Cutting instrument for oblong acetabular cups

Abstract: Apparatus for cutting a second spherical cavity in a patient's pelvis adjacent to and displaced from a first spherical cavity in the pelvis, comprising: (a) guide means for engaging the surface of the first spherical cavity; (b) cutting means having an axis for cutting the second spherical cavity; and (c) means for holding the guide means and the cutting means in a predetermined spatial relationship with respect to one another so that the axis of the cutting means is displaced from a parallel axis through the center of the first spherical cavity.

Description: BACKGROUND OF THE INVENTION 1. Field of the Invention This invention relates to apparatuses for cutting a patient's bone to prepare an oblong cavity for a prosthesis and, in particular, for an acetabular prosthesis used in a hip joint replacement. 2. Description of the Prior Art Total hip joint replacements comprise a femoral component and an acetabular component. The femoral component is implanted in the patient's femur and the acetabular component is implanted in the acetabular cavity in the patient's pelvis. The normal acetabular cavity is generally spherically shaped. Accordingly, as illustrated in Figure 1, during initial hip joint replacement, a spherically-shaped cavity 10 is prepared in the pelvis 14 for the great majority of patients, and the outer surface of the acetabular prosthesis 12 has a generally spherical shape to fit in this cavity. See, for example, Mallory et al., U.S. Patents Nos. 4,883,491 and 4,944,759. Over the past two decades, millions of hip joint replacements have been performed. As time has progressed, a significant number of these implants have failed by either or both of the femoral or acetabular components becoming loose. In the case of the acetabulum, a loose prosthesis often erodes bone in the direction of the applied forces during use, i.e., in the superior and posterior directions. This is particularly true where the loosened prosthesis had been implanted using bone cement. As a result, during a second or further repeated hip joint replacement, the surgeon often finds that the once spherical cavity in the pelvis has become elongated in a posterior-superior direction, as shown at 16 in Figure 2 and 32 in Figure 23. Also, in some cases, elongated acetabular cavities may be found for patients undergoing their first hip joint replacement. The classical way to deal with this problem of an elongated acetabular cavity has been to fill a portion of the cavity with a bone graft to create as best as possible a spherical cavity in its normal location. As is evident, this approach suffers from a variety of problems, including availability of bone for the bone graft, mechanical difficulties of securing the bone graft to the host bone, failure of the bone graft to provide and maintain long term mechanical support for the prosthesis, and the hazard of the spread of certain infectious diseases. In some cases, customized elongated or oblong acetabular prostheses have been used to address this condition. Figures 2-5 illustrate this approach to the problem. As shown in these figures, a block of metal has been machined to produce prosthesis 18 having outer surface 20 which is composed of two spherical sections 22 connected by a cylindrical section 24. In these custom prostheses, a cavity 26 has been machined in the body of metal to receive a suitable bearing element 28 (see Figure 4) Although these oblong prostheses have represented an improvement over the bone graft approach, they have suffered from a number of problems of their own. First, they have been expensive to manufacture because a separate machining setup has been required for each prothesis geometry which has been produced. As a result, oblong prostheses of this construction have been used in only a limited number of cases. Even more importantly, the existing oblong prostheses have not fully responded to the anatomical and physiological needs of the patient. This problem is illustrated in Figure 4. As shown in this figure, the angle in the coronal plane (X-Z plane in Figure 17) between the face of the bearing element 28 of the prior art oblong prostheses and the transverse plane (X-Y plane in Figure 17) is typically 60 or more degrees. This orientation results from the contour of the bone and the elongation of the cavity. In medical terminology, the prosthesis is said to have an insufficient amount of adduction, i.e., the angle between the face of the prosthesis and the transverse plane is greater than the preferred angle. (Note that the amount of adduction increases as the angle decreases.) For joint stability, however, the preferred angle of the face of the bearing element in the coronal plane is on the order of 45 degrees or less. See F. Pipino and P.M. Calderale, "A Biequatorial Acetabular Cup for Hip Prosthesis," Acta Orthopaedica Belgica , Vol. 48, pages 5-13 (1980) and F. Pipino and P.M. Calderale, "A Biequatorial Hip Prosthesis," Panminerva Medical , Vol. 25, pages 231-239 (1983). See also Figure 19. Thus, the configuration of Figure 4 is typically more than 15° from the preferred orientation. Moreover, the greater the elongation of the cavity, the greater the departure from the preferred orientation. In terms of function, such a geometry means that the patient will have a significantly higher likelihood of dislocation during use. In addition to the orientation in the coronal plane, the functionality of the prosthesis is also affected by the orientation of the face of the bearing element in the transverse plane (X-Y plane in Figure 17). In this case, the preferred angle between the face of the bearing element and the sagittal plane (Y-Z plane in Figure 17) is on the order of 15° anteverted. See Figure 20. (Note that the amount of anteversion increases as the angle increases.) Due to the curvature of the pelvis and the usual direction of erosion and elongation, the prior art oblong acetabular prostheses tend to assume an orientation which is less anteverted or, in some cases, may even be retroverted. The magnitude of this problem also becomes greater as the elongation of the cavity becomes greater. Again, in terms of function, orientations which are less anteverted or are retroverted mean that the patient will have a higher likelihood of dislocation during use. An alternative construction is shown in Figure 6 wherein an asymmetric bearing element 30 having a skewed face is used. For a skew which is orientable (see Noiles U.S. Patent No. 4,678,472), some compensation can be made for the misorientation in both the coronal and transverse planes. Figure 6 shows a typical improvement in the coronal plane. As shown in this figure, skewing the face of the bearing element can bring the angle in the coronal plane down to around 50°. However, full correction cannot be satisfactorily achieved in this way because a sufficiently large extension of the plastic bearing would be mechanically inadequate to withstand the loads applied during use. Similarly, some improvement in inadequate anteversion can be achieved in the transverse plane, but again full correction cannot be achieved without jeopardizing the mechanical strength of the bearing. U.S. Patent No. 3 633 583 discloses an orthopaedic single-blade bone cutter having a rotary cutter head. The head has a substantially hemispherical surface coaxial with its axis of rotation and is longitudinally and medially split into two halves by a diametral slot intersecting the axis of rotation. A single flat blade having a longitudinally curved edge is positioned in the slot and projects marginally beyond the surface of revolution. The blade edge is opposite the bevel on opposite sides of its mid point to form two longitudinally curved rotatable shearing edges. The cutter head may be formed as a concave or a convex hemispherical surface. SUMMARY OF THE INVENTION According to a first aspect of the present invention there is provided apparatus for cutting a second spherical cavity in a patient's pelvis adjacent to and displaced from a first spherical cavity in the pelvis, the apparatus comprising: (a) guide means having an external surface for engaging the surface of the first spherical cavity, said external surface defining a geometric center of the guide means; (b) cutting means having an axis for cutting the second spherical cavity; and (c) means for maintaining the guide means and the cutting means in a predetermined spatial relationship with respect to one another so that the axis of the cutting means is displaced from a parallel axis through the geometric center of the guide means. According to a second aspect of the present invention there is provided apparatus for cutting a second spherical cavity in a patient's pelvis adjacent to and displaced from a first spherical cavity in the pelvis, the apparatus comprising: (a) guide means having an external surface for engaging the surface of the first spherical cavity, said external surface defining a geometric center of the guide means; (b) cutting means for cutting the second spherical cavity, said cutting means having a geometric center and comprising a drive shaft; and (c) means for maintaining the guide means and the cutting means in a predetermined spatial relationship with respect to one another whilst enabling the cutting means to be moved relative to the guide means to a point where the geometric centers of the guide means and cutting means lie on a line which is substantially perpendicular to the drive shaft. BRIEF DESCRIPTION OF THE DRAWINGS Figure 1 is a stylized drawing showing the implantation of a spherically-shaped acetabular cup in a spherical cavity formed in a patient's pelvis. The cross-section through the patient's pelvis in this figure and in Figures 2, 4, and 6 is in the coronal plane. Figure 2 is a stylized drawing showing an oblong acetabular cup adjacent to a cavity which has become elongated in a posterior and superior direction as a result of the loosening and removal of a prior acetabular prosthesis. Figure 3 is a perspective view of a prior art oblong acetabular prosthesis formed from a single block of metal and having no provision for adduction or anteversion correction. Figure 4 is a stylized drawing showing the implantation of a prior art prosthesis of the type shown in Figure 3. As illustrated in this figure, the angle between the face of bearing 28 and the transverse plane is 60° or more, which is undesirable. Figure 5 is a cross-sectional view through the longitudinal axis of the prosthesis of Figure 3. Figure 6 is a stylized drawing shoving the implantation of a prior art prosthesis of the type shown in Figure 3 equipped with a bearing element 30 having a skewed face. The angle between the face of bearing element 30 and the transverse plane is approximately 50° which is better than the 60+° of Figure 4, but is still unsatisfactory. Figure 7 is a perspective view of a prosthesis to be implanted in the cavity made in accordance with the present invention, the prosthesis being constructed from a single block of metal and having a bearing-receiving cavity which has been skewed to provide adduction correction. Figure 8 is a plan view of the prosthesis of Figure 7. Figure 9 is a cross-sectional view along lines 9-9 in Figure 8 of the prosthesis of Figure 7 with a skewed bearing element inserted into the prosthesis' skewed cavity. The centers of the two spherically-shaped portions of the outside surface of the cup are identified by the reference numbers 5 and 7. Figure 10 is a perspective view of a prosthesis to be implanted in a cavity constructed in accordance with the present invention, the prosthesis being made from a single block of metal and having a bearing-receiving cavity which has been skewed to provide both adduction and anteversion correction. Figure 11 is an exploded, perspective view of a prosthesis to be implanted in a cavity constructed in accordance with the present invention, the prosthesis being made from two components which when united produce an outside surface for the prosthesis which includes a cusp. Figure 12 is a plan view of the cavity-containing component of the prosthesis of Figure 11. Figure 13 is a side view of the assembled prosthesis of Figure 11. Figure 14 is an exploded, perspective view of a prosthesis to be implanted in a cavity constructed in accordance with the present invention, the prosthesis being made from two components which when united produce an outside surface for the prosthesis which has a central cylindrical portion. Figure 15 is a plan view of the cavity-containing component of the prosthesis of Figure 14. Figure 16 is a side view of the prosthesis of Figure 14. Figure 17 is a stylized, perspective view of a person showing the coronal (X-Z), transverse (X-Y) and sagittal (Y-Z) planes. A stylized portrayal of the person's pelvis is shown at 34. Figure 18 is an enlarged view of the stylized pelvis 34. A stylized portrayal of the normal acetabulum is shown at 36. Figure 19 is a coronal (X-Z) section along lines 19-19 in Figure 18 showing the desired adduction angle of approximately 45° for an acetabular prosthesis. Figure 20 is a transverse (X-Y) section along lines 20-20 in Figure 18 showing the desired anteversion angle of approximately 15° for an acetabular prosthesis. Figure 21 is a perspective view of a surgical instrument according to the present invention. Figure 22 is a sectional view along lines 22-22 of the surgical instrument of Figure 21. Figure 23 is a perspective view of a portion of a human pelvis showing the cavity formed in the pelvis through the use of the instrument of Figure 21. Figures 24-26 are stylized views of prostheses to be implanted in cavities constructed by instruments in accordance with the present invention showing the prosthesis' longitudinal plane and the plane defined by the opening of the prosthesis' bearing-receiving cavity. The prosthesis of Figure 24 includes only adduction correction and thus can be used in either the patient's right or left hip. The prostheses of Figures 25 and 26 include both adduction and anteversion correction and thus can be advantageously used in the right hip for the Figure 25 prosthesis and the left hip for the Figure 26 prosthesis. 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 Figures 7-9 an oblong acetabular cup 40 to be implanted in a cavity constructed in accordance with the present invention. As shown in these figures, the prosthesis is made from a single block of material, e.g., a block of metal, and includes body 42 in which is formed cavity 13 for receiving bearing element 44. In addition to bearing-receiving cavity 13, body 42 also includes apertures 48 which 1) allow the surgeon to visualize the underlying bone as the prosthesis is implanted and 2) can receive bone screws for affixing the prosthesis to the pelvis. Bearing 44 is retained in cavity 13 by means of 1) complimentary bayonet spaces 50 and lugs 52 formed at the mouth of the cavity which receive and mate with corresponding spaces and lugs formed on the outside surface of the bearing, and 2) bone screws (not shown) which pass through apertures 46 and lock the bearing to the prosthesis. See Noiles U.S. Patents Nos. 4,801,301 and 4,960,427. Other means for securing the bearing to the cup can of course be used, if desired. As shown in Figure 7, prosthesis 40 has a longitudinal axis defined by line OEG and a longitudinal plane which is defined by lines OEG and FEH and which contains line AOC. For the particular construction shown, points 0 and E are the centers of two spherically-shaped surfaces which form the ends of the oblong cup. The opening into bearing-receiving cavity 13 defines a "first" plane which contains lines AOC and DOB. In accordance with the invention, the opening, into cavity 13 and thus the first plane is skewed with respect to the prosthesis' longitudinal plane so as to provide adduction correction or anteversion correction or both adduction correction and anteversion correction. The prosthesis of Figures 7-9 shows the case of adduction correction only. The first plane is rotated out from the longitudinal plane by adduction correction angle GOB in Figure 7 which is also shown as angle A in Figure 9. The magnitude of the adduction correction angle will generally be in the range of from about 10° to about 30°, although larger or smaller adduction correction angles can be used for particular applications if necessary or desired. Prostheses having adduction correction angles of different magnitudes can be provided to the surgeon so that a selection can be made at the time of implantation to better meet the needs of individual patients. For example, the surgeon can be given a choice between prostheses having adduction correction angles of 10, 20, and 30 degrees. As shown in Figure 7, the first plane and the longitudinal plane intersect along line AOC. Because only adduction correction is being performed, this line of intersection is perpendicular to the longitudinal axis of the oblong prosthesis, i.e., line AOC is perpendicular to line OEG. As discussed below, when both adduction and anteversion correction is performed, the angle between the longitudinal axis and the line of intersection is greater than 90° for a right hip cup and less than 90° for a left hip cup. When only anteversion correction is performed, the line of intersection between the first plane and the longitudinal plane is the longitudinal axis or, in the general case, is parallel to that axis. Figure 9 shows the use of skewed bearing element 44 with cup 40. This combination allows for even greater adduction correction, i.e., correction through the sum of angles A and B in Figure 9. Also, by using an orientable bearing (see Noiles U.S. Patent No. 4,678,472), some anteversion correction can be achieved for a cup having only adduction correction. Conversely, the use of an orientable, skewed bearing allows some adduction correction for a cup having only anteversion correction. Further, by using an orientable, skewed bearing with a cup having both adduction and anteversion correction, relatively fine adjustments of the levels of adduction and anteversion correction can be made in situ. This allows the surgeon to achieve as good a match as possible between the configuration of the prosthesis and the needs of the patient. In particular, it gives the surgeon the needed flexibility to address the twin goals of maximum range of motion and minimum likelihood of dislocation. It is important to note that by skewing the opening to cavity 13, bearing 44 has strong mechanical support from the body of the cup even though the bearing's orientation is substantially different from that of the cup's longitudinal plane/axis. Figure 10 shows an oblong cup having both adduction and anteversion correction. As in Figure 7, points 0 and E are the centers of two spherically-shaped surfaces which form the ends of the oblong cup. Also, as in Figure 7, the longitudinal axis of the cup of Figure 10 is defined by line OEG, the longitudinal plane of the cup is defined by lines OEG and FEH, the first plane contains lines AOC and DOB, and the adduction correction angle is GOB. In this case, however, the longitudinal plane does not contain line AOC, but rather contains the reference line JOK which is parallel to the reference line FEH. The angle between lines AOC and JOK, i.e., angle JOA, represents the anteversion correction angle for this cup. The magnitude of the anteversion correction angle will generally be in the range of from about 10° to about 30°, although larger or smaller anteversion correction angles can be used for particular applications if necessary or desired. As with the adduction correction angle, prostheses having anteversion correction angles of different magnitudes, e.g., prostheses having anteversion correction angles of 10, 20, and 30 degrees, can be provided to the surgeon. Since anteversion corrections are in relation to the patient's midsagittal plane, different prostheses are needed for the right and left hips. Specifically, for a right hip, the first plane is rotated to the patient's left relative to the prosthesis' longitudinal plane, while for the left hip, it is rotated to the right. This effect is shown in Figures 25 and 26, where 54 is the prosthesis' longitudinal plane, 56 is the first plane, 58 is the prosthesis' longitudinal axis, and 60 is the line of intersection between the first plane and the longitudinal plane. For comparison, Figure 24 shows a prosthesis having only adduction correction. The prosthesis of Figure 25, like that of Figure 10, is for a right hip and thus first plane 56 is rotated to the left relative to longitudinal plane 54. The Figure 26 prosthesis, on the other hand, is for a left hip and thus first plane 56 has been rotated to the right relative to the longitudinal plane. This aspect of correction can also be seen by examining the angle W between the prosthesis' longitudinal axis 58 and the line of intersection 60 between the first plane and the longitudinal plane. As shown in Figure 25, for a right hip, angle W is greater than 90°, while as shown in Figure 26, for a left hip, it is less than 90°. For comparison, as shown in Figure 24, for a prosthesis with just adduction correction and no anteversion correction, angle W equals 90°. Figures 11-13 and 14-16 show particularly preferred constructions for the prostheses to be used in cavities opened by the present invention. In each case, body 42 of the prosthesis is composed of two components which engage and mate with each other along cylindrically-shaped surfaces. In this way, anteversion corrections of different magnitudes and right and left hip prostheses can be easily constructed from a common set of components by simply joining the components together at different offset angles. In Figures 11-13, component 62 includes bearing-receiving cavity 13 and component 64 extends away from component 62 to produce the overall oblong shape of the cup. The outside, bone-engaging surfaces of both components are portions of a sphere. Accordingly, when the components are joined together, the outside surface of the assembled cup includes cusp 70 at the intersection between the two spherical portions. The overall length of the cup can be adjusted by varying the size of component 64, i.e., by using more or less of a sphere to form the outside surface of this component. Also, the outside surfaces of the components can have different spherical radii to provide further flexibility in the overall configuration of the cup. As shown most clearly in Figure 13, face 72 of component 62 meets face 74 of component 64 at an angle so as to provide the assembled prosthesis with adduction correction. Components 62 and 64 are joined together by means of cylindrically-shaped external surface 66 on component 62 and cylindrically-shaped internal surface 68 on component 64. To produce anteversion correction, the components are rotated relative to one another along these surfaces. When the desired degree and direction of anteversion correction has been selected, the components are permanently joined together by, for example, electron beam welding in a vacuum in the case of metal components. As mentioned above, the prosthesis of Figures 11-13 includes cusp 70 in its outside surface. A surgical instrument 94 suitable for preparing a cavity in a patient's pelvis for receiving such a prosthesis is shown in Figures 21 and 22. Instrument 94 comprises spherical shell 84 and spherical reamer 76, which includes cutting blade 78 and chip clearance groove 80. The reamer is driven by conventional means (not shown) through shaft 82. . Extending out from shaft 82 is platform 86 to which is attached shell 84. As explained below, the shell serves as a guide for cutting a second spherical cavity in the patient's pelvis adjacent to a first spherical cavity. The radii of reamer 76 and shell 84 correspond to the radii of the bone-engaging surfaces of components 64 and 62, respectively. Accordingly, the reamer and the shell can have different radii if components 64 and 62 have different radii. Platform 86 includes holes 90 through which threaded bolt 88 can pass to attach shell 84 to the platform. Multiple holes are provided so that instrument 94 can be used with prostheses of different sizes, e.g., prostheses having larger and smaller components 64. Although only two adjustments are shown, more adjustments can, of course, be provided if a greater variety of prostheses is to be made available to the surgeon. The implantation of a prosthesis using the instrument of Figures 21 and 22 is illustrated in Figure 23. First, the surgeon prepares first spherical cavity 96 using a conventional reamer. Next, the surgeon cuts second spherical cavity 98 using instrument 94. Specifically, the surgeon places shell 84 into the first spherical cavity and uses the shell as a guide to cut the second cavity at a predetermined distance from the first cavity. The result is finished cavity 32 which includes a ridge of bone 100 which will mate with cusp 70 in the outside surface of the prosthesis. Figures 14-16 show a second two-component embodiment of the invention, again using cylindrically-shaped surfaces 66 and 68 at the interface between the components to allow for easy anteversion correction. In this case, component 102 includes bearing-receiving cavity 13 and component 104 extends away from component 102 to produce the overall oblong shape of the cup. The outside, bone-engaging surface of component 102 is a portion of a sphere, while the outside, bone-engaging surface of component 104 includes a spherical portion 106 and a cylindrical portion 108. For this embodiment, adjustments in the overall length of the prosthesis can be easily made by simply changing the length of cylindrical portion 108. As shown most clearly in Figure 16, face 110 of component 102 meets face 112 of component 104 at an angle so as to provide the assembled prosthesis with adduction correction. The embodiment of Figures 14-16 has two, spaced-apart, outside, spherically-shaped surfaces, and thus an instrument of the type shown in Figures 21 and 22 can advantageously be used to produce a cavity in the patient's pelvis for this prosthesis as described above. Because the prosthesis does not include a cusp, a conventional reamer is advantageously used to form a continuous cylindrical connection between the spaced-apart, spherically-shaped sections of the cavity resulting from the use of instrument 94. The finished cavity thus includes two spherically-shaped portions and a cylindrically-shaped portion corresponding to the outside surface of the prosthesis. The prostheses to be used in cavities opened by the instrument of the invention are preferably implanted by being press fit into the prepared cavity in the patient's bone. Bone screws which pass through screw holes 48 can be used to provide additional fixation for the prosthesis. Preferably, the outside surface of the prosthesis includes porous coating 113 to provide long term fixation through bone ingrowth. To provide a tight initial fit between the prosthesis and the prepared cavity, the prosthesis with its porous coating is dimensioned approximately 1 millimeter larger in diameter than the cavity. The above prostheses can be made of conventional materials known in the art for making artificial joint replacements. For example, the body of the cup can be made of a Ti 6Al 4V alloy, the porous coating can be chemically pure titanium, and the bearing can be ultra high molecular weight polyethylene. Other materials now known or subsequently developed can of course be used. Similarly, the prostheses can be manufactured using conventional techniques known in the art such as through the use of computer controlled machine tools. Although specific embodiments of the invention have been described and illustrated, it is to be understood that modifications can be made without departing from the invention's scope. For example, the outside surface of the prosthesis to be used in the cavity opened by the instrument of the invention can have configurations other than those shown and methods different from those illustrated can be used to join together the various parts of the prosthesis. Along these same lines, the geometry of the prosthesis can be described in terms different from those used above. For example, the prosthesis can be described in terms of the shape of its outer surface and the central axis of the cavity which receives the bearing element. As discussed above, the prosthesis' outer surface includes two spherically-shaped portions, the centers of which spheres are spaced-apart and thus define a line. In the prior art oblong prostheses, the central axis of the bearing-receiving cavity was perpendicular to the line between the centers of the spheres. In contrast, in accordance with the present invention, when adduction correction is performed, the central axis intersects the line between the centers at an angle other than 90°. A variety of other variations and modifications which do not depart from the scope of the invention will be evident to persons of ordinary skill in the art from the disclosure herein. The following claims are intended to cover the specific embodiments set forth herein as well as such modifications, variations, and equivalents.

Claims: Apparatus (94) for cutting a second spherical cavity (98) in a patient's pelvis (14) adj acent to and displaced from a first spherical cavity (96) in the pelvis (14), the apparatus comprising: (a) guide means (84) having an external surface for engaging the surface of the first spherical cavity (96), said external surface defining a geometric center of the guide means (84); (b) cutting means (76, 78, 80, 82) having an axis for cutting the second spherical cavity (98); and (c) means (86, 88, 90) for maintaining the guide means (84) and the cutting means (76, 78, 80, 82) in a predetermined spatial relationship with respect to one another so that the axis of the cutting means (76, 78, 80, 82) is displaced from a parallel axis through the geometric center of the guide means (84). Apparatus (94) for cutting a second spherical cavity (98) in a patient's pelvis (14) adjacent to and displaced from a first spherical cavity (96) in the pelvis (14), the apparatus comprising: (a) guide means (84) having an external surface for engaging the surface of the first spherical cavity (96), said external surface defining a geometric center of the guide means (84); (b) cutting means (76, 78, 80, 82) for cutting the second spherical cavity (98), said cutting means having a geometric center and comprising a drive shaft (82); and (c) means (86, 88, 90) for maintaining the guide means (84) and the cutting means (76, 78, 80, 82) in a predetermined spatial relationship with respectto one another whilst enabling the cutting means (76, 78, 80, 82) to be moved relative to the guide means (84) to a point where the geometric centers of the guide means (84) and cutting means (76,78, 80,82) lie on a line which is substantially perpendicular to the drive shaft (82).

Inventors: CHRISTIE MICHAEL, DECARLO ALFRED F, MCTIGHE TIMOTHY, NOILES DOUGLAS C, CHRISTIE, MICHAEL, DECARLO, ALFRED F., MCTIGHE, TIMOTHY, NOILES, DOUGLAS C.
Applicants: JOINT MEDICAL PRODUCTS CORP, JOINT MEDICAL PRODUCTS CORPORATION
Application year: 1992
Main classification: A61B17
IPC codes: A61F2, A61B17