Abstract:
A ball and socket joint for implanting in the body is provided wherein the socket portion of the joint can have various orientations with respect to the patient&#39;s anatomy, and the orientation used for a particular patient can be selected and/or changed in situ, that is, during or after implantation of the joint. In addition, the configuration of the joint, e.g., constrained versus semi-constrained, as well as the materials making up the socket portion of the joint, e.g., plastic versus metal, can be selected and/or changed in situ.  The questions raised in reexamination request Nos. 90/004,732, filed Aug. 26, 1997 and 90/005,596, filed Jun. 22, 1999, have been considered and the results are reflected in this reissue.

Description:
CROSS REFERENCE TO RELATED APPLICATION 
     This is a continuation-in-part of copending application Ser. No. 473,431, filed Mar. 8, 1983 no U.S. Pat. No. 4,642,123. 
    
    
     BACKGROUND OF THE INVENTION 
     1. Field Of The Invention 
     This invention relates to artificial joints and in particular to artificial joints of the ball and socket type. 
     2. Description Of The Prior Art 
     As is well known in the art, artificial hip and shoulder joints conventionally employ ball and socket articulations. The socket is embedded in one bony structure, for example, the pelvis for a hip reconstruction. The ball is attached to an arm composed of a neck and a stem or shaft, the stem or shaft being embedded in another bony structure, for example, the femur for a hip reconstruction. 
     A number of methods are known for retaining the ball in the socket. In the most common method, referred to herein as the “semi-constrained” construction, the patient&#39;s own anatomy, i.e., his muscles, tendons and ligaments, are used to retain the ball within the socket. For this construction, a hemispherical socket typically is used which allows the ball and its attached arm the maximum amount of movement without contact of the arm with the edge of the socket. The surgeon, when installing such a semi-constrained joint, aligns the ball and socket as closely as possible with the patient&#39;s natural anatomy so that the patient&#39;s movements do not tend to dislocate the ball from the joint. As a general proposition, such precise alignment is easiest the first time an artificial joint is placed in a patient. Subsequent reconstructions are much more difficult to align because of deterioration of anatomical landmarks as a result of the first operation, the healing process after the operation and changes in the anatomy caused by the presence of the artificial joint. 
     In order to increase the inherent stability against dislocation of such semi-constrained constructions, it has become conventional to add a cylindrical portion to the hemispherical socket to make it deeper. Although the ball is not physically constrained by the socket by this adjustment, the ball does not have further to travel than if just a hemisphere had been used and thus some reduction in the propensity towards dislocation is achieved. Ball and socket joints of this type generally provide an arc or range of motion of approximately 115° when a 28 mm diameter sphere is used and the socket is made a few millimeters deeper than a hemisphere. Larger ranges of motion can be obtained by keeping the size of the arm attached to the ball constant and increasing the diameter of the ball. In this way, the angular extent of the arm relative to the ball becomes smaller. In the limit, if the ball could be made progressively larger and larger, a range of motion of 180° could be achieved. In practice, however, the largest sphere in common use in artificial joints, and in particular artificial hip joints, has a diameter of 32 mm and provides a range of motion of approximately 120°. It should be noted however, that such larger sphere sizes are not universally favored because frictional torque increases with diameter. 
     A recent study by the Mayo clinic, which appeared in December, 1982 edition of The Journal of Bone and Joint Surgery, reported a dislocation frequency of 3.2% for 10,500 hip joint implant procedures using the semi-constrained construction. Such dislocations essentially make the patient immobile and can necessitate a second operation. As discussed above, the critical alignment required for the semi-constrained construction is even more difficult to achieve when a second implantation is performed. Accordingly, even higher dislocation frequencies are encountered for second and subsequent implantations. 
     An alternative to the semi-constrained construction is the construction wherein the ball is physically constrained within the socket. In this construction, a spherically-shaped bearing surrounds the ball and serves as the socket. The bearing is attached to a fixation element which is embedded in, for example, the patient&#39;s pelvic bone. The bearing encompasses more than one-half of the ball and thus constrains the ball and its attached arm from dislocation. 
     The bearing is typically made from plastic, such as ultra-high molecular weight polyethylene (UHMWPE), or metal. For plastic bearings, the ball and bearing are usually assembled by forcing the bearing over the ball. The more of the ball which is encompassed by the bearing, the greater the required assembly force, and the greater the constraining force to prevent postoperative dislocation of the joint. In addition, the more that the bearing encompasses the ball, the smaller the range of motion for the ball prior to contact of the bearing with the arm attached to the ball. 
     An example of a constrained artificial joint employing a plastic bearing is shown in Noiles, U.S. Pat. No. 3,996,625. As can be seen in FIG. 1 of this patent, a plastic bearing  17  fitted with a metal reinforcing band (un-numbered) extends beyond the diameter of ball  24  so as to physically constrain the ball within the bearing. The bearing itself is attached to fixation element  12 . The metal reinforcing band is assembled over the lip of the opening of bearing  17  after that bearing has been forced over sphere  24 . The reinforcing band increases the force required to dislocate the joint. In practice, the design shown in FIG. 1 of U.S. Pat. No. 3,966,625 3,996,625 has been found to provide a range of motion of approximately 85° when a sphere diameter of 28 mm is used and to resist direct dislocating forces of several hundred pounds. 
     For constrained constructions such as that shown in U.S. Pat. No. 3,996,625, it has been found in use that a dislocating force is created when the neck of the arm attached to the ball impinges on the rim of the bearing. Because of the leverage associated with the arm and the long bone of the patient to which it is attached, e.g., the patient&#39;s femur, the dislocating force produced when the neck contacts the rim of the bearing can be considerable. For example, a force on the order of 25 pounds applied to a patient&#39;s leg can produce a dislocating force of over several hundred pounds because of the leverages involved. This type of dislocation force can be avoided by geometrically aligning the artificial joint with the patient&#39;s anatomy so that the neck does not come in contact with the rim of the bearing during normal motion of the patient&#39;s limb. That is, the leverage based dislocation forces can be avoided in the same way as dislocations are avoided in the seim-constrained semi- constrained  construction, i.e., through precise alignment of the artificial joint with the natural anatomy of the patient. Unfortunately, as is apparent from the geometry of the situation, the more the socket bearing encompasses the ball, the greater the restraining force on the ball, but at the same time the less the range of motion prior to the neck impinging upon the edge of the bearing to create undesired leverage. In practice, artificial hips having the construction shown in U.S. Pat. No. 3,996,625 have been found to suffer dislocation due to the leverage effect in fewer than 0.5% of the implantations performed. This is significantly better than the 3.5% dislocation frequency reported in the Mayo clinic study discussed above, but an even lower dislocation frequency is obviously desirable. 
     A constrained construction using a metal socket bearing is shown in Noiles, U.S. Pat. Re. 28,895 (reissue of U.S. Pat. No. 3,848,272). This construction provides approximately a 90° range of motion where the sphere diameter is 28 mm. In a practical sense, the metal bearing can be said to be non-dislocatable. The force required to extract the metal sphere from the enclosing metal socket bearing is more than several thousand pounds. Accordingly, is use, rather than the metal ball dislocating from the metal socket bearing, any overly severe dislocating leverage will cause the fixation element to be disrupted from the bone in which it has been embedded. 
     As a general proposition, metal balls in metal socket bearings are used in only a minority of joint reconstructions because the medical profession is not in agreement that a metal sphere in a metal bearing is as biologically acceptable as a metal sphere in a UHMWPE plastic bearing, even though clinical use over 15 years has failed to show the metal to metal joint to be inferior to a metal to plastic joint. 
     A third type of artificial ball and socket joint, referred to as an endoprosthesis, eliminates the fixation element associated with the socket and simply uses a ball surrounded by a plastic socket bearing in a spherical metal head, which head is placed in the patient&#39;s natural socket but not secured to bone. For this construction, the ball can rotate within the bearing up to the rim of the bearing (the bearing is greater than a hemisphere so as to be retained on the ball), and then the bearing and its attached head rotates in the patient&#39;s socket. As with the semi-constrained construction, anatomical alignment is used to avoid dislocations, in this case between the metal head and the natural socket. 
     In view of the foregoing, it is apparent that in semi-constrained and endoprosthesis hip joints, reconstructive geometry of the prosthesic components is critical in ensuring the stability of the prosthesis against dislocation. Moreover, in ball and socket constructions which constrain the elements against dislocation, the range of motion inherent in the prosthesis is reduced and thus because of the possibility of leverage type dislocations, similar demands are placed on the surgeon to establish the geometry of the reconstruction within rather narrow limits. 
     Accordingly, an object of this invention is to provide a ball and socket joint which provides the surgeon with increased latitude in geometric positioning of the prosthetic components over those ball and socket joints presently available. 
     A further object of the invention is to provide a ball and socket joint the materials and configuration of at least a portion of which can be selected and/or changed in situ, that is, during or after implantation of the joint in the patient. 
     An additional object of the invention is to provide a ball and socket joint including a bearing member which can be readily replaced in situ with either a bearing member of the same or of a different type depending on the patient&#39;s post-operative history. 
     Another object of the invention is to provide a ball and socket joint wherein (1) the socket portion of the joint has more than one orientation with respect to the ball portion of the joint, the preferred orientation being a function of the patient&#39;s anatomy, and (2) the orientation of the socket portion with respect to the ball portion can be selected and/or changed in situ, that is, during or after implantation of the joint in the patient. 
     A further object of the invention is to provide a prosthetic ball and socket joint of increased inherent range of motion which is readily assembled and disassembled at the surgical site. 
     An additional object of the invention is to provide a ball and socket bearing for an artificial joint which constrains the joint from dislocating and at the same time provides a range of motion which is greater than that available in the construction of the constrained type described above. 
     SUMMARY OF THE INVENTION 
     To achieve these and other objects, the invention, in accordance with one of its aspects, provides a ball and socket joint for implantation in a patient&#39;s body comprising a ball portion and a socket portion, 
     the ball portion including: 
     a ball; and 
     first fixation means for implantation in a first bony structure, said fixation means being connected to said ball; and 
     the socket portion including: 
     a bearing for receiving the ball; said bearing defining an orientation between itself and the patient&#39;s body; 
     second fixation means for implantation in a second bony structure; and 
     connecting means associated with the bearing and the second fixation means for connecting the bearing to the second fixation means in more than one orientation. 
     In accordance with a further one of its aspects, the invention provides a ball and socket joint for implantation in a patient&#39;s body comprising a ball portion and a socket portion, 
     the ball portion including: 
     a ball; and 
     first fixation means for implantation in a first bony structure, said fixation means being connected to said ball; and 
     the socket portion including: 
     a bearing for receiving the ball, said bearing being one member of a family of interchangeable bearings, the family including at least one member which is made from a different material or which has a different configuration or which is both made from a different material and has a different configuration from at least one other member of the family; 
     second fixation means for implantation in a second bony structure; and 
     connecting means associated with the bearing and the second fixation means for interchangeably connecting any bearing in the family to the second fixation means. 
     In accordance with an additional one of its aspects, the invention provides a ball and socket joint for implanting in the body which comprises: 
     a ball; 
     a cup with a spherical cavity, said cup to be affixed to bone; and 
     a bearing member surrounding a portion of the ball and rotatable within said spherical cavity about only one axis, said bearing member having an asymmetric opening therein, the opening having an angular extent of less than 180° in at least one plane. 
     In accordance with another one of its aspects, the invention provides an artificial joint of the ball and socket type for implantation in the body which comprises: 
     a ball; 
     a bearing for forming a socket to receive the ball, the bearing having an asymmetric opening therein, the opening having an angular extent of less than 180° in a first plane; 
     means for pivoting the bearing about an axis lying in a plant other than the first plane; and 
     means for affixing the means for pivoting to bone. 
     In accordance with another of its aspects, the invention provides a socket for a ball and socket joint for implantation in the body which comprises (1) a cup with a cavity, and (2) a bearing for receiving the ball of the ball and socket joint, said bearing being constrained to rotate within said cavity about a single axis. 
     In accordance with certain preferred embodiments of the invention, the asymmetric opening into the sockets is less in one direction than it is at 90° to this one direction. The socket bearing is movably retained within the cup about an axis which is (1) parallel to the face of the cup and (2) in the direction of the greater opening in the socket bearing. The socket bearing is retained within the cup by two stub half round pins integral with the cup and extending part way through the wall thickness of the socket. The axes of the half round pins coincide with an axis of the spherical cup like cavity and they are also coaxial in the direction of the greater opening in the socket bearing. 
     When the ball and the neck of the arm of the prosthesis move in the direction of the lesser opening in the socket bearing, the total range of motion is the sum of the arc of motion which the neck can make within the bearing plus the arc of motion which the bearing can make within the cup. The cup can be a hemisphere or even less. Rotation of the ball is limited by impingement of the neck against the rim of the cup, or alternatively, and most preferably, by limiting the rotation of the socket bearing so that the neck comes just up to, but not actually into contact with, the rim of the cup. In this regard, reference is made to copending U.S. patent application Ser. No. 553,518 to Alfred Frederick DeCarlo, Jr., filed simultaneously herewith and assigned to the assignee of the present application. This application, the pertinent portions of which are incorporated herein by reference, discloses a preferred system for limiting the rotation of the socket bearing to keep the neck of the arm of the prosthesis out of contact with the rim of the cup. 
     When the diameter of the ball is approximately the 28 mm in common use, and the socket bearing wall thickness is approximately 7 mm, the inner diameter of the cup, and thus the outer diameter of the bearing, is approximately 42 mm (28 mm+7 mm+7 mm). This outer diameter for the bearing is larger than the largest diameter sphere commonly used in semi-constrained artificial hip replacements, and thus the present constrained construction achieves a greater range of motion than the semi-constrained construction, and at the same time, restrains the ball within the socket. 
     When the ball and the neck move in the direction of the greater opening in the socket bearing, the neck contacts the flat side of a stub half round pin, rather than the rim of the cup, or alternatively, and most preferably, a web portion of the socket bearing in the region of the stub half round pins (see, for example, element  106  in FIGS. 13,  15  and  21  below). To allow the neck and ball to move through the same arc in this direction, the flat sides of the pins can be contoured. With this feature, the total range of motion in all quadrants, using the above dimensions, is approximately 135°. 
     To summarize, in accordance with the above preferred embodiments of the invention, when motion is in the plane of the stub pins, the total motion is by movement of the ball within the bearing. When motion is at 90° to the plane of the pins (the “90° plane”), the total motion is the sum of the motion of the ball within the bearing and the motion of the bearing within the cup. In other planes, the motion of the ball within the bearing is greater than it is in the 90° plane and the motion of the bearing within the cup is less than it is in the 90° plane. In this way, the invention provides a constrained ball and socket prosthesic joint with a total range of motion significantly greater than hitherto generally available. 
     In connection with artificial hip joints, it is advantageous to orient the cup in situ so that the axis of the stub pins is inclined according to the anatomical requirements of the patient as determined by the surgeon. For example, the axis can be inclined somewhat upward in the forward direction. In this manner almost all highly repetitive load bearing motions of the hip joint fall within the motion capability of the sphere within the socket bearing. Additional motion is furnished by movement of the bearing within the cup in such activities as crossing the legs when seated, or in significant abduction. To conveniently permit such orientation of the stub pins, in certain embodiments of the invention, the cup includes first and second portions, the first portion to be affixed to bone, the second portion having associated therewith the pin members are being moveable with respect to the first portion to provide a plurality of possible orientations for the axis of rotation of the bearing member within the spherical cavity. 
     In connection with both artificial hip joints and other types of ball and socket joints, it is advantageous for the surgeon to have as wide a range of joint configurations and materials to choose from as possible. It is particularly advantageous for the surgeon to be able to refine his selection of materials and configurations during the operative procedure, after he has seen the diseased joint and has a full appreciation of the patient&#39;s medical condition and anatomy. Along these same lines, it is also advantageous to be able to re-operate and change materials and/or joint configurations as a function of the patient&#39;s post-operative history without substantially disturbing the established fixation of the joint to bony structures. For example, a patient originally fitted with a semi-constrained joint may be found to be especially prone to dislocations so that a constrained construction, perhaps including a metal socket, would be more appropriate. 
     To achieve these types of flexibility, in accordance with certain preferred embodiments of the invention, a family of interchangeable socket bearings of different configurations and/or materials is provided to the surgeon. Each of the bearings includes means for interchangeably connecting the bearing to a fixation element for the socket portion of the joint in such a way that the bond between the fixation element and the patient&#39;s bone is not substantially disturbed by the connecting process. In view of this easy interchangeability, during the initial operation, the surgeon need not choose the specific socket bearing to be used until after completing the implantation of the fixation element, and during subsequent operations, if any, he can substitute a different bearing or replace a worn bearing without breaking the bond between the fixation element and the patient&#39;s bone. 
     In the description of the preferred embodiments which appears below, constructions are shown using both plastic and metal socket bearings, as well as bearings employing a combination of metal and plastic components. Also, various assembly and disassembly constructions are illustrated. It is to be understood, of course, that both the foregoing general description and the following detailed description are explanatory only and are not restrictive of the invention. 
     The accompanying drawings, which are incorporated in and constitute part of the specification, illustrate the preferred embodiments of the invention, and together with the description, serve to explain the principles of the invention. 
    
    
     BRIEF DESCRIPTION OF THE DRAWINGS 
     FIG. 1 is a perspective view of an artificial joint embodying the present invention. 
     FIG. 2 is an exploded view showing the components of the joint of FIG.  1 . 
     FIG. 3 is a cross-sectional view along lines  3 — 3  in FIG. 1 showing the ball and the socket bearing partially inserted into the cup. 
     FIG. 4 is a cross-sectional view along lines  3 — 3  of FIG. 1 showing the range of motion of the ball within the socket bearing with the socket bearing stationary. 
     FIG. 5 is a cross-sectional view along lines  3 — 3  of FIG. 1 showing the range of motion of the ball within the socket bearing when the socket bearing moves within the cup. 
     FIG. 6 is an exploded view of an alternate embodiment of the invention wherein the cup includes two portions which are moveable relative to each other. 
     FIG. 7 is a cross-sectional view along lines  7 — 7  in FIG. 6 after the joint has been assembled. 
     FIG. 8 is a cross-sectional view along lines  8 — 8  in FIG. 6 after the joint has been assembled. 
     FIG. 9 is an alternate embodiment of the embodiment shown in FIGS. 6-8 wherein a two piece metal socket bearing is used. 
     FIG. 10 is a cross-sectional view along lines  10 — 10  in FIG. 9 after the joint has been assembled. 
     FIG. 11 is an exploded view showing an alternative method for rotatably retaining the socket bearing within the cup. 
     FIG. 12 is a cross-sectional view along lines  12 — 12  in FIG. 11 after the joint has been assembled. 
     FIGS. 13 and 14 show alternative socket bearings for use with the present invention. 
     FIG. 15 is an exploded view of an artificial joint similar to that shown in FIGS. 6-8 but employing a system of the type disclosed in the DeCarlo patent application referred to above to limit the range of motion of the socket bearing within the joint. 
     FIG. 16 is a cross-sectional view along lines  16 — 16  in FIG.  15 . 
     FIG. 17 is a cross-sectional view along lines  17 — 17  of FIG.  15 . 
     FIG. 18 is a perspective view of the outer surface of the bearing member of FIG.  15 . 
     FIGS. 19 and 20 are schematic diagrams illustrating the relationships between the angular extents of the various components of the artificial joint shown in FIGS. 15-17. 
     FIG. 21 is an exploded view of an artificial joint of the semi-constrained type embodying the present invention and employing a system of the type disclosed in the DeCarlo patent application referred to above to limit the range of motion of the socket bearing within the joint. 
     FIG. 22 is a cross-sectional view along lines  22 — 22  in FIG.  21 . 
     FIG. 23 is a cross-sectional view along lines  23 — 23  in FIG.  21 . 
     FIG. 24 is an exploded view of an artificial joint of the constrained type constructed in accordance with the present invention and including a metal reinforcing band to increase the amount of force required to dislocate the joint. This embodiment also employs a system of the type disclosed in the DeCarlo patent application referred to above to limit the range of motion of the socket bearing within the joint. 
     FIG. 25 is a cross-sectional view along lines  25 — 25  in FIG.  24 . 
     FIG. 26 is a perspective view of a plastic socket bearing constructed in accordance with the present invention and designed to produce a completed joint of the non-rotating, constrained type. 
     FIG. 27 is a front view of the bearing of FIG.  26 . 
     FIG. 28 is a cross-sectional view along lines  28 — 28  in FIG.  27 . 
     FIG. 29 is a cross-sectional view along lines  29 — 29  in FIG.  27 . 
     FIG. 30 is a side view of the bearing of FIG.  26 . 
     FIG. 31 is a side view of a plastic socket bearing constructed in accordance with the present invention and designed to produce a completed joint of the non-rotating, semi-constrained type. 
     FIG. 32 is a side view of a plastic socket bearing similar to the bearing of FIG. 31 but including a lip to help restrain dislocations of the completed joint. 
     FIG. 33 is an exploded view of an artificial joint of the non-rotating, constrained type constructed in accordance with the present invention and employing a metal socket bearing. 
     FIG. 34 is a cross-sectional view along lines  34 — 34  in FIG.  33 . 
    
    
     DESCRIPTION OF THE PREFERRED EMBODIMENTS 
     With reference now to the drawings, wherein like reference characters designate like or corresponding parts throughout the several views, there is shown in FIG. 1 an assembly  20  of ball or sphere  10 , socket bearing  12  and cup  14  for a prosthetic joint. The neck  16  of arm  30  is intermediate ball  10  and stem or shaft  18 , which stem or shaft is fixed to, for example, the femur bone at the time of implant surgery. 
     FIG. 2 shows in more detail socket bearing  12  of assembly  20 . The preferred material for bearing  12  is ultra-high molecular weight polyethylene (UHMWPE). Inner spherical bearing surface  21  of bearing  12  is concentric with outer spherical bearing surface  22 . Cylindrical surfaces  24  are coaxial with each other and with the center of spherical surfaces  21  and  22  and are tangent to surfaces  26 . Small barb-shaped protuberances  28  serve a detent function described below. 
     In the plane passing through the lines P—P in FIG. 2, socket bearing  12  encompasses less than one half of ball  10 . In the plane passing through the lines S—S, the socket bearing encompasses more than half of ball  10 . 
     Owing to the resilience and elasticity of the plastic material of socket bearing  12 , socket bearing  12  can be snapped over ball  10 . The amount of interference between the equator of the ball and socket bearing  12  depends on the angular extent of the bearing&#39;s opening in the plane passing through the lines S—S in FIG.  2 . the The amount of interference should be such as will cause an elastic deformation of socket bearing  12  while the bearing is being assembled over the ball  10 . To aid in assembly, socket bearing  12  can be heated to a non-destructive temperature (for example 70°-80° C. for UHMWPE). Plastic in general, and UHMWPE in particular, has a large coefficient of thermal expansion and such thermal expansion due to heating significantly aids in assembly. 
     As shown in FIG. 2, cup  14  has a hemispherical inner surface  32  and two coaxial stub half pin members  34  which are structurally integral with cup  14 . The pins  34  are shown bevelled at  36 . Recesses  38  are provided at the inner rim of the cup at locations 90° displaced from the pins  34 . The exterior surface  40  of cup  14  is of any conventional contour for fixation in bone whether by use of cement, or without cement by means of impaction, screwing in, or by bone ingrowth into porous metal or the like. Cup  14  is normally made of metal, and it is to be understood that the metal used is to be structurally and biologically suitable for surgical implantation. 
     A step midway in the process of assembly is schematically shown in FIG. 3 where bearing  12  has been positioned against neck  16  at  42  and the bearing  12  and arm  30  have been inserted into cup  14  with neck  16  contacting the rim of cup  14  at  44 . Cylindrical surface  24  of bearing  12  engages stub pin  34  as the entering rim  46  of bearing  12  contacts inner surface  32  of cup  14 . At this time the bearing  12  is pressed firmly enough into cup  14  to compress protuberance  28 , allowing bearing  12  to be rotated clockwise about ball  10  and pin  34  while it is in contact with inner spherical surface  32 . 
     When bearing  12  has been rotated sufficiently for protuberance  28  adjacent rim  46  to reach recess  38 , protuberance  28  expands to resist rotation in the reverse direction and thereby resist disassembly of the ball and socket joint  20  unless a tool is inserted into recess  38  to again compress protuberance  28  as rotation in the disassembly direction is started. 
     The assembled joint is shown in FIG. 1, where the neck  16  of arm  30  can move through the arc from the position shown to that which is symmetrically opposite. That is, the neck of the prosthesis can move in the plane through lines P—P of FIG. 2 from a position of contact with lower stub pin  34  to contact with upper stub pin  34 . When ball  10  has a diameter of 28 mm and the outer diameter of bearing  12  is 42 mm, the arc or range of motion of neck  16  is somewhat greater than 135°, depending on the design of the neck  16 . 
     To achieve this same range of motion in the plane through lines S—S in FIG. 2 requires two motions. First, as shown in FIG. 4, the neck  16  and ball  10  move through the angle A by the ball  10  turning inside the socket bearing  12 , at the completion of which neck  16  contacts the rim of bearing  12 . Thereafter, as shown in FIG. 5, to achieve the full range of motion A′, ball  10  and bearing  12  rotate in unison, at the completion of which neck  16  contacts cup  14 . 
     Normally, until neck  16  reaches the rim of socket bearing  12 , socket bearing  12  will remain stationary relative to cup  14 . This is so because frictional torque is the product of friction force times the distance from the center of rotation. Given similar materials, finish and geometric accuracy, so that the coefficient of friction for ball  10  and cup  14  against bearing  12  are equal, the frictional force on inner surface  21  will be the same as that on outer surface  22  when ball  10  rotates within cup  14 , because the load transmitted across the two bearing surfaces is the same. Since the radius to the outer surface  22  is the greater, the frictional torque at the outer surface will be greater and thus motion will occur along surface  21  rather than surface  22 . 
     For major oscillation of ball  10  and neck  16  in the plane through lines P—P in FIG. 2, the entire excursion is due to rotation of ball  10  within bearing  12 . The total possible oscillation in all planes is the same, however, the contribution made by rotation of bearing  12  increases as the plane of oscillation moves from that including the lines P—P to that including the lines S—S in FIG.  2 . 
     As described above, bearing  12  constrains ball  10  from dislocation. Further, socket bearing  12  is constrained within cup  14  by cylindrical surfaces  24  being journaled by the stub half pins  34  in all positions of bearing  12  as bearing  12  moves to allow arm  30  to move through angle A′. In the complete assembly  20 , the constraint against dislocation of ball  10  by deformation of plastic bearing  12  is greater in magnitude than the force required to assemble bearing  12  over ball  10  because, in addition to the fact that the assembly operates at the body temperature of 37° C., the bearing  12  is now itself constrained against the deflection of dislocation by being captured within metal cup  14 . 
     FIGS. 6,  7  and  8  show an alternate construction intended to (1) facilitate final assembly at the operative site, and (2) for hip joint replacements, allow the axis of stub pins  34  to be inclined accordingly to the anatomical requirements of the patient as determined by the surgeon. Cup  14  now includes two portions—portion  64  which is affixed in the patient&#39;s bone, and retaining ring portion  74  which carries stub pins  34  and is engageable with portion  64  at a number of locations to provide a plurality of orientations for the axis through pins  34  about which socket bearing  12  rotates. Portion  64  is shaped to accept and hold retaining ring  74  by means of bayonet spaces  68  and lugs  70 . Inner spherical surface  72  is continuous with spherical surface  76  of ring  74 . Ring  74  carries stub half pin members  34 , has recesses  38  and bayonet lugs  78 . A particularly preferred construction for portion  64 , and, in particular, for the exterior surface of this portion, is disclosed in copending U.S. patent application Ser. No. 553,519 to Douglas G. Noiles, filed simultaneously herewith and assigned to the assignee of the present application. The pertinent portions of this application are incorporated herein by reference. 
     With the embodiment shown in FIGS. 6-8, the portion  64  of cup  14  is implanted in the patient&#39;s bone by conventional techniques, or, most preferably, by the techniques described in the above-referenced copending application to Douglas G. Noiles. Ball  10  and bearing  12  are assembled into retaining ring  74  after stem  18  of arm  30  has been implanted in, for example, the patient&#39;s femur, the assembly procedure being the same as that described above with reference to FIG. 3 except that protuberance  28  is compressed only once it contacts the back surface of ring  74 . The sub-assembly of ball  10 , bearing  12  and retaining ring  74  is then inserted into portion  64  in any of the several angular positions the bayonet lug fittings will permit. A fraction of a turn in either direction will engage the lugs  78  of ring  74  under lugs  70  of portion  64 . Alternatively, lugs  78  can be beveled at either their right or left hand leading edges so that insertion by rotation in only one direction is facilitated, e.g., clockwise rotation. The engagement of bayonet lugs  78  and  70  is locked by conventional means, such as by one or more pins  80 . Holes  79  and  81  for such locking pins can be precisely made in the cooperating parts at the time of manufacture. Although only one hole  81  is shown in FIGS. 6 and 7, a hole would normally be drilled at each bayonet space  68  so that ring  74  can be locked in place for any of its possible orientations. 
     An embodiment of the present invention similar to that shown in FIGS. 6-8 but employing the system disclosed in the DeCarlo patent application referred to above is shown in FIGS. 15-20. In this embodiment, spherical surface  72  has associated therewith pin or projection  50 . This projection is located at the geometric pole of the spherical cavity formed by spherical surfaces  72  and  76 . As shown in the figures, pin  50  has sloping sides  60 . 
     Projection  50 , in combination with aperture  13  formed in outer surface  22  of bearing member  12 , serves to constrain the rotation of bearing  12  so as to prevent the bearing from being rotated out of the spherical cavity once the joint is assembled and to limit the rotation of the bearing so as to keep neck  16  just out of contact with the rim of ring  74 , e.g., on the order of a half a millimeter above the rim. In particular, bearing  12  can rotate only to the point where polar pin  50  and one of the end walls  52  or  54  of aperture  13  are in engagement. As discussed below, this constrained condition for bearing  12  occurs automatically as the joint is assembled without any additional assembly steps. Also, the constraining of socket bearing  12  within the joint is accomplished irrespective of the angular orientation chosen for retaining ring  74  with respect to body portion  64  of cup  14 . 
     Aperture  13  has a long axis parallel to side walls  56  and  58  and a short axis at 90° to side walls  56  and  58 . The angular extent of aperture  13  along its short axis is sufficient to accommodate polar pin  50 . The angular extent of aperture  13  along its long axis determines the range of motion of socket bearing  12 . As discussed above, a particularly preferred range motion for bearing  12  is one in which neck  16  is kept just out of contact with ring  74 . In this case, as shown in FIGS. 19-20, the angular extent (α) of aperture  13  along its long axis is determined by: (1) the maximum angular extent (β) of socket bearing  12 : (2) the minimum angular extent (γ) of cup  14 ; (3) the angular extent (δ) of polar pin  50 ; and the angular offset (ε) of neck  16  from cup  14 . In particular, the angular extent of aperture  13  is given by: 
     
       
         α=β+δ−γ−ε.  
       
     
     Similar relationships can be derived for other desired ranges of motion for socket bearing  12 . 
     The placement of pin  50  at the pole of the spherical cavity formed by surfaces  72  and  76  allows retaining ring  74  to be inserted into body portion  64  of cup  14  in any of the possible orientations provided by the mating of bayonet lugs  78  with bayonet lugs  70 . That is, once socket bearing  12  is rotated about stub pins  34  until at least some portion of aperture  13  is located over the central axis of ring  74 , ring  74  can be mated with body portion  64  in any of their possible relative orientations, because, for each of those orientations, aperture  13  will slip over projection  50 . Since placing aperture  13  about pin  50  results in the restraining of bearing  12  in cup  14  without any further action by the surgeon, it can be seen that assembly of the joint automatically produced the desired restraining function. 
     A typical sequence of steps for implanting the prosthesis of the embodiment shown in FIGS. 15-20 in a patient are as follows. Stem  18  of arm  30  is implanted by conventional techniques in, for example, the patient&#39;s femur bone. Body portion  64  of cup  14  can also be implanted by conventional techniques, or, most preferably, by the techniques described in the above-referenced copending application to Douglas G. Noiles. Bearing  12  is assembled into ring  74  and then ball  10  is forced into bearing  12 . Alternatively, bearing  12  can first be placed on ball  10  and that combination assembled into ring  74 . In either case, the sub-assembly of ball  10 , bearing  12  and retaining ring  74  is then inserted into body portion  64  in any of the several angular positions the bayonet lug fittings will permit with polar pin  50  sliding into aperture  13 . A fraction of a turn in either direction will engage the lugs  78  of ring  74  under lugs  70  of portion  64 . Alternatively, as discussed above, lugs  78  can be beveled at either their right or left hand leading edges so that insertion by rotation in only one direction is facilitated, e.g., clockwise rotation. To aid in the rotation of ring  74 , the ring can include apertures  122  for engagement with a spanner wrench or the like. Note that because of the polar location of pin  50 , ring  74  and its attached bearing  12  can be rotated to engage lugs  78  and  70  irrespective of where pin  50  is located along the length of aperture  13 . The engagement of bayonet lugs  78  and  70  is locked by one or more screws  83  which pass through openings  100  and  98  in lugs  70  and  78 , respectively, and then through holes  102  to engage the bone into which cup  64  has been implanted. 
     For hip joints, the possibility of a number of orientations for the axis of rotation of bearing  12  is used to place that axis in an orientation in which the greater required range of motion is aligned approximately with axis P—P. For example, the axis of rotation can be oriented upward in the forward direction to achieve this result. In this way, almost all of the highly repetitive lead load bearing motions of the joint will occur along or close to this axis. As discussed above, motions along or near to the axis of rotation of bearing  12  consist primarily of ball  10  moving in bearing  12 , rather than bearing  12  moving in cup  14 . As also discussed above, the frictional torques involved further favor movement of ball  10  in bearing  12 . Accordingly, by placing the axis of rotation of bearing  12  in a favorable orientation, most repetitive motion will occur by movement of ball  10 . This is an important advantage because it means that the joint will have low friction in that friction increases with the diameter of the moving member and ball  10  has a smaller diameter than bearing  12 . Put another way, by orienting the axis of rotation of the bearing  12  in the manner described above, the joint of the present invention for the great majority of motions of the patient&#39;s limb exhibits the frictional behavior of a small ball, e.g., a 28 mm ball, while providing a range of motion corresponding to a large ball, e.g., a 42 mm ball. 
     FIGS. 9 and 10 show another embodiment employing retaining ring  74  in which the socket bearing comprises two metal half bearings  82 . A groove  86  is formed along the junction of the bearings and ends short of the edge of the bearing to form shoulders  88 . Metal half bearings  82  are brought together to encompass ball  10 , and the ball, half bearings, retaining ring  74  and portion  64  of cup  14  are assembled in the same manner as described above in connection with FIGS. 6-8. 
     Screws  94  having screw heads  96  are conveniently used both to lock lugs  70  and  78  in place and to prevent socket bearing  12  from rotating back out of retaining ring  74 . Screw heads  96  ride in groove  86  and engage shoulders  88  when socket bearing  12  has been moved through its full range of motion about stub pins  34 . Lugs  70  and  78  have appropriate openings  100  and  98 , respectively, to receive screws  94  and allow the screws to be engaged with, in this case, threaded screw holes  102 . Although only two openings  100  and two threaded screw holes  102  are shown in FIGS. 9 and 10, such openings and threaded holes would normally be provided at each lug  70  so that ring  74  can be locked in place for any of its possible orientations. 
     As shown in FIGS. 9 and 10, and most clearly in FIG. 10, screw heads  96  for the present embodiment lie above the plane of the front face of retaining ring  74 . So as to provide the same range of motion of socket bearing  12  for this embodiment as for the embodiment of FIGS. 6-8, stub pins  34  also lie above this plane, so that the axis of rotation of socket bearing  12  is in the plane of screw heads  96 . For this arrangement, the motion of bearing  12 , and thus arm  30 , is limited by screw head  96  contacting shoulder  88 , rather than by neck  16  contacting retaining ring  74 . 
     A further embodiment of the present invention is shown in FIGS. 11 and 12. This embodiment employs means other than half stub pins  34  to define the axis of rotation of socket bearing  12  within cup  14 . In particular, a dovetail arrangement is used wherein male portion  90  of the dovetail is attached to socket bearing  12  and female portion  92  of the dovetail is cut into surface  32  of cup  14 . Socket bearing  12  and cup  14  are assembled in a manner similar to that shown in FIG.  3 . That is, after socket bearing  12  has been placed over ball  10 , the ball and socket bearing are moved into cup  14  until the center of ball  10  lies at the center of the cup&#39;s spherical cavity. Thereafter, socket bearing  12  is rotated so that male portion  90  and female portion  92  of the dovetail engage with each other. To retain socket bearing  12  within cup  14 , screws  94  can be inserted into threaded holes  104  in cup  14  so as to block the outward passage of male portion  90  of the dovetail from cup  14 . 
     FIGS. 13 and 14 show alternate socket bearings for use with the present invention. 
     In FIG. 13, cylindrical surfaces  24  do not extend completely through the wall of bearing  12 , but rather stop approximately half way through to leave webs  106 . So as to provide as large a range of motion of arm  30  in the plane through lines P—P as possible (see FIG.  2 ), the webs extend to just above height of stub pins  34  at the end of bevels  36 . In this way, as discussed above, the motion of ball  10  in the plane through lines P-P is limited by arm  16  contacting webs  106 . The webs, although small, help restrain ball  10  within bearing  12 . 
     FIGS.  14  and  21 - 23  show embodiments of bearing  12  which do not physically contrain constrain ball  10 . For these embodiments, inner surface  21  of bearing  12  has a cylindrical shape  108  beyond its equator. This provides a semiconstrained type of construction having a greater depth than presently available. Such a bearing can be used with the other components of the present invention to provide the advantages, discussed above, of (1) producing a wider range of motion, e.g., on the order of 135°, and (2) providing a level of friction characteristic of a small ball for the majority of the motions of the patient&#39;s limb. 
     FIGS. 24-25 show another embodiment of the present invention wherein a plastic bearing  12  is fitted at its rim  118  with a metal reinforcing band  120  to produce a constrained joint able to withstand higher dislocation forces than, for example, the joints including plastic bearings shown in FIGS. 1-8 and  15 - 20 . For this joint, the order of assembly is first to combine bearing  12  with ring  74 , then to force the bearing  12  over ball  10  and finally to assemble band  120  to the rim of bearing  12 . If the ball portion of the joint has already been implanted in the patient, this assembly order means that band  120  has to be placed over ball  10  before the bearing is mounted onto the ball. 
     The constructions of FIGS. 6-8,  9 - 10 ,  15 - 20 ,  21 - 23  and  24 - 25  illustrate various joint configurations which can be interchangeably connected to body  64  by means of bayonet lugs  70  and  78  on body  64  and ring  74 , respectively. These configurations share the common characteristic that bearing  12  is free to rotate about stub pins  34  in the final assembled joint. They differ from one another in the degree of constraint imposed on the ball by the bearing and/or the types of materials used to construct the bearing. Because the bearings are free to rotate, these joints, when applied to hip reconstructions, also share the characteristic that there is a preferred orientation of the joint with respect to the patient&#39;s anatomy, namely, an orientation wherein most of the highly repetitive load bearing motions of the joint occur along or close to the axis of rotation of the bearing. 
     FIGS. 26-34 show further examples of joint components which can be interchangeably connected to body  64  by means of bayonet lugs  70  and  78  on body  64  and, in this case, on bearing  12 , respectively. These joint configurations have the common characteristic that bearing  12  is stationary with respect to body  64 . As with the joints of the prior examples, these joints differ among themselves in the degree of constraint imposed on the ball by the bearing and/or the types of materials used to construct the bearing. 
     More particularly, FIGS. 26-30 show a construction of the constrained type employing a plastic socket bearing to which has been added a metal reinforcing band  120  at rim  118  of the bearing so as to increase the bearing&#39;s ability to withstand dislocation forces. As shown in the figures, the bearing includes a recess  126  at its pole which allows the bearing to be used with a body  64  which includes a polar pin  50 . Of course, if body  64  does not have a polar pin, the bearing need not have recess  126 . 
     Assembly of a completed joint using this bearing is accomplished as follows. First, bearing  12  is forced over ball  10  and band  120  is forced over the bearing&#39;s rim  118 . If the ball portion of the joint has already been implanted in the patient, band  120  must be placed over ball  10  before bearing is mounted onto the ball. The sub-assembly of ball  10 , bearing  12  and reinforcing band  120  is then inserted into body  64  in any of the several angular positions the bayonet lug fittings will permit. Polar pin  50  is received in recess  126  during this process. Since the bearing of FIGS. 26-30 is symmetric and thus does not define a particular orientation with respect to the patient&#39;s anatomy, the specific oritentation orientation of the bearing with respect to body  64  is immaterial. Once placed into body  64 , a fraction of a turn in either direction will engage the lugs  78  on the bearing under the lugs  70  of body  64 . If desired, as described above, lugs  78  can be beveled at either their right or left hand leading edges so that insertion by rotation in only one direction is facilitated, e.g., clockwise rotation. To aid in the rotation of bearing  12 , the bearing can include slots  128  for engagement with a spanner wrench or the like. The engagement of bayonet lugs  78  and  70  is locked by one or more screws  83  which pass through openings  100  and  98  in lugs  70  and  78 , respectively, and then through holes  102  in body  64  to engage the bone in which cup  64  has been implanted (see FIGS.  33  and  34 ). 
     FIG. 31 shows another plastic socket bearing of essentially the same design as the bearing of FIGS. 26-30 except that rather creating a constrained joint, this bearing produces a semi-constrained joint. That is, the bearing of FIG. 31 does not encompass more than one half of ball  10  and thus does not constrain the ball within the joint. Assembly of a joint using this bearing simply involves inserting and locking the bearing in body  64  using bayonet lugs  78  and one or more bone screws, and then placing ball  10  into bearing  12  using the standard techniques employed in semi-constrained surgical reconstructions. 
     FIG. 32 shows another plastic socket for use in a semi-constrained reconstruction, in this case with an added lip  130  to help restrain dislocations of ball  10  from the bearing. The lip can be conveniently formed by gradually sloping the front surface of the bearing as shown in FIG. 32. A suitable slope is on the order of 9°. Unlike the symmetric bearings of FIGS. 26-31, the bearing of FIG. 32 does define an orientation between itself and the patient&#39;s anatomy. Accordingly, when installing this bearing, the surgeon will choose an orientation of the bearing with respect to body  64  which will place lip  130  in the most advantageous position to inhibit dislocation. Other than this orientation step, the installation procedure for a joint using this bearing is identical to the installation procedure described above for the bearing of FIG.  31 . 
     FIGS. 33-34 show a non-rotating, constrained joint employing a metal bearing. The bearing is composed of two half-bearings  132  which carry bayonet lugs  78 . During assembly of the joint, half-bearings  132  are placed about ball  10  and then held in place by plastic retaining ring  134 . The sub-assembly of ball  10  and bearing  12  is then inserted into body  64  in basically the same manner as the bearing of FIGS. 26-30. Typically, body  64  is made of a titanium alloy, e.g., an alloy containing 6% aluminum and 4% vanadium (see ASTM Spec. No. F136-79), while bearing halves  132 , as well as ball  10 , are made of a cobalt-chromium alloy. As is known in the art, titanium alloys are not wear resistant when in moving contact with cobalt-chromium alloys and thus continual relative movement between a titanium part and a cobalt-chromium part will eventually result in significant wearing of the titanium part. 
     To prevent such wearing due to relative movement, the joint of FIGS. 33-34 includes wedge  136  which serves to force half-bearings  132  into tight engagement with body  64 . Wedge  136  passes through slot  140  in bearing  12  and into recess  144  in retaining ring  134 . The head portion  148  of the wedge is struck with a hammer or the like after bearing  12  has been positioned in body  64 . The hammer blow forces the bearing halves apart and locks them into position with respect to body  64 . 
     To prevent wedge  136  from working loose over time, bone screw  83  can be used to engage the head of the wedge as shown in FIG.  34 . So that the wedge can easily be removed, e.g., during replacement of the bearing by a different type of bearing, the underside of head  148  can be cambered so that the wedge can readily be pried away from the bearing. Because the wedging process causes the bearing halves  132  to move away from each other by pivoting about their point of contact opposite the location of the wedge, the interior surfaces of the bearing halves can be contoured so that a spherical surface is formed only after the outward movement of the bearing halves. Alternatively, the interior surfaces can be made spherical since the slight amount of play between ball  10  and bearing  12  caused by the wedging process can normally be tolerated in the completed joint. 
     As can be seen most clearly in FIG. 33, edge  146  of bearing  12  is not symmetric. More particularly, this edge allows ball  10  to move through one angular range in the plane of FIG. 34 and a relatively larger angular range in the plane orthogonal to the plane of FIG.  34 . Accordingly, when installing this bearing, the surgeon will choose an orientation of bearing  12  in body  64  which causes the plane corresponding to the relatively larger range of angular motion to coincide as closely as possible with the plane in which the patient&#39;s limb normally moves through its largest range of angular motion. 
     The nine joint configurations shown in FIGS. 6-8,  9 - 10 ,  15 - 20 ,  21 - 23 ,  24 - 25 ,  26 - 30 ,  31 ,  32 , and  33 - 34  are each interchangeable with each other. This interchangeability gives the surgeon the flexibility of being able to choose, in situ, any of these configurations or any other configuration constructed to mate with body  64 . In this way, a more perfect match between the requirements of the patient and the characteristics of the artificial joint is achieved. 
     From the foregoing, it is evident that the present invention provides a constrained ball and socket joint which has a range of motion greater than that generally available in artificial joints whether of the constrained or semi-constrained type. Moreover, the present invention provides an artificial joint which can be oriented in the patient to provide low friction movement of a ball of relatively small diameter for most of the patient&#39;s repetitive activities. The limiting factor in providing the increased range of motion is the outside diameter of the bearing. Accordingly, within anatomical limits, it is advantageous for the bearing outside diameter to be as large as possible. 
     The increased range of motion provided by the present invention allows the patient to move his limb further than heretofore possible in constrained joints without the arm of the prosthesis impinging on the edge of the bearing. Accordingly, there is less likelihood of dislocation when plastic bearings are used or disruption of the bond between the fixation element and the bone to which it is attached when metal bearings are used. Moreover, when the range of motion of the present joint is greater than the patient can take advantage of, the surgeon is afforded greater latitude for variation in the orientation of the prosthetic components with respect to the patient&#39;s anatomy without the hazard of impingement. 
     In addition to these orientability and range of motion aspects, the present invention, by providing interchangeable sockets, also gives the surgeon the ability to select the most appropriate prosthesis for the patient&#39;s specific requirements both during the initial operation and, if necessary, during re-operations. As demonstrated by the examples described above, the surgeon, in accordance with the present invention, has a diverse family of ball and socket joints to choose from extending from semi-constrained, fixed bearings made of plastic through constrained, rotating bearings made of metal, as well as a variety of configurations in between. This choice plainly permits a better match between the requirements of the patient and the capabilities of the prosthesis. 
     Numerous modifications and variations of the present invention are possible in light of the above teachings. For example, ball  10 , socket bearing  12  and retaining ring  74  can be provided to the surgeon as a unit, rather than being assembled at the surgical site. Also, metal socket bearings can be used with one piece cups, such as cup  14  shown in FIG. 1, rather than with a retaining ring as shown in FIGS. 9 and 10. Furthermore, various connecting means other than bayonet spaces and lugs can be used to attach ring  74  or bearing  12  to body  64 , such as, snap rings. In addition, a variety of socket bearings other than those specifically illustrated herein can be used to make up the family of interchangeable bearings supplied to the surgeon. It is therefore understood that within the scope of the appended claims, the invention may be practiced otherwise than as specifically described.