 5414049 | Sun | May 1995 | A |
| 5449745 | Sun | Sep 1995 | A |
| 5458637 | Hayes | Oct 1995 | A |
| 5480446 | Goodfellow | Jan 1996 | A |
| 5543471 | Sun | Aug 1996 | A |
| 5549686 | Johnson et al. | Aug 1996 | A |
| 5571187 | Devanathan | Nov 1996 | A |
| 5571194 | Gabriel | Nov 1996 | A |
| 5609639 | Walker | Mar 1997 | A |
| 5609643 | Colleran et al. | Mar 1997 | A |
| 5639279 | Burkinshaw et al. | Jun 1997 | A |
| 5650485 | Sun | Jul 1997 | A |
| 5658333 | Kelman | Aug 1997 | A |
| 5658342 | Draganich et al. | Aug 1997 | A |
| 5658344 | Hurlburt | Aug 1997 | A |
| 5681354 | Eckhoff | Oct 1997 | A |
| 5683468 | Pappas | Nov 1997 | A |
| 5702458 | Burstein et al. | Dec 1997 | A |
| 5702463 | Pothier | Dec 1997 | A |
| 5702464 | Lackey et al. | Dec 1997 | A |
| 5702466 | Pappas et al. | Dec 1997 | A |
| 5728748 | Sun | Mar 1998 | A |
| 5732469 | Hamamoto | Mar 1998 | A |
| 5755800 | O'Neil | May 1998 | A |
| 5755801 | Walker et al. | May 1998 | A |
| 5755803 | Haines et al. | May 1998 | A |
| 5765095 | Flak | Jun 1998 | A |
| 5766257 | Goodman et al. | Jun 1998 | A |
| 5776201 | Colleran et al. | Jul 1998 | A |
| 5800552 | Forte | Sep 1998 | A |
| 5811543 | Hao et al. | Sep 1998 | A |
| 5824096 | Pappas et al. | Oct 1998 | A |
| 5824100 | Kester et al. | Oct 1998 | A |
| 5824102 | Buscayret | Oct 1998 | A |
| 5824103 | Williams | Oct 1998 | A |
| 5871543 | Hofmann | Feb 1999 | A |
| 5871545 | Goodfellow | Feb 1999 | A |
| 5871546 | Colleran et al. | Feb 1999 | A |
| 5879394 | Ashby | Mar 1999 | A |
| 5879400 | Merrill | Mar 1999 | A |
| 5906644 | Powell | May 1999 | A |
| 5935173 | Roger et al. | Aug 1999 | A |
| 5951603 | O'Neil et al. | Sep 1999 | A |
| 5957979 | Beckman | Sep 1999 | A |
| 5964808 | Blaha | Oct 1999 | A |
| 5976147 | LaSalle et al. | Nov 1999 | A |
| 5984969 | Matthews | Nov 1999 | A |
| 5989027 | Wagner | Nov 1999 | A |
| 5997577 | Herrington et al. | Dec 1999 | A |
| 6004351 | Tomita et al. | Dec 1999 | A |
| 6005018 | Cicierega | Dec 1999 | A |
| 6010534 | O'Neil et al. | Jan 2000 | A |
| 6013103 | Kaufman et al. | Jan 2000 | A |
| 6017975 | Saum | Jan 2000 | A |
| 6039764 | Pottenger et al. | Mar 2000 | A |
| 6042780 | Huang | Mar 2000 | A |
| 6053945 | O'Neil et al. | Apr 2000 | A |
| 6059949 | Gal Or | May 2000 | A |
| 6068658 | Insall | May 2000 | A |
| 6080195 | Colleran et al. | Jun 2000 | A |
| 6090144 | Letot | Jul 2000 | A |
| 6123728 | Brosnahan | Sep 2000 | A |
| 6123729 | Insall et al. | Sep 2000 | A |
| 6123896 | Meeks, III | Sep 2000 | A |
| 6126692 | Robie et al. | Oct 2000 | A |
| 6135857 | Shaw | Oct 2000 | A |
| 6139581 | Engh et al. | Oct 2000 | A |
| 6152960 | Pappas | Nov 2000 | A |
| 6162254 | Timoteo | Dec 2000 | A |
| 6174934 | Sun | Jan 2001 | B1 |
| 6206926 | Pappas | Mar 2001 | B1 |
| 6210444 | Webster | Apr 2001 | B1 |
| 6210445 | Zawadzki | Apr 2001 | B1 |
| 6217618 | Hileman | Apr 2001 | B1 |
| 6228900 | Shen | May 2001 | B1 |
| 6238434 | Pappas | May 2001 | B1 |
| 6242507 | Saum | Jun 2001 | B1 |
| 6245276 | McNulty | Jun 2001 | B1 |
| 6258127 | Schmotzer | Jul 2001 | B1 |
| 6264697 | Walker | Jul 2001 | B1 |
| 6280476 | Metzger | Aug 2001 | B1 |
| 6281264 | Salovey | Aug 2001 | B1 |
| 6299646 | Chambat et al. | Oct 2001 | B1 |
| 6316158 | Saum | Nov 2001 | B1 |
| 6319283 | Insall | Nov 2001 | B1 |
| 6325828 | Dennis et al. | Dec 2001 | B1 |
| 6344059 | Krakovits et al. | Feb 2002 | B1 |
| 6361564 | Marceaux | Mar 2002 | B1 |
| 6372814 | Sun | Apr 2002 | B1 |
| 6379388 | Ensign et al. | Apr 2002 | B1 |
| 6428577 | Evans et al. | Aug 2002 | B1 |
| 6443991 | Running | Sep 2002 | B1 |
| 6475241 | Pappas | Nov 2002 | B2 |
| 6485519 | Meyers et al. | Nov 2002 | B2 |
| 6491726 | Pappas | Dec 2002 | B2 |
| 6494914 | Brown et al. | Dec 2002 | B2 |
| 6503280 | Repicci | Jan 2003 | B2 |
| 6506215 | Letot | Jan 2003 | B1 |
| 6506216 | McCue | Jan 2003 | B1 |
| 6524522 | Vaidyanathan | Feb 2003 | B2 |
| 6540787 | Biegun et al. | Apr 2003 | B2 |
| 6558426 | Masini | May 2003 | B1 |
| 6569202 | Whiteside | May 2003 | B2 |
| 6582469 | Tornier | Jun 2003 | B1 |
| 6582470 | Lee | Jun 2003 | B1 |
| 6589283 | Metzger et al. | Jul 2003 | B1 |
| 6592787 | Pickrell | Jul 2003 | B2 |
| 6620198 | Burstein et al. | Sep 2003 | B2 |
| 6623526 | Lloyd | Sep 2003 | B1 |
| 6645251 | Salehi et al. | Nov 2003 | B2 |
| 6660039 | Evans et al. | Dec 2003 | B1 |
| 6660224 | Lefebvre | Dec 2003 | B2 |
| 6664308 | Sun | Dec 2003 | B2 |
| 6702821 | Bonutti | Mar 2004 | B2 |
| 6719800 | Meyers et al. | Apr 2004 | B2 |
| 6726724 | Repicci | Apr 2004 | B2 |
| 6730128 | Burstein | May 2004 | B2 |
| 6764516 | Pappas | Jul 2004 | B2 |
| 6770078 | Bonutti | Aug 2004 | B2 |
| 6770099 | Andriacchi et al. | Aug 2004 | B2 |
| 6773461 | Meyers et al. | Aug 2004 | B2 |
| 6797005 | Pappas | Sep 2004 | B2 |
| 6818020 | Sun | Nov 2004 | B2 |
| 6846327 | Khandkar | Jan 2005 | B2 |
| 6846329 | McMinn | Jan 2005 | B2 |
| 6849230 | Feichtinger | Feb 2005 | B1 |
| 6852272 | Artz | Feb 2005 | B2 |
| 6869448 | Tuke et al. | Mar 2005 | B2 |
| 6893388 | Reising et al. | May 2005 | B2 |
| 6893467 | Bercovy | May 2005 | B1 |
| 6916340 | Metzger et al. | Jul 2005 | B2 |
| 6923832 | Sharkey | Aug 2005 | B1 |
| 6926738 | Wyss | Aug 2005 | B2 |
| 6942670 | Heldreth et al. | Sep 2005 | B2 |
| 6972039 | Metzger et al. | Dec 2005 | B2 |
| 6986791 | Metzger | Jan 2006 | B1 |
| 7025788 | Metzger et al. | Apr 2006 | B2 |
| 7048741 | Swanson | May 2006 | B2 |
| 7066963 | Naegerl | Jun 2006 | B2 |
| 7070622 | Brown | Jul 2006 | B1 |
| 7081137 | Servidio | Jul 2006 | B1 |
| 7094259 | Tarabichi | Aug 2006 | B2 |
| 7101401 | Brack | Sep 2006 | B2 |
| 7104996 | Bonutti | Sep 2006 | B2 |
| 7105027 | Lipman et al. | Sep 2006 | B2 |
| 7147819 | Bram | Dec 2006 | B2 |
| 7160330 | Axelson, Jr. et al. | Jan 2007 | B2 |
| 7175665 | German | Feb 2007 | B2 |
| 7255715 | Metzger | Aug 2007 | B2 |
| 7261740 | Tuttle et al. | Aug 2007 | B2 |
| 7297164 | Johnson et al. | Nov 2007 | B2 |
| 7326252 | Otto et al. | Feb 2008 | B2 |
| 7341602 | Fell et al. | Mar 2008 | B2 |
| 7344460 | Gait | Mar 2008 | B2 |
| 7357817 | D'Alessio, II | Apr 2008 | B2 |
| 7422605 | Burstein et al. | Sep 2008 | B2 |
| 7510557 | Bonutti | Mar 2009 | B1 |
| 7527650 | Johnson et al. | May 2009 | B2 |
| 7572292 | Crabtree et al. | Aug 2009 | B2 |
| 7578850 | Kuczynski et al. | Aug 2009 | B2 |
| 7608079 | Blackwell et al. | Oct 2009 | B1 |
| 7611519 | Lefevre et al. | Nov 2009 | B2 |
| 7615054 | Bonutti | Nov 2009 | B1 |
| 7618462 | Ek | Nov 2009 | B2 |
| 7628818 | Hazebrouck et al. | Dec 2009 | B2 |
| 7635390 | Bonutti | Dec 2009 | B1 |
| 7658767 | Wyss | Feb 2010 | B2 |
| 7678151 | Ek | Mar 2010 | B2 |
| 7678152 | Suguro et al. | Mar 2010 | B2 |
| 7708740 | Bonutti | May 2010 | B1 |
| 7708741 | Bonutti | May 2010 | B1 |
| 7740662 | Barnett et al. | Jun 2010 | B2 |
| 7749229 | Bonutti | Jul 2010 | B1 |
| 7753960 | Cipolletti et al. | Jul 2010 | B2 |
| 7771484 | Campbell | Aug 2010 | B2 |
| 7776044 | Pendleton | Aug 2010 | B2 |
| 7806896 | Bonutti | Oct 2010 | B1 |
| 7806897 | Bonutti | Oct 2010 | B1 |
| 7837736 | Bonutti | Nov 2010 | B2 |
| 7842093 | Peters et al. | Nov 2010 | B2 |
| 7875081 | Lipman et al. | Jan 2011 | B2 |
| 7922771 | Otto et al. | Apr 2011 | B2 |
| 8187335 | Wyss et al. | May 2012 | B2 |
| 8192498 | Wagner et al. | Jun 2012 | B2 |
| 8206451 | Wyss et al. | Jun 2012 | B2 |
| 8236061 | Heldreth et al. | Aug 2012 | B2 |
| 20020138150 | Leclercq | Sep 2002 | A1 |
| 20030009232 | Metzger et al. | Jan 2003 | A1 |
| 20030035747 | Anderson | Feb 2003 | A1 |
| 20030044301 | Lefebvre | Mar 2003 | A1 |
| 20030075013 | Grohowski | Apr 2003 | A1 |
| 20030139817 | Tuke | Jul 2003 | A1 |
| 20030153981 | Wang | Aug 2003 | A1 |
| 20030171820 | Wilshaw | Sep 2003 | A1 |
| 20030199985 | Masini | Oct 2003 | A1 |
| 20030212161 | McKellop | Nov 2003 | A1 |
| 20030225456 | Ek | Dec 2003 | A1 |
| 20040015770 | Kimoto | Jan 2004 | A1 |
| 20040039450 | Griner et al. | Feb 2004 | A1 |
| 20040167633 | Wen | Aug 2004 | A1 |
| 20040186583 | Keller | Sep 2004 | A1 |
| 20040215345 | Perrone | Oct 2004 | A1 |
| 20040243244 | Otto et al. | Dec 2004 | A1 |
| 20040243245 | Plumet et al. | Dec 2004 | A1 |
| 20050021147 | Tarabichi | Jan 2005 | A1 |
| 20050055102 | Tornier | Mar 2005 | A1 |
| 20050059750 | Sun | Mar 2005 | A1 |
| 20050069629 | Becker | Mar 2005 | A1 |
| 20050096747 | Tuttle et al. | May 2005 | A1 |
| 20050100578 | Schmid | May 2005 | A1 |
| 20050123672 | Justin | Jun 2005 | A1 |
| 20050143832 | Carson | Jun 2005 | A1 |
| 20050154472 | Afriat | Jul 2005 | A1 |
| 20050203631 | Daniels | Sep 2005 | A1 |
| 20050209701 | Suguro et al. | Sep 2005 | A1 |
| 20050209702 | Todd | Sep 2005 | A1 |
| 20050249625 | Bram | Nov 2005 | A1 |
| 20050278035 | Wyss et al. | Dec 2005 | A1 |
| 20060002810 | Grohowski | Jan 2006 | A1 |
| 20060015185 | Chambat et al. | Jan 2006 | A1 |
| 20060036329 | Webster | Feb 2006 | A1 |
| 20060052875 | Bernero | Mar 2006 | A1 |
| 20060100714 | Ensign | May 2006 | A1 |
| 20060178749 | Pendleton et al. | Aug 2006 | A1 |
| 20060195195 | Burstein | Aug 2006 | A1 |
| 20060228247 | Grohowski | Oct 2006 | A1 |
| 20060231402 | Clasen | Oct 2006 | A1 |
| 20060241781 | Brown | Oct 2006 | A1 |
| 20060257358 | Wen | Nov 2006 | A1 |
| 20060271191 | Hermansson | Nov 2006 | A1 |
| 20060289388 | Yang | Dec 2006 | A1 |
| 20070061014 | Naegerl | Mar 2007 | A1 |
| 20070073409 | Cooney | Mar 2007 | A1 |
| 20070078521 | Overholser | Apr 2007 | A1 |
| 20070100463 | Aram | May 2007 | A1 |
| 20070129809 | Meridew | Jun 2007 | A1 |
| 20070135926 | Walker | Jun 2007 | A1 |
| 20070173948 | Meridew | Jul 2007 | A1 |
| 20070196230 | Hamman | Aug 2007 | A1 |
| 20070203582 | Campbell | Aug 2007 | A1 |
| 20070219639 | Otto et al. | Sep 2007 | A1 |
| 20070293647 | McKellop | Dec 2007 | A1 |
| 20080004708 | Wyss | Jan 2008 | A1 |
| 20080021566 | Peters et al. | Jan 2008 | A1 |
| 20080091272 | Aram | Apr 2008 | A1 |
| 20080097616 | Meyers et al. | Apr 2008 | A1 |
| 20080114462 | Guidera et al. | May 2008 | A1 |
| 20080114464 | Barnett et al. | May 2008 | A1 |
| 20080119940 | Otto et al. | May 2008 | A1 |
| 20080161927 | Savage | Jul 2008 | A1 |
| 20080195108 | Bhatnagar et al. | Aug 2008 | A1 |
| 20080199720 | Liu | Aug 2008 | A1 |
| 20080206297 | Roeder | Aug 2008 | A1 |
| 20080269596 | Revie et al. | Oct 2008 | A1 |
| 20090043396 | Komistek | Feb 2009 | A1 |
| 20090048680 | Naegerl | Feb 2009 | A1 |
| 20090082873 | Hazebrouck | Mar 2009 | A1 |
| 20090084491 | Uthgenannt | Apr 2009 | A1 |
| 20090088859 | Hazebrouck et al. | Apr 2009 | A1 |
| 20090125114 | May et al. | May 2009 | A1 |
| 20090192610 | Case | Jul 2009 | A1 |
| 20090265012 | Engh et al. | Oct 2009 | A1 |
| 20090265013 | Mandell | Oct 2009 | A1 |
| 20090292365 | Smith | Nov 2009 | A1 |
| 20090295035 | Evans | Dec 2009 | A1 |
| 20090306785 | Farrar et al. | Dec 2009 | A1 |
| 20090319047 | Walker | Dec 2009 | A1 |
| 20090326663 | Dun | Dec 2009 | A1 |
| 20090326664 | Wagner et al. | Dec 2009 | A1 |
| 20090326665 | Wyss et al. | Dec 2009 | A1 |
| 20090326666 | Wyss et al. | Dec 2009 | A1 |
| 20090326667 | Williams et al. | Dec 2009 | A1 |
| 20090326674 | Liu | Dec 2009 | A1 |
| 20100016979 | Wyss et al. | Jan 2010 | A1 |
| 20100036499 | Pinskerova | Feb 2010 | A1 |
| 20100036500 | Heldreth et al. | Feb 2010 | A1 |
| 20100042224 | Otto et al. | Feb 2010 | A1 |
| 20100042225 | Shur | Feb 2010 | A1 |
| 20100063594 | Hazebrouck | Mar 2010 | A1 |
| 20100070045 | Ek | Mar 2010 | A1 |
| 20100076563 | Otto et al. | Mar 2010 | A1 |
| 20100076564 | Schilling et al. | Mar 2010 | A1 |
| 20100094429 | Otto | Apr 2010 | A1 |
| 20100098574 | Liu | Apr 2010 | A1 |
| 20100100189 | Metzger | Apr 2010 | A1 |
| 20100100190 | May et al. | Apr 2010 | A1 |
| 20100100191 | May et al. | Apr 2010 | A1 |
| 20100125337 | Grecco et al. | May 2010 | A1 |
| 20100161067 | Saleh et al. | Jun 2010 | A1 |
| 20100191341 | Byrd | Jul 2010 | A1 |
| 20100222890 | Barnett | Sep 2010 | A1 |
| 20100286788 | Komistek | Nov 2010 | A1 |
| 20100292804 | Samuelson | Nov 2010 | A1 |
| 20100305710 | Metzger et al. | Dec 2010 | A1 |
| 20100312350 | Bonutti | Dec 2010 | A1 |
| 20110029090 | Zannis | Feb 2011 | A1 |
| 20110029092 | Deruntz | Feb 2011 | A1 |
| 20110035017 | Deffenbaugh | Feb 2011 | A1 |
| 20110035018 | Deffenbaugh | Feb 2011 | A1 |
| 20110106268 | Deffenbaugh | May 2011 | A1 |
| 20110118847 | Lipman et al. | May 2011 | A1 |
| 20110125280 | Otto et al. | May 2011 | A1 |
| 20110153026 | Heggendorn et al. | Jun 2011 | A1 |
| 20120239158 | Wagner et al. | Sep 2012 | A1 |
| 20120259417 | Wyss et al. | Oct 2012 | A1 |
| 20120296437 | Wyss et al. | Nov 2012 | A1 |
| 20130006372 | Wyss et al. | Jan 2013 | A1 |
| 20130006373 | Wyss et al. | Jan 2013 | A1 |
| Number | Date | Country |
|---|---|---|
| 1803106 | Jul 2006 | CN |
| 1872009 | Dec 2006 | CN |
| 4308563 | Sep 1994 | DE |
| 19529824 | Feb 1997 | DE |
| 510178 | May 1992 | EP |
| 495340 | Jul 1992 | EP |
| 634155 | Jan 1995 | EP |
| 636352 | Feb 1995 | EP |
| 732091 | Sep 1996 | EP |
| 883388 | Dec 1998 | EP |
| 634156 | May 1999 | EP |
| 1129676 | Sep 2001 | EP |
| 636352 | Jan 2002 | EP |
| 1196118 | Apr 2002 | EP |
| 765645 | Aug 2003 | EP |
| 1374805 | Jan 2004 | EP |
| 1421918 | May 2004 | EP |
| 1440675 | Jul 2004 | EP |
| 1470801 | Oct 2004 | EP |
| 732092 | Feb 2005 | EP |
| 1518521 | Mar 2005 | EP |
| 1226799 | May 2005 | EP |
| 1591082 | Nov 2005 | EP |
| 1779812 | May 2007 | EP |
| 1923079 | May 2008 | EP |
| 2417971 | Feb 1979 | FR |
| 2621243 | Apr 1989 | FR |
| 2653992 | May 1991 | FR |
| 2780636 | Jan 2000 | FR |
| 2787012 | Jun 2000 | FR |
| 2809302 | Nov 2001 | FR |
| 2835178 | Aug 2003 | FR |
| 1065354 | Apr 1967 | GB |
| 2293109 | Mar 1996 | GB |
| 2335145 | Sep 1999 | GB |
| 62205201 | Sep 1987 | JP |
| 8500992 | Feb 1996 | JP |
| 08224263 | Sep 1996 | JP |
| 2002291779 | Oct 2002 | JP |
| 2004167255 | Jun 2004 | JP |
| 2006015133 | Jan 2006 | JP |
| 7900739 | Oct 1979 | WO |
| 8906947 | Aug 1989 | WO |
| 9014806 | Dec 1990 | WO |
| 9014806 | Dec 1990 | WO |
| 9601725 | Jan 1996 | WO |
| 9623458 | Aug 1996 | WO |
| 9624311 | Aug 1996 | WO |
| 9624312 | Aug 1996 | WO |
| 9846171 | Oct 1998 | WO |
| 9927872 | Jun 1999 | WO |
| 9966864 | Dec 1999 | WO |
| 0209624 | Feb 2002 | WO |
| 03039609 | May 2003 | WO |
| 03101647 | Dec 2003 | WO |
| 2004058108 | Jul 2004 | WO |
| 2004069104 | Aug 2004 | WO |
| 2005009489 | Feb 2005 | WO |
| 2005009729 | Feb 2005 | WO |
| 2005072657 | Aug 2005 | WO |
| 2005087125 | Sep 2005 | WO |
| 2006014294 | Feb 2006 | WO |
| 2006130350 | Dec 2006 | WO |
| 2007106172 | Sep 2007 | WO |
| 2007108804 | Sep 2007 | WO |
| 2007119173 | Oct 2007 | WO |
| 2008100784 | Aug 2008 | WO |
| 2009046212 | Apr 2009 | WO |
| 2009128943 | Oct 2009 | WO |
| Entry |
|---|
| European Search Report for European Patent Application No. 09164160.5-1526, Jan. 4, 2010, 4 pgs. |
| European Search Report for European Patent Application No. 09164228.0-1526, Feb. 2, 2010, 6 pgs. |
| European Search Report for European Patent Application No. 09164235.5-1526, Dec. 22, 2009, 6 pgs. |
| European Search Report for European Patent Application No. 09164168.8-1526, Jan. 4, 2010, 6 pgs. |
| European Search Report for European Patent Application No. 11150648.1-2310, Apr. 7, 2011, 5 Pgs. |
| Shaw et al., “The Longitudinal Axis of the Knee and the Role of the Cruciate Ligaments in Controlling Transverse Rotation”, J.Bone Joint Surg. Am. 1974:56:1603-1609, 8 Pages. |
| Kurosawa, et al., “Geometry and Motion of the Knee for Implant and Orthotic Design”, The Journal of Biomechanics 18 (1985), pp. 487-499, 12 Pages. |
| Barnes, C.L., et al, “Kneeling Is Safe for Patients Implanted With Medical-Pivot Total Knee Arthoplasty Designs, Journal of Arthoplasty”, vol. 00, No. 0 2010, 1-6, 6 Pages. |
| Blaha, et al., “Kinematics of the Human Knee Using an Open Chain Cadaver Model”, Clinical Orthopaedics and Related Research, vol. 410 (2003); 25-34, 10 Pages. |
| Dennis, et al. “A Multi-Center Analysis of Axial Femorotibial Rotation After Total Knee Arthoplasty”, Clinical Orthopaedics 428 (2004); 180-189, 10 Pages. |
| Fan, Cheng-Yu, et al., “Primitive Results After Medical-Pivot Knee Arthroplasties: A Minimum 5 Year Follow-Up Study”, The Journal of Arthroplasty, vol. 25, No. 3 2010, 492-496, 5 Pages. |
| Freeman, M.A.R., et al., “The Movement of the Normal Tibio-Femoral Joint”, The Journal of Biomechanics 38 (2005) (2), pp. 197-208, 12 Pgs. |
| Fuller, et al., “A Comparison of Lower-Extremity Skeletal Kinematics Measured Using Skin and Pin-Mounted Markers”, Human Movement Science 16 (1997) 219-242, 24 Pages. |
| Hill, et al., “Tibiofemoral Movement 2: The Loaded and Unloaded Living Knee Studied by MRI” The Journal of Bone & Joint Surgery, vol. 82-B, No. 8 (Nov. 2000), 1196-1198, 3 Pages. |
| Karachalios, et al., “A Mid-Term Clinical Outcome Study of the Advance Medial Pivot Knee Arthroplasty”, www.sciencedirect.come, The Knee 16 (2009); 484-488, 5 Pages. |
| Komistek, et al., “In Vivo Flouroscopic Analysis of the Normal Human Knee”, Clinical Orthopaedics 410 (2003): 69-81, 13 Pages. |
| Komistek, et al., “In Vivo Polyethylene Bearing Mobility Is Maintained in Posterior Stabilized Total Knee Arthroplasty”, Clinical Orthopaedics 428 (2004): 207-213, 7 Pages. |
| Koo, et al., “The Knee Joint Center of Rotation Is Predominantly on the Lateral Side During Normal Walking”, Journal of Biomechanics, vol. 41 (2008): 1269-1273, 5 Pages. |
| Mannan, et al., “The Medical Rotation Total Knee Replacement: A Clinical and Radiological Review at a Mean Follow-Up of Six Years”, The Journal of Bone and Joint Surgery, vol. 91-B, No. 6 (Jun. 2009): 750-756, 7 Pages. |
| Moonot, et al., “Correlation Between the Oxford Knee and American Knee Society Scores at Mid-Term Follow-Up”, The Journal of Knee Surgery, vol. 22, No. 3 (Jul. 2009), 226-230, 5 Page. |
| Murphy, Michael Charles, “Geometry and the Kinematics of the Normal Human Knee”, Submitted to Masachusetts Institute of Technology (1990), 379 Pages. |
| Nakagawa, et al., “Tibiofemoral Movement 3: Full Flexion of the Normal Human Knee”, J.Bone Joint Surg. Am, vol. 82-B, No. 8 (2000). 1199-1200, 2 Pages. |
| Omori, et al., “The Effect of Geometry of the Tibial Polyethylene Insert on the Tibiofemoral Contact Kinematics in Advance Medical Pivot Total Knee Arthroplasty”, The Journal of Orthopaedics Science (2009), 14:754-760, 7 Pages. |
| Shakespeare, et al., “Flexion After Total Knee Replacement. A Comparison Between the Medical Pivot Knee and a Posterior Stabilised Knee”, www.sciencedirect.com, The Knee 13 (2006): 371-372, 3 Pages. |
| Walker, et al., “Motion of a Mobile Bearing Knee Allowing Translation of Rotation”, Journal of Arthroplasty 17 (2002): 11-19, 9 Pages. |
| European Patent Office, Search Report for App. No. 09164479.9-2310, mailed Nov. 4, 2009, 6 pages. |
| 2nd Int'l Johnson-Elloy Knee Meeting, Mar. 1987, 9 pages. |
| Operative Technique, Johnson Elloy Knee System, Chas F. Thackray, Ltd., 1988, 34 pgs. |
| Operative Technique the Turning Point, Accord, The Johnson/Elloy Concept, Chas FL Thackray Ltd, 32 pages (1998). |
| Restoration of Soft Tissue Stability, Johnson, et al., Chas. F. Thackray, Ltd., 21 pages (1998). |
| The Accuracy of Intramedullary Alignment in Total Knee Replacement, Elloy, et al, Chas F. Thackray Ltd, 12 pages (1992). |
| The Turning Point, Accord, The Johnson Elloy Concept, Chas F. Thackray Ltd, 20 pages (1998). |
| Prosthesis and Instrumentation the Turning Point, Accord, The Johnson/Elloy Concept, Chas F. Thackray Ltd, 8 pages (1988). |
| Five to Eight Year Results of the Johnson/Elloy (Accord) Total Knee Arthroplasty, Johnson et al, The Journal of Arthroplasty, vol. 8, No. 1, Feb. 1993, 6 pages. |
| Factors Affecting the Range of Movement of Total Knee Arthroplasty, Harvey et al, The Journal of Bone and Joint Surgery, vol. 75-B, No. 6, Nov. 1993, 6 pages. |
| Advice Notice (NI) Mar. 2000, Defect & Investigation Centre, Mar. 13, 2000, 3 pages. |
| The Johnson Elloy (Accord) Total Knee Replacement, Norton et al, The Journal of Bone and Joint Surgery (BR), vol. 84, No. 6, Aug. 2002, 4 pages. |
| Midvatus Approach in Total Knee Arthroplasty, A Description and a Cadaveric Study Determining the Distance of the Popliteal Artery From the Patellar Margin of the Incision, Cooper et al., The Journal of Arthoplasty, vol. 14 No. 4, 1999, 4 Pages. |
| Cari Zeiss, Zeiss Surfcomm 5000—“Contour and Surface Measuring Machines”, 2005, 16 pages. |
| Zimmer Nexgen Trabecular Metal Tibial Tray, The Best Thing Next to Bone, 97-5954-001-00, 2007, 4 pages. |
| European Search Report for European Patent Application No. 08164944.4-2310-2042131, Mar. 16, 2009, 12 pgs. |
| European Search Report for European Patent Application No. 08253140.1-2310, Dec. 23, 2008, 7 pgs. |
| European Search Report for European Patent Application No. 11150648.1-2310, Apr. 7, 2011, 4 pages. |
| European Search Report, European Application No. 10174439.9-1526, Dec. 20, 2010, 4 pages. |
| Biomet, Vanguard Mono-Lock Tibial System, Patented Convertible Tibial Bearing Technology, 2009, 2 Pages. |
| DePuy Inc., “AMK Total Knee System Product Brochure”, 1996, 8 pages. |
| DePuy Knees International, “Sigma CR Porocoat®,” 1 page, (downloaded May 12, 2011). |
| DePuy Orthopaedics, Inc., “AMK Total Knee System Legent II Surgical Techinque”, 1998, 30 pages. |
| DePuy Orthopaedics, Inc., “Sigma Fixed Bearing Knees—Function with Wear Resistance”, 2010, 0612-65-508 (Rev. 1) 20 pages. |
| DePuy PFC Sigma RP, “PFC Sigma Knee System with Rotating Platform Technical Monograph”, 1999, 0611-29-050 (Rev. 3), 70 pages. |
| Effects of Coronal Plane Conformity on Tibial Loading in TKA: A Comparison of AGC Flat Versus Conforming Articulations, Brent, et al, Orthopaedic Surgery, Surgical Technology International, XVIII, 6 pages. |
| European Search Report for European Patent Application No. 09164245.4-2310, Oct. 15, 2009, 5 pgs. |
| European Search Report for European Patent Application No. 06739287.8-2310, Mar. 16, 2010, 3 Pages. |
| European Search Report for European Patent Application No. 09164478.1-2310, Oct. 20, 2009, 6 Pages. |
| European Search Report for European Patent Application No. 09164478.1-2310, Apr. 28, 2010, 12 Pages. |
| European Search Report for European Patent Application No. 10162138.1, Aug. 30, 2010, 7 Pages. |
| Japanese Search Report for Japanese Patent Application No. 2009-501393, Oct. 26, 2010, 5 Pages. |
| PCT Notification Concerning Transmittal of International Prel. Report for Corresponding International App. No. PCT/US2006/010431, Jun. 5, 2007, 89 Pages. |
| Procedure, References Guide for Use with P.F.C. Sigma Knee Systems, 1998, 8 pages. |
| Signus Medizintechnik, “PEEK-OPTIMA®, The Polymer for Implants, Technical Information for the Medical Professional”, 7 pages. |
| The Effects of Conformity and Load in Total Knee Replacement, Kuster, et al, Clinical Orthopaedics and Related Research No. 375, Jun. 2000, 11 pages. |
| Zimmer, Trabecular Metal Monoblock Tibial Components, An Optimal Combination of Material and Design, www.zimmer.com, 2009, 3 pages. |
| Kessler et al., “Sagittal curvature of total knee replacements predicts in vivo kinematics,” Clinical Biomechanics 22(1): 52-58, 2007. |
| Wang et al., “Biomechanical differences exhibited during sit-to-stand between total knee arthroplasty designs of varying radii,” J Arthroplasty 21(8): 1196-9, 2006. |
| Saari et al., “The effect of tibial insert design on rising from a chair; motion analysis after total knee replacement,” Clin Biomech 19(9): 951-6, 2004. |
| Ranawat, “Design may be counterproductive for optimizing flexion after TKR,” Clin Orthop Rel Res 416: 174-6, 2003. |
| D'Lima et al., “Quadriceps moment arm and quadriceps forces after total knee arthroplasty,” Clin Orthop Rel Res 393:213-20, 2001. |
| Uvehammer et al., “In vivo kinematics of total knee arthroplasty: flat compared with concave tibial joint surface,” J Orthop Res 18(6): 856-64, 2000. |
| Dennis et al., “In vivo anteroposterior femorotibial translation of total knee arthroplasty: a multicenter analysis,” Clin Orthop Rel Res, 356: 47-57, 1998. |
| Clary et al., “Kinematics of Posterior Stabilized and Cruciate Retaining Knee Implants During an in Vitro Deep Knee Bend,” 54th Annual Meeting of the Orthopaedic Research Society, Poster No. 1983, Mar. 2008. |
| Wang et al., “A biomechanical comparison between the single-axis and multi-axis total knee arthroplasty systems for stand-to-sit movement,” Clin Biomech 20(4): 428-33, 2005. |
| Dennis et al., “Multicenter Determination of In Vivo Kinematics After Total Knee Arthroplasty,” Clin. Orthop. Rel. Res., 416, 37-57, 21 pgs. |
| Yoshiya et al., “In Vivo Kinematic Comparison of Posterior Cruciate-Retaining and Posterior Stabilized Total Knee Arthroplasties Under Passive and Weight-bearing Conditions,” J. Arthroplasty, vol. 20, No. 6, 2005, 7 pgs. |
| Bertin et al., “In Vivo Determination of Posterior Femoral Rollback for Subjects Having a NexGen Posterior Cruciate-Retaining Total Knee Arthroplasty,” J. Arthroplasty, vol. 17, No. 8, 2002, 9 pgs. |
| Suggs et al., “Three-Dimensional Tibiofemoral Articular Contact Kinematics of a Cruciate-Retaining Total Knee Arthroplasty,” JBJS-Am, vol. 88, No. 2, 2006, 10 pgs. |
| Dennis et al., “In Vivo Determination of Normal and Anterior Cruciate Ligament-Deficient Knee Kinematics,” J. Biomechanics, 38, 241-253, 2005, 13 pgs. |
| Li et al., “Anterior Cruciate Ligament Deficiency Alters the In Vivo Motion of the Tibiofemoral Cartilage Contact Points in Both Anteroposterior and Mediolateral Directions,” JBJS-Am, vol. 88, No. 8, Aug. 2006, 10 pgs. |
| Ries, “Effect of ACL Sacrifice, Retention, or Substitution on K After TKA,” http://www.orthosupersite.com/view.asp?rID=23134, Aug. 2007, 5 pgs. |
| Ferris, “Matching observed spiral form curves to equations of spirals in 2-D images, ”The First Japanese-Australian Joint Seminar, Mar. 2000, 7 pgs. |
| Goodfellow et al., “The Mechanics of the Knee and Prosthesis Design,” The Journal of Bone and Joint Surgery, vol. 60-B, No. 3, Aug. 1978, 12 pgs. |
| “Vanguard Complete Knee System,” Biomet, available at: http://www.biomet.com/patients/vanguard—complete.cfm, downloaded on Feb. 2009, (3 pages). |
| “NexGen Complete Knee Solution Cruciate Retaining Knee (CR),” Zimmer, available at: http://zimmer.com.au/ctl?template=PC&op=global&action=&template=PC&id=356, downloaded on Feb. 18, 2009, (1 page). |
| Scorpio Knee TS Single Axis Revision Knee System, Stryker Orthopaedics, http://www.stryker.com/stellent/groups/public/documents/web—prod/023609.pdf, (6 pages). |
| P. Johal et al, “Tibio-femoral movement in the living knee. A study of weight bearing and non-weight bearing knee kinematics using ‘interventional’ MRI,” Journal of Biomechanics, vol. 38, Issue 2, Feb. 2005, pp. 269-276, (8 pages). |
| Andriacchi, T.P., “The Effect of Knee Kinematics, Gait and Wear on the Short and Long-Term Outcomes of Primary Knee Replacement,” NIH Consensus Development Conference on Total Knee Replacement, pp. 61-62, Dec. 8-10, 2003, (4 pages). |
| Asano et al. “In Vivo Three-Dimensional Knee Kinematics Using a Biplanar Image-Matching Technique,” Clin Orthop Rel Res, 388: 157-166, 2001, (10 pages). |
| State Intellectual Property Office of People's Republic China; Chinese Search Report; Application No. 200910166935.6; Mar. 26, 2013; 2 pages. |
| Number | Date | Country | |
|---|---|---|---|
| 20140303740 A1 | Oct 2014 | US |
| Number | Date | Country | |
|---|---|---|---|
| 61077124 | Jun 2008 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 13540177 | Jul 2012 | US |
| Child | 14309466 | US | |
| Parent | 12488107 | Jun 2009 | US |
| Child | 13540177 | US |
