# Patent

## Title
Method for optimization of joint arthroplasty component design

## Abstract

Methods and devices are disclosed for the optimization of shoulder arthroplasty component design through the use of computed tomography scan data from arthritic shoulders.

## Background
CROSS-REFERENCES TO RELATED APPLICATIONS
This application is a divisional application of U.S. patent application Ser. No. 14/300,805 filed Jun. 10, 2014, which is a continuation-in-part of U.S. patent application Ser. No. 13/818,738 filed Feb. 25, 2013 which is a 371 application of PCT/US11/049686 filed Aug. 30, 2011 which claims priority from U.S. Provisional Patent Application No. 61/379,222 filed Sep. 1, 2010, and U.S. Provisional Patent Application No. 61/379,634 filed Sep. 2, 2010.


STATEMENT REGARDING FEDERALLY SPONSORED RESEARCH
Not Applicable.
BACKGROUND OF THE INVENTION
1. Field of the Invention
The invention relates to a method for the optimization of joint arthroplasty component design, and more particularly to a method for the optimization of shoulder arthroplasty component design through the use of computed tomography scan data.
2. Description of the Related Art
Various prostheses for the replacement of the shoulder joint are known. In one example shoulder prosthesis, the upper portion of the humerus is replaced by a humeral component including (i) a stem that extends into a bore formed within the humerus and (ii) a generally hemispherical head portion that is connected to the stem. The hemispherical head of the humeral component articulates with a complementary concave section of a glenoid component mounted within the glenoid cavity of the scapula. This type of shoulder prosthesis may be called a “primary” or “total” prosthesis. In another example shoulder prosthesis, often called a “reverse” or “inverted” prosthesis, the glenoid component includes a convex section that articulates with a complementary concave section of the head of the humeral component.
One alternative to total shoulder replacement is referred to as shoulder hemiarthroplasty. In one version of this procedure, the humeral head is replaced with a generally hemispherical head that may or may not include a connected stem. The glenoid cavity of the scapula is not replaced with a glenoid component, but may be refinished in a way that gives it a smooth surface and a shape which matches the generally hemispherical replacement head. Another version of this procedure can use a glenoid component with resurfacing of the humeral head.
Several deficiencies have been found in currently available shoulder arthroplasty systems including glenoid sizes (primary and reverse) and humeral sizes that are not based on the anatomic distribution. In addition, the advent of reverse arthroplasty for the treatment of proximal humerus fractures has also changed the requirements for an appropriate fracture stem. Specific design features are necessary to make the fracture stem appropriate for hemiarthroplasty and reverse arthroplasty use. Although resurfacing of the humerus has become popular, the designs are not based on an anatomic distribution. The instrumentation that is currently available is inadequate and may lead to significant malposition in version and inclination.
Prior magnetic resonance imaging and cadaveric studies of glenohumeral anatomy have been performed on shoulders without arthritis (Iannotti et al., “The normal glenohumeral relationships. An anatomical study of one hundred and forty shoulders”, J Bone Joint Surg Am. 1992; 74:491-500; Hertel et al., “Geometry of the proximal humerus and implications for prosthetic design”, J Shoulder Elbow Surg., July/August 2002, pp. 331-338; and Boileau et al., “The Three-Dimensional Geometry Of The Proximal Humerus—Implications For Surgical Technique And Prosthetic Design”, J Bone Joint Surg [Br], 1997; 79-B:857-865). However, in reality, shoulder arthroplasty is not performed on normal shoulders. Shoulder arthroplasty is performed in patients with arthritis in the setting of cartilage loss and usually associated bone loss. In order to make properly sized implants that will accommodate patients with arthritis, it is important to understand the anatomy of these patients.
Typically, the designing surgeon has used a system with three glenoid sizes. In one study, it was determined that the distribution of glenoid components used in total shoulder arthroplasty was as follows: 4% large, 40% medium, and 56% small. One can see that based on component use, the sizing of these implants is not optimal. If glenoid component sizes are not optimal, there may be issues related to perforation of the glenoid by fasteners used in attaching the glenoid component to the scapula. In addition, certain components may be too large for smaller patients resulting in component overhang and potentially leading to violation of important neurovascular structures. Thus, it could be hypothesized that the preference for small glenoid components may result from the desire to avoid glenoid perforation and/or avoid component overhang. However, larger glenoid components can lead to a better fitting prosthesis and greater stability.
There has been increasing interest in the use of augmented glenoid components in shoulder arthroplasty. Bone graft has been used in the past to manage bone deficiency; however there has been a high rate of graft resorption. It has also been clearly recognized that removal of the remaining hard cortical bone to create a neutral surface can compromise fixation by leaving the surgeon with only soft cancellous bone resulting in insufficient implant support for certain patients. In addition, excess reaming results in medialization and shortening the remaining rotator cuff lever arm with functional implications. Therefore, there has been increasing interest in the use of augmented glenoid components.
In FIG. 5A, one example augmented glenoid component 102 for use in a total shoulder system is shown. The glenoid component 102 has a single component plastic body 104. A concave articular surface 105 of the body 104 provides a smooth bearing surface for the head portion of the humeral component implanted into the humerus. The thickness of the plastic body 104 gradually increases from an anterior edge 106 to a posterior edge 108 thereof thereby creating a relatively smooth, arcuate-shaped medial base surface 110 from which a number of posts or pegs 112 extend. It can be seen that the augmented glenoid component 102 has an augment that has a defined slope along the entire posterior surface of the glenoid. An augment thickness can be defined as the thickness of the posterior edge 108 minus the thickness of the anterior edge 106.
In FIG. 5B, another example augmented glenoid component 114 for use in a total shoulder system is shown. The augmented glenoid component 114 includes a body 116 having a concave articular surface 118 on one end thereof. The concave surface 118 of the body 116 provides a smooth bearing surface for the head portion of the humeral component implanted into the humerus. The body 116 includes a step 120 on or from a body surface 122 opposite the concave surface 118. The step 121 forms a portion of the posterior edge 121 of the body 116. The augmented glenoid component 114 also includes an anchor peg 123 and a plurality of stabilizing posts pegs 124. It can be seen that the augmented glenoid component 114 has an augment that is a step on the posterior aspect of the glenoid. An augment thickness can be defined as the thickness of the posterior edge 121 minus the thickness of the anterior edge 117.
In FIGS. 6A and 6B, an example augmented glenoid component 130 for use in a reverse shoulder system is shown. The glenoid component 130 includes a baseplate 132 in which the thickness of the baseplate 132 gradually increases from a first edge 133 to an opposite second edge 134 thereof. The baseplate 132 has a surface 136 from which a peg 138 extends. The baseplate 132 is secured in a glenosphere 139 forming the glenoid component 130. The glenosphere 139 has an convex articular surface 137 that provides a smooth bearing surface for the concave articular portion of the humeral component implanted into the humerus. An augment thickness can be defined as the thickness of the second edge 134 minus the thickness of the first edge 133.
In FIGS. 6C and 6D, another example augmented glenoid component 130A for use in a reverse shoulder system is shown. The glenoid component 130A includes a baseplate 132A in which the thickness of the baseplate 132A gradually increases from a first edge 133A to an approximately central section and then the thickness is approximately constant to an opposite second edge 134A thereof. The baseplate 132A has a surface 136A from which a peg 138A extends. The baseplate 132A is secured in a glenosphere 139A forming the glenoid component 130A. The glenosphere 139A has an convex articular surface 137A that provides a smooth bearing surface for the concave articular portion of the humeral component implanted into the humerus. An augment thickness can be defined as the thickness of the first edge 134A minus the thickness of the second edge 133A.
However, significant deficiencies have been found in currently available augmented glenoid components that are not based on an anatomic distribution. The currently available commercial designs for augmented glenoids are not designed based on the specific dimensions of glenoid bone loss present in patients undergoing shoulder arthroplasty. In order to make properly sized augmented glenoid components that will accommodate patients with arthritis, it is important to understand the anatomy of these patients. One issue that continues to be raised is that no one has ever defined on average where this transition zone begins between native bone and worn bone. This would allow one to design an augment that is shaped according to the defects that actually exist and covers the appropriate amount of glenoid worn rather than being based on guesswork. Ideally, to design proper augmented glenoids one needs to define the bone loss based on the anatomy of patients actually undergoing shoulder arthroplasty. In order to make properly sized augmented glenoid components that will accommodate patients with arthritis, it is important to understand the anatomy of these patients.
Thus, there exists a need for a method for the optimization of joint arthroplasty component design, and in particular, there exists a need for a method for the optimization of shoulder arthroplasty component design.
SUMMARY OF THE INVENTION
The present invention addresses the foregoing needs by providing methods for the optimization of joint arthroplasty component design.
In one aspect, the invention provides a method for manufacturing a prosthetic component for replacing a part of a bone of a joint in a subject. The method comprises: (a) obtaining an axial image of the bone of the joint; (b) orienting on the image a reference angle from a body of the bone to create a neutral face plate line that extends from a first border of the bone to an opposite second border of the bone; (c) measuring a length of the neutral face plate line; and (d) manufacturing the prosthetic component to include a base surface and an opposed articular surface wherein a width of the base surface is a predetermined percentage of the length of the neutral face plate line. For example, the width of the base surface may be the same or less than the length of the neutral face plate line.
In another aspect, the invention provides a method for manufacturing a prosthetic component for replacing a part of a bone of a joint in a subject. The method comprises: (a) obtaining an axial image of the bone of the joint; (b) orienting on the image a reference angle from a body of the bone to create a neutral face plate line that extends from a first border of the bone to an opposite second border of the bone; (c) orienting on the image a first reference line perpendicular to the neutral face plate line and extending over the bone in the image; (d) measuring a first reference length of the first reference line from the neutral face plate line perpendicular to a depth of a cavity in the bone; and (e) manufacturing the prosthetic component to include an articular section and a projection extending away from the articular section wherein a length of the projection is a predetermined percentage of the first reference length. For example, the length of the projection is typically less than the first reference length.
In another aspect, the invention provides a method for manufacturing a glenoid component for replacing a part of a scapula of a shoulder joint in a subject, the method comprises: (a) obtaining a sagittal image of the glenoid of the scapula; (b) orienting on the image a first reference line that extends perpendicularly from an inferior border of the glenoid image over the scapula in the image; (c) orienting on the image a second reference line that perpendicularly intersects the first reference line and that extends from a first border of the scapula to an opposite second border of the scapula; (d) measuring a length of the second reference line; and (e) manufacturing the glenoid component to have a width that is a predetermined percentage of the length of the second reference line. For example, the width of the glenoid component may be the same or less than the length of the second reference line.
In another aspect, the invention provides a method for manufacturing a prosthetic component for replacing a part of a bone of a joint in a subject. The method comprises: (a) obtaining a coronal image of the bone of the joint; (b) orienting on the image a first reference line that extends from a first border of a head of the bone to an opposite second border of the head of the bone; (c) orienting on the image a 90 degree reference angle from an inferior position of the first reference line to create a second reference line that extends over the image of the bone; (d) orienting on the image a third reference line that extends over the image of the bone from the second reference line to a superior aspect of a tuberosity of the bone; (e) measuring a length of the third reference line; and (f) manufacturing the prosthetic component to include a protruding section wherein a length of the protruding section is a predetermined percentage of the length of the reference line.
In another aspect, the invention provides a method for manufacturing a prosthetic component for replacing a part of a bone of a joint in a subject. The method comprises: (a) obtaining a coronal image of the bone of the joint; (b) orienting on the image a first reference line that extends from a first border of a head of the bone to an opposite second border of the head of the bone; (c) orienting on the image a ninety degree reference angle from an inferior position of the first reference line to create a second reference line that extends over the image of the bone; (d) orienting on the image a third reference line that extends over the image of the bone from the second reference line to a superior border of a tuberosity of the bone; (e) orienting on the image a fourth reference line that extends over the image of the bone from the third reference line to a side border of the tuberosity of the bone; (f) measuring a length of the fourth reference line; and (g) manufacturing the prosthetic component to include a protruding section wherein a diameter of the protruding section is a predetermined percentage of the length of the fourth reference line.
In another aspect, the invention provides a method for manufacturing a prosthetic component for replacing a part of a bone of a joint in a subject. In the method, the prosthetic component is formed to include a base surface and an opposed articular surface wherein a width of the base surface is a predetermined percentage of a length of a neutral face plate line. The length of the neutral face plate line used by the manufacturer in forming the prosthetic component has been determined by (i) obtaining an image of the bone of the joint, (ii) orienting on the image a reference angle from a body of the bone to create the neutral face plate line, wherein the neutral face plate line extends from a first border of the bone to an opposite second border of the bone, and (iii) measuring the length of the neutral face plate line. The predetermined percentage of the length of a neutral face plate line used by the manufacturer in forming the prosthetic component can be 100% or less, 90%-99%, or 80%-99%. The predetermined percentage can be greater than, equal to, or less than 100%, and can take into account a range of data values observed when analyzing a number of images for the measurement of interest. For example, the predetermined percentage can be selected to include any number of standard deviations above a mean of the collected measurement data. The joint can be arthritic. In one form, at least a section of the base surface of the prosthetic component is flat. For example, the base surface of the prosthetic component can be flat around a central post that extends away from the base surface of the prosthetic component. The neutral face plate line can correspond to a width of a flat neutral face plate formed by removing a portion of the bone during arthroplasty. In one version of the method, the bone is the scapula, and the joint is the shoulder. The prosthetic component can be a glenoid component. The image can be a computed tomography scan slice, and the reference angle can be 90 degrees. In one version of the method, the neutral face plate line is a straight line positioned completely within a perimeter of the image of the bone from the first border of the bone to the second border of the bone. At least a section of the straight line is spaced from a portion of the perimeter of the image of the bone, and the portion of the perimeter of the image of the bone represents a natural articular surface of the bone.
In another aspect, the invention provides a method for manufacturing a prosthetic component for replacing a part of a bone of a joint in a subject. In the method, the prosthetic component is formed to include an articular section and a projection extending away from the articular section wherein a length of the projection is a predetermined percentage of a first reference length. The first reference length used by the manufacturer in forming the prosthetic component has been determined by (i) obtaining an image of the bone of the joint, (ii) orienting on the image a reference angle from a body of the bone to create a neutral face plate line that extends from a first border of the bone to an opposite second border of the bone, (iii) orienting on the image the first reference line, the first reference line being perpendicular to the neutral face plate line and extending over the bone in the image, (iv) measuring the first reference length of the first reference line from the neutral face plate line perpendicular to a depth of a cavity in the bone. The predetermined percentage of the first reference length can be 100% or less, 90%-99%, or 80%-99%. The predetermined percentage can be greater than, equal to, or less than 100%, and can take into account a range of data values observed when analyzing a number of images for the measurement of interest. For example, the predetermined percentage can be selected to include any number of standard deviations above a mean of the collected measurement data. The projection can be a post. In one version of the method, the prosthetic component is formed such that the length of the projection is a predetermined percentage of a second reference length. The second reference length used by the manufacturer in forming the prosthetic component has been determined by (i) orienting on the image a second reference line parallel to the first reference line and extending over the bone in the image, (ii) measuring the second reference length of the second reference line from the neutral face plate line to the depth of a cavity in the bone. In one version of the method, the bone is the scapula, and the joint is an arthritic shoulder, and the prosthetic component is a glenoid component. The image can be a computed tomography scan slice. In one version of the method, the neutral face plate line is a straight line positioned completely within a perimeter of the image of the bone from the first border of the bone to the second border of the bone. At least a section of the straight line is spaced from a portion of the perimeter of the image of the bone, and the portion of the perimeter of the image of the bone represents a natural articular surface of the bone.
In another aspect, the invention provides a method for manufacturing a glenoid component for replacing a part of a scapula of a shoulder joint in a subject. In the method, the glenoid component is formed to have a width that is a predetermined percentage of a length of a second reference line. The length of the second reference line used by the manufacturer in forming the prosthetic component has been determined by (i) obtaining an image of the glenoid of the scapula, (ii) orienting on the image a first reference line that extends perpendicularly from an inferior border of the glenoid image over the scapula in the image, (ii) orienting on the image the second reference line, the second reference line perpendicularly intersecting the first reference line and extending from a first border of the scapula to an opposite second border of the scapula, and (iii) measuring the length of the second reference line. The predetermined percentage of the length of the second reference line can be 100% or less, 90%-99%, or 80%-99%. The predetermined percentage can be greater than, equal to, or less than 100%, and can take into account a range of data values observed when analyzing a number of images for the measurement of interest. For example, the predetermined percentage can be selected to include any number of standard deviations above a mean of the collected measurement data. The second reference line intersects the first reference line at about 10 to 18 millimeters above the inferior border of the glenoid image. The second reference line preferably intersects the first reference line at about 14 millimeters above the inferior border of the glenoid image. The image can be a computed tomography scan slice.
In another aspect, the invention provides a method for manufacturing a prosthetic component for replacing a part of a bone of a joint in a subject. In the method, the prosthetic component is formed to include a protruding section wherein a first length of the protruding section is a predetermined percentage of a length of the third reference line. The length of the third reference line used by the manufacturer in forming the prosthetic component has been determined by (i) obtaining an image of the bone of the joint, (ii) orienting on the image a first reference line that extends from a first border of a head of the bone to an opposite second border of the head of the bone, (iii) orienting on the image a 90 degree reference angle from an inferior position of the first reference line to create a second reference line that extends over the image of the bone, (iv) orienting on the image the third reference line, the third reference line extending over the image of the bone from the second reference line to a superior aspect of a tuberosity of the bone, and (v) measuring the length of the third reference line. In one version of the method, the prosthetic component is formed such that a second length of the projection is a predetermined percentage of a fourth reference length wherein the second length of the projection is perpendicular to the first length of the projection. The fourth reference length used by the manufacturer in forming the prosthetic component has been determined by (i) orienting on the image a fourth reference line perpendicular to the third reference line and extending over the bone in the image from the third reference line to a perimeter of the bone in the image, and (ii) measuring the fourth reference line to determine the fourth reference length. In one version of the method, the bone is the humerus, the joint is the shoulder, the length of the third reference line is a superior-inferior length of a greater tuberosity of the humerus, and the fourth reference length is a medial-lateral length of the greater tuberosity of the humerus. In one version of the method, the joint has been fractured, and the protruding section includes a plurality of fins for immobilizing fracture fragments.
In another aspect, the invention provides a method for manufacturing a prosthetic component for replacing a part of a bone of a joint in a subject. In the method, the prosthetic component is formed to include a head and a stem connected to the head. The head has a longitudinal head axis and the stem has a longitudinal stem axis. The head axis and the stem axis are angled to create an inclination angle between the head axis and the stem axis. The inclination angle used by the manufacturer in forming the prosthetic component has been determined by (i) obtaining an image of the bone of the joint, (ii) orienting on the image a first reference line that extends from a first border of a head of the bone to an opposite second border of the head of the bone, (iii) orienting on the image a 90 degree reference angle from an inferior position of the first reference line to create a second reference line that extends over the image of the bone, (iv) orienting on the image the third reference line, the third reference line extending over the image of the bone from the second reference line to a superior aspect of a tuberosity of the bone, and (v) measuring an angle between the first reference line and the third reference line, wherein the angle is equal to the inclination angle. In one version of the method, the bone is the humerus, and the joint is an arthritic shoulder. The image can be a computed tomography scan slice.
In another aspect, the invention provides a method for manufacturing a prosthetic component for replacing a part of a bone of a joint in a subject. In the method, the prosthetic component is formed to include an articular head and an opposed base surface. The head has a longitudinal head axis, and the head axis and the base surface are angled to create an inclination angle between the head axis and the base surface. The inclination angle used by the manufacturer in forming the prosthetic component has been determined by (i) obtaining an image of the bone of the joint, (ii) orienting on the image a first reference line that extends from a first border of a head of the bone to an opposite second border of the head of the bone, (iii) orienting on the image a 90 degree reference angle from an inferior position of the first reference line to create a second reference line that extends over the image of the bone, (iv) orienting on the image the third reference line, the third reference line extending over the image of the bone from the second reference line to a superior aspect of a tuberosity of the bone, and (v) measuring an angle between the first reference line and the third reference line, the angle being equal to the inclination angle. In one version of the method, the bone is the humerus, and the joint is an arthritic shoulder. The image can be a computed tomography scan slice.
In another aspect, the invention provides a method for manufacturing a prosthetic component for replacing a part of a bone of a joint in a subject. In the method, the prosthetic component is formed to include a body having a base surface, an outer surface opposite the base surface, a first side edge extending between the base surface and the outer surface, and a second side edge extending between the base surface and the outer surface. The second side edge is opposite the first side edge. A first thickness of the first side edge is less than a second thickness of the second side edge by an augment thickness. The augment thickness is determined by (i) obtaining an image of the bone of the joint, (ii) orienting on the image a reference angle from a body of the bone to create a first reference line parallel to a bone surface, wherein the first reference line extends from a first border of the bone to an opposite second border of the bone, (iii) orienting on the image a second reference line from the first reference line to an eroded region of the bone surface, (iv) determining a length of the second reference line, and (v) selecting the augment thickness based on the length of the second reference line. The augment thickness can be equal to the length of the second reference line. The image can be a computed tomography scan axial slice, and the reference angle can be 90 degrees. The first side edge can be an anterior edge, and the second side edge can be a posterior edge.
In one version of the method, the augment thickness extends from the second side edge to a location on the base surface between the first side edge and the second side edge. The location can be determined by (vi) identifying on the image a junction between the eroded region of the bone surface and a native region of the bone surface, and (vii) determining a reference point on the first reference line where a third reference line intersects the first reference line, the third reference line extending perpendicularly from the junction to the first reference line. The location can be determined by (viii) calculating a percentage of a fourth reference line from the first border of the bone to the reference point with respect to a length of the first reference line, and (ix) selecting the percentage to be an amount of the body having the augment thickness.
In one version of the method, the augment thickness increases from the first side edge to the second side edge thereby defining an augment angle between the outer surface and the base surface. The augment angle can be determined by orienting on the image an angle reference line from the first border to where the second reference line intersects the bone surface and by selecting the augment angle as an angle between the first reference line and the angle reference line.
In one version of the method, the augment thickness increases from the first side edge to the second side edge at a step discontinuity.
The bone can be the scapula, the joint can be the shoulder, and the prosthetic component can be a glenoid component. The outer surface can be a concave bearing surface for articulating with a humeral head component of a total shoulder arthroplasty system. The glenoid component can be a glenoid baseplate dimensioned to be secured to a glenosphere of a reverse shoulder arthroplasty system.
In another aspect, the invention provides a method for manufacturing a prosthetic component for replacing a part of a bone of a joint in a subject. In the method, the prosthetic component is formed to include a body having a base surface, an outer surface opposite the base surface, a first side edge extending between the base surface and the outer surface, and a second side edge extending between the base surface and the outer surface wherein the second side edge is opposite the first side edge. A first thickness of the first side edge is less than a second thickness of the second side edge by an augment thickness. The augment thickness can be determined by (i) obtaining an image of the bone of the joint, (ii) orienting on the image a neutral face plate line, (iii) orienting on the image a first reference line, the first reference line being parallel or within 20 degrees of parallel to the neutral face plate line, the first reference line extending from a first border of the bone to an opposite second border of the bone, (iv) orienting on the image a second reference line from the first reference line to a bone surface, the second reference line intersecting the first reference line a predetermined distance from the first border of the bone, (v) determining a length of the second reference line, and (vi) selecting the augment thickness based on the length of the second reference line. The augment thickness can be equal to the length of the second reference line.
In one version of the method, the augment thickness extends from the second side edge to a location on the base surface between the first side edge and the second side edge. The location can be determined by (vii) identifying on the image a junction between the eroded region of the bone surface and a native region of the bone surface, and (viii) determining a reference point on the first reference line where a third reference line intersects the first reference line, the third reference line extending perpendicularly from the junction to the first reference line. The location can be determined by (viii) calculating a percentage of a fourth reference line from the first border of the bone to the reference point with respect to a length of the first reference line, and (ix) selecting the percentage to be an amount of the body having the augment thickness.
In one version of the method, the augment thickness increases from the first side edge to the second side edge thereby defining an augment angle between the outer surface and the base surface, and the augment angle can be determined by orienting on the image an angle reference line from the first border to where the second reference line intersects the bone surface and by selecting the augment angle as an angle between the first reference line and the angle reference line. The augment thickness may increase from the first side edge to the second side edge at a step discontinuity.
In the method, the bone can be the scapula, the joint can be the shoulder, and the prosthetic component can be a glenoid component. The outer surface can be a concave bearing surface for articulating with a humeral head component of a total shoulder arthroplasty system. The glenoid component can be a glenoid baseplate dimensioned to be secured to a glenosphere of a reverse shoulder arthroplasty system.
In one version of the method, the image is a computed tomography scan coronal slice. The first reference line can be about 10 degrees from parallel to the neutral face plate line. In one version of the method, the first side edge of the prosthetic component body is an inferior edge, and the second side edge is a superior edge. The predetermined distance can be about 20 millimeters to about 40 millimeters.
In another aspect, the invention provides a method for manufacturing a prosthetic component for replacing a part of a bone of a joint in a subject. In the method, the prosthetic component is formed to include a body having a base surface, an outer surface opposite the base surface, a first side edge extending between the base surface and the outer surface, and a second side edge extending between the base surface and the outer surface wherein the second side edge is opposite the first side edge. A first thickness of the first side edge is less than a second thickness of the second side edge by an augment thickness. The augment thickness increases from the first side edge to the second side edge thereby defining an augment angle between the outer surface and the base surface. The augment angle can be determined by (i) obtaining an image of the bone of the joint, (ii) orienting on the image a neutral face plate line, (iii) orienting on the image a first reference line, the first reference line being parallel to the neutral face plate line, the first reference line extending from a first border of the bone to an opposite second border of the bone, (iv) orienting on the image a second reference line from the first reference line to a bone surface, the second reference line intersecting the first reference line a predetermined distance from the first border of the bone, (v) orienting on the image an angle reference line from the first border to where the second reference line intersects the bone surface, and (vi) selecting the augment angle based on a measured angle between the first reference line and the angle reference line. The image can be a computed tomography scan coronal slice.
In one version of the method, when the measured angle is in the range of 0 to 10 degrees superior tilt, the augment angle is selected as about 10 degrees. In another version of the method, when the measured angle is between 10 and 15 degrees superior tilt, the augment angle is selected as about 15 degrees. In another version of the method, when the measured angle is in the range of 15 to 20 degrees superior tilt, the augment angle is selected as about 20 degrees.
In one version of the method, the bone is the scapula, the joint is the shoulder, and the prosthetic component is a glenoid component. The glenoid component can be a glenoid baseplate dimensioned to be secured to a glenosphere of a reverse shoulder arthroplasty system. The first side edge of the prosthetic component body can be an inferior edge, and the second side edge can be a superior edge.
The methods of the present disclosure can be used in a number of different joints in addition to the shoulder. For example, the methods may be used in the elbow, wrist, hand, spine, hip, knee, ankle, and/or foot. When the joint is the elbow, the bone can be selected from the ulna, radius, and humerus. When the joint is the wrist, the bone can be selected from the radius, ulna, and carpal bones. When the joint is the hand, the bone can be selected from phalanges, metacarpals, and carpals. When the joint is the spine, the bone can be a vertebrae. When the joint is the hip, the bone can be selected from the femur and the pelvis/acetabulum. When the joint is the knee, the bone is selected from the femur, tibia and patella. When the joint is the ankle, the bone can be selected from the talus, the tibia and the fibula. When the joint is the foot, the bone can be selected from phalanges tarsals and metatarsals.
The method of the present disclosure allows one to design an augment that is shaped according to the defects that actually exist and covers the appropriate amount of glenoid worn rather than being based on guesswork. This disclosure facilitates design in three ways: (1) it defines the angle of glenoid erosion; (2) it defines the depth of glenoid erosion; and (3) it defines what percent of the glenoid has an eroded surface. This information will significantly improve the ability to design an augmented glenoid component.
These and other features, aspects, and advantages of the present invention will become better understood upon consideration of the following detailed description, drawings, and appended claims.



BRIEF DESCRIPTION OF THE DRAWINGS
FIG. 1 is a cross-sectional view of one embodiment of a shoulder prosthesis suitable for use in the invention.
FIG. 2 shows a tracing of a computed tomography (CT) axial two-dimensional (2D) CT slice of the scapula and humerus with measurement lines according to the invention shown in broken lines.
FIG. 3 shows a tracing of a 2D CT sagittal slice of the scapula with measurement lines according to the invention shown in broken lines.
FIG. 4 shows a tracing of a CT 2D coronal slice of the scapula and humerus with measurement lines according to the invention shown in broken lines.
FIG. 5A is a side sectional view of a prior art augmented glenoid component.
FIG. 5B is a side view of another prior art augmented glenoid component.
FIG. 6A is an exploded side view of yet another prior art augmented glenoid component.
FIG. 6B is a side view the augmented glenoid component of FIG. 6A in the assembled configuration.
FIG. 6C is an exploded side view of yet another prior art augmented glenoid component.
FIG. 6D is a side view the augmented glenoid component of FIG. 6C in the assembled configuration.
FIG. 7 shows a tracing of a computed tomography (CT) axial two-dimensional (2D) CT slice of the scapula and humerus with measurement lines according to the invention shown in broken lines.
FIG. 8 shows a tracing of a 2D CT coronal slice of the scapula with measurement lines according to the invention shown in broken lines.
FIG. 9 shows another tracing of a CT 2D coronal slice of the scapula and humerus with measurement lines according to the invention shown in broken lines.



Like reference numerals will be used to refer to like parts from Figure to Figure in the following description of the drawings.
DETAILED DESCRIPTION OF THE INVENTION
Looking first at FIG. 1, there is shown one example embodiment of a shoulder prosthesis 10 suitable for use in the invention. The upper portion of the humerus 12 is replaced by a humeral component 14 including a stem 16 that extends into a bore formed within the humerus 12. Typically, the stem 16 is fixed within the bore formed within the humerus 12. The stem 16 has a longitudinal stem axis S. A generally hemispherical head 18 is connected to the stem 16. The stem 16 can be monolithic with the head 18, or the stem 16 and the head 18 can formed as separate parts. The hemispherical head 18 has a base surface 19 and a longitudinal head axis H. The hemispherical head 18 of the humeral component 14 articulates with a complementary concave section 22 of a glenoid component 24 that is fixed within the glenoid cavity of the scapula 26 (shown cutaway) using cemented or uncemented posts 28. The glenoid component 24 includes a base surface 27 opposite the concave section 22 that serves as an articular surface of the glenoid component 24.
Proper design and selection of the hemispherical head 18 and the glenoid component 24 can be achieved using the method of the invention. In one non-limiting example method of the invention, eleven measurements are obtained using CT slices. The eleven measurements are as follows: (1) glenoid version; (2) anterior-posterior (AP) diameter at the articular surface; (3) anterior-posterior width at a neutral face plate; (4) depth of the glenoid vault from a neutral face plate; (5) depth of the glenoid vault from a neutral face plate with a diameter of the center post (an example center post diameter being five millimeters); (6) superior-inferior glenoid height; (7) determination of the anterior-posterior width fourteen millimeters from the inferior border of the glenoid; (8) humeral head diameter; (9) humeral head thickness; (10) greater tuberosity length of the humerus; (11) greater tuberosity width of the humerus; and (12) humeral inclination.
Proper design and selection of an augmented glenoid component can be achieved using the method of the invention. In one non-limiting example method of the invention, measurements are obtained using CT slices as shown in FIGS. 7-9.
The degree of anterior-posterior glenoid wear has been defined in a series of patients undergoing shoulder arthroplasty. This angle allows one to determine a specific anatomic range of augments to accommodate anterior-posterior bone loss in patients undergoing anatomic total shoulder arthroplasty and reverse shoulder arthroplasty.
Superior glenoid wear may occur in patients with rotator cuff insufficiency undergoing reverse shoulder arthroplasty. Previously, there was no information on the specific range of inferior-superior glenoid wear among these patients. Therefore, in order to design a glenoid baseplate that accommodates the anatomy of these patients and allows for proper fit with minimal bone removal, it is critical to understand the anatomic distribution in these patients. Thus, a method has been developed and utilized among patients who have undergone reverse arthroplasty of the shoulder to determine the anatomic distribution. The concept of superior wear angle and depth expands and is an extension on the neutral face plate concept described herein.
The most frequently used glenoid baseplate in the United States has a diameter of 25 millimeters. Therefore, one may determine the angle of an augmented glenoid component by placing an angle to the most medial aspect of the glenoid 25 millimeters from the inferior aspects of the glenoid compared to one parallel to the faceplate of the glenoid. However, the method is not limited to 25 millimeter diameter circular baseplates. One may determine the angle of an augmented glenoid component by placing an angle to the most medial aspect of the glenoid about 20 to about 40 millimeters from the inferior aspects of the glenoid compared to one parallel to the faceplate of the glenoid. This would accommodate circular baseplates having a 20-40 millimeter diameter, or oval baseplates having a major axis up to 40 millimeters. In cases where superior glenoid erosion has resulted in loss of the superior aspect of the glenoid, the scapular spine can be used with a standardized population based average to determine the inclination plane of the glenoid face.
Various combinations of these measurements are used for manufacturing a prosthetic component for replacing a part of a bone of a joint in a subject (e.g., mammal). The prosthetic component may be formed from, for example: (i) a metal or metal alloy such as a titanium alloy (e.g., titanium-6-aluminum-4-vanadium), a cobalt alloy, a stainless steel alloy, or tantalum; (ii) a nonresorbable ceramic such as aluminum oxide or zirconia; (iii) a nonresorbable polymeric material such as polyethylene; or (iv) a nonresorbable composite material such as a carbon fiber-reinforced polymers (e.g., polysulfone). The prosthetic component can be manufactured by machining an article formed from these materials, or by molding these materials in a suitable mold.
EXAMPLES
The following Examples have been presented in order to further illustrate the invention and are not intended to limit the invention in any way.
Example A
1. Glenoid Version
Using an axial 2D CT scan of a human shoulder, the mid point of the glenoid was determined. A first line was then drawn through the midpoint and parallel to the scapular body. The first line intersects a second line drawn parallel to the joint surface. The glenoid version was the angle between the first line and the second line, and was recorded in degrees.
2. Anterior-Posterior (AP) Width at the Articular Surface
Using an axial 2D CT scan of a human shoulder, the diameter (AP width) was measured at the mid-point of the glenoid in millimeters.
3. Anterior-Posterior (AP) Width at a Neutral Face Plate
Looking at FIG. 2, an axial 2D CT scan of a human shoulder was obtained and a 90 degree angle A (shown in broken lines) was oriented from the scapular body 26 and then placed on the glenoid 30 to create a neutral face plate 32 (shown in broken lines) that runs from one side border 34 to the other side border 36 of the glenoid 30. This width was then measured in millimeters. This measurement is important to determine the true AP width of the glenoid after creating a flat neutral face plate by removing bone during arthroplasty. This is what occurs at surgery according to the method of the invention, yet this measurement has never been previously described. Prior measurements have been made of the articular surface only of the glenoid. This explains why many glenoid component sizes are too large. The measurement at a neutral faceplate is usually several millimeters less than the measurement at the articular surface due to reaming or removing glenoid bone to make the surface flat to place the glenoid component 24.
When manufacturing a glenoid component, a manufacturer can be supplied with the length of the neutral face plate 32 which provides a true AP width of the glenoid after creating a flat neutral face plate by removing bone during arthroplasty. A predetermined percentage of the length of the neutral face plate 32 can be used to machine or mold the glenoid component to have a selected width for the base surface 27 (see FIG. 1).
4. Depth of the Glenoid Vault from a Neutral Face Plate
Still looking at FIG. 2, a line 38 (shown in broken lines) was started at the neutral face plate 32 and was drawn medially to determine the depth of the glenoid vault 40. Previous reports have mentioned only the depth from the articular surface which overstates the depth of the glenoid. This explains why many central posts or peripheral pegs of glenoid components that are currently in the market are too long and perforate the glenoid. Prior designs have not been designed based on patients with arthritis and associated bone loss who have undergone shoulder arthroplasty.
When manufacturing a glenoid component, a manufacturer can be supplied with the length of the line 38. A predetermined percentage of the length of the line 38 can be used to machine or mold the glenoid component to have a selected longitudinal length for the post 28 (see FIG. 1).
5. Depth of the Glenoid Vault from a Neutral Face Plate with a Diameter of 5 Millimeters
Still looking at FIG. 2, a five millimeter line 42 (shown in broken lines) was placed within the vault parallel to the line 38. This will show one the depth of the glenoid vault that one can drill back to a five millimeter diameter. This allows accurate determination of the safe length for a central post or screw. Other post diameters are allowed in the design, five millimeters is used only as an example.
When manufacturing a glenoid component, a manufacturer can be supplied with the length of the line 42. A predetermined percentage of the length of the line 42 can be used to machine or mold the glenoid component to have a selected length for the post 28 (see FIG. 1).
6. Superior-Inferior Glenoid Length
The height of the glenoid was measured in millimeters.
7. Determination of the AP Width Fourteen Millimeters from the Inferior Border of the Glenoid
Turning to FIG. 3, a 2D CT scan of a human shoulder was obtained and on the sagittal cut, an anterior-posterior width on line 46 (shown in broken lines) was measured. Line 46 was perpendicular to and fourteen millimeters up line 50 (shown in broken lines) from the inferior border 48 of the glenoid 30. This measures the anterior-posterior width of the glenoid fourteen millimeters above the inferior rim of the glenoid. This allows determination of the appropriate width of a glenoid base plate for reverse arthroplasty.
When manufacturing a glenoid component, a manufacturer can be supplied with the length of the line 46. A predetermined percentage of the length of the line 46 can be used to machine or mold the glenoid component to have a selected width for the base surface 27 (see FIG. 1).
8. Humeral Head Diameter and 9. Humeral Head Thickness
Turning to FIG. 4, a 2D CT scan of a human shoulder was obtained and on the coronal slice the diameter of the humeral head was measured in millimeters at line 52 (shown in broken lines). A line 54 (shown in broken lines) was then drawn perpendicular from line 52 to the surface 56 of the humeral head. The length of line 54 (here measured in millimeters) gives one the thickness of the humeral head.
10. Greater Tuberosity Length and 11. Greater Tuberosity Width
A 90 degree line 58 (shown in broken lines) was taken off the most inferior aspect of the humeral head cut. A line 62 (shown in broken lines) was then placed from the superior aspect of the greater tuberosity (intersection with the superior end point of line 52) to intersect this line 58. This line 62 shows the true distance of the greater tuberosity in length (superior-inferior). Next a line 64 (shown in broken lines) was taken 90 degrees to this line 62 to show the maximum diameter of the greater tuberosity. This line 64 shows the true distance of the greater tuberosity in width (medial-lateral). This facilitates designing a humeral component that maximizes tuberosity healing as well as anatomic component shape. This data also facilitates the design of different size humeral components specifically for fracture cases to improve tuberosity healing. This would include different size “fins” or other components to accommodate and secure fracture fragments based on the size of the patient.
12. Measurement of Humeral Inclination
On FIG. 4, taking the angle B between lines 52 and 62 in degrees and adding 90° defines the inclination angle of the humeral head in degrees (i.e., angle B in degrees+90°=the inclination of the humeral head). This measurement can determine the true range of inclination necessary for humeral component design.
When manufacturing a humeral component, a manufacturer can be supplied with the inclination angle of the humeral head. The inclination angle of the humeral head can be used to machine or mold the humeral component to have a selected angle, or a selected range of angles (for adjustable humeral inclination) between the longitudinal head axis H (see FIG. 1) and the longitudinal stem axis S (see FIG. 1) or the longitudinal head axis H and the base surface 19 (see FIG. 1).
Results
Using the measurement technique of Examples 1-12, a review of 800 patients who have undergone shoulder arthroplasty (436 total shoulder arthroplasties, 210 reverse shoulder arthroplasties, and 154 hemiarthroplasties) was completed and is shown in Table 1 below. In addition, statistical analysis revealed that when evaluating for specific anatomic ratios there were very tight confidence intervals. This can be further used to ensure proper component design as shown in Table 2.







TABLE 1







Anatomic Measurements of 800 Shoulders




















10th



Variable
Mean
Std Dev
Median
Minimum
Maximum
Pctl
90th Pctl

















1. Glenoid version (degrees)
10.66
9.68
10.00
−27.00
49.00
0.00
24.00


2. AP width at articular surface (mm)
28.71
4.32
28.50
12.40
41.20
23.30
34.20


3. AP width at a neutral faceplate (mm)
24.59
3.83
24.70
12.00
36.90
19.80
29.30


4. Vault depth from a neutral face plate (mm)
21.79
4.30
22.00
6.10
37.00
16.30
27.20


5. Vault depth to a 5 mm diameter (mm)
16.07
4.2
16.30
2.00
27.30
10.80
21.50


6. Superior-Inferior: Glenoid Height (mm)
34.61
4.4
34.20
24.00
50.10
29.10
40.60


7. AP width 14 mm from inferior glenoid rim (mm)
26.78
3.14
26.80
15.00
35.20
22.80
30.80


8. Humeral head diameter (mm)
43.47
4.31
43.00
32.80
56.00
38.30
49.60


9. Humeral head thickness (mm)
22.11
2.76
22.20
14.20
29.70
18.80
25.60


10. Greater tuberosity superior-inferior (mm)
33.61
4.54
33.10
21.00
47.00
28.00
40.00


11. Greater tuberosity medial-lateral (mm)
11.29
2.01
11.00
6.30
18.00
8.90
14.00


12. Humeral Inclination (degrees)
129.13
5.72
129.00
115.00
145.00
121.00
137.00





The 10th and 90th percentile refer to the range of data.















TABLE 2







Overall - 95%



Overall
Confidence


Ratio
Ratio
Intervals

















Humeral head diameter/Humeral head
1.98
1.97, 2.00


thickness


Greater tuberosity medial-lateral (width)/
0.337
0.334, 0.341


Greater tuberosity superior-inferior (height)


AP width at a neutral faceplate/
1.16
1.14, 1.18


Vault depth from a neutral faceplate









Example B
Glenoid wear typically occurs in a posterior pattern with osteoarthritis and a superior direction with rotator cuff insufficiency. Anterior wear may also occur as well as combined patterns, however posterior or superior wear patterns are the dominant wear patterns.
There are two primary means to resurface a worn glenoid component: anatomic shoulder arthroplasty and reverse arthroplasty. Anatomic arthroplasty is typically done in the setting of a posterior wear pattern. Reverse arthroplasty may be done in a posterior or superior wear pattern. In order to design appropriately sized augmented components, one needs to know the dimensions of wear.
1. Design of an Augment for a Posteriorly Worn Glenoid
The angle of the augment is determined by determining the version of the glenoid. Looking at FIG. 7, an axial 2D CT scan of a human shoulder was obtained. One orients a line 231 parallel to the scapular body 226 that intersects a line 232 parallel to the joint surface at 90 degree angle A2. The line 232 runs at least from a posterior side border 234 to an anterior side border 236 of the glenoid 230. The thickness dimension of the augment is determined by measuring along line 238 in millimeters the amount of wear of the posterior aspect of the glenoid 230. One can also determine where the junction 241 occurs between native bone and eroded bone. This facilitates design of the augment by determining what percent of the glenoid 230 should have an augmented surface. For example, a distance along line 232 from the posterior side border 234 to the anterior side border 236 can be determined, and then a distance along line 232 from the anterior side border 236 to a point P at a line 243 passing through the junction 241 and perpendicular to the line 232. An augment angle can be determined from angle G between line 232 and an angle reference line 239 from the anterior side border 236 to the line 238 where line 238 intersects the bone. The thickness of the augment, angle, and percent of surface covered by the augment may be less depending on the amount that the surgeon would want to ream the glenoid. However, reaming weakens the bone as well as decreases the moment arm for the rotator cuff muscles. Therefore, there has been increasing interest for the use of augments rather than reaming glenoid bone.
2. Design of an Augment for a Superiorly Worn Glenoid
Looking at FIG. 8, a coronal 2D CT scan of a human shoulder was obtained. One determines the thickness of an augment needed by measuring a set distance from the inferior part 242 of the glenoid 230. For example, for a glenoid baseplate that is 25 millimeters in diameter, one can measure 25 millimeters (as dimension D of FIG. 8) from the inferior part 242 of the glenoid 230 along a line 244 parallel to the neutral face plate 246 of the glenoid 230 for a baseplate placed in neutral tilt. One can then measure medially along line 248 from the line 244 to the bone surface to determine the thickness of the superior augment needed. One can determine the angle of an augmented glenoid by placing a line 249 creating an angle A3 to the most medial aspect of the glenoid 230 compared to the line 244 parallel to the neutral face plate 246 of the glenoid 230. One can also determine where the junction 251 occurs between native bone and eroded bone. This facilitates design of the augment by determining what percent of the glenoid should have an augmented surface. For example, a distance along line 244 from the inferior part 242 to the superior side border 256 can be determined, and then a distance along line 244 from the inferior part 242 to a point P1 at a line 253 passing through the junction 251 and perpendicular to the line 244.
One can create a glenoid component with 10 degrees of inferior tilt as preferred by some surgeons. Looking at FIG. 9, a coronal 2D CT scan of a human shoulder was obtained. One determines the thickness of an augment needed by measuring a set distance from the inferior part 342 of the glenoid 230. For example, for a glenoid baseplate that is 25 millimeters in diameter, one can measure 25 millimeters (as dimension D of FIG. 9) from the inferior part 342 of the glenoid 230 along a line 344 that has 10 degrees of tilt with respect to the neutral face plate 346 of the glenoid 230 for a baseplate placed in 10 degrees of inferior tilt. One can then measure medially along line 348 from the line 344 to the bone surface to determine the thickness of the superior augment needed. One can determine the angle of an augmented glenoid by placing a line 349 creating an angle A4 to the most medial aspect of the glenoid 230 compared to the line 344. One can also determine where the junction 351 occurs between native bone and eroded bone. This facilitates design of the augment by determining what percent of the glenoid should have an augmented surface. For example, a distance along line 344 from the inferior part 342 to the superior side border 356 can be determined, and then a distance along line 344 from the inferior part 342 to a point P2 at a line 353 passing through the junction 351 and perpendicular to the line 344.
3. Glenoid Wear Patterns
In a series of 50 consecutive shoulders that underwent reverse arthroplasty, CT scans indicated that there were 28 with no superior glenoid wear (56%) and 22 with superior glenoid wear (44%). Among the glenoids without wear, superior inclination averaged 8 degrees. Among the glenoids with superior wear, there were 3 with mild wear with 5-10 degrees superior inclination, 10 with moderate wear with 10-15 degrees superior inclination, and 9 with severe wear with greater than 15 degrees of superior inclination. Among the 9 with severe wear, two had wear greater than 20 degrees.
This study revealed a high rate of superior glenoid wear in patients undergoing reverse arthroplasty (44%). The data derived from this method has provided insight for the range of augments necessary to accommodate patients undergoing reverse arthroplasty.
The methodology has revealed the potential benefit of an augmented glenoid baseplate for the reverse arthroplasty not only in the setting of significant glenoid erosion but also in the patient with no glenoid erosion. An augmented glenoid can facilitate the inferior tilting of the glenoid component to decrease the chance of loosening—while maintaining better quality bone and preserving bone.
Among shoulders with no wear, there was on average 8 degrees of superior tilt. A preferred amount of inferior inclination is approximately 10 degrees. One strategy would allow the surgeon to ream the glenoid to a neutral position and then use a 10 degree augmented glenoid to create the appropriate tilt. This allows the surgeon to provide optimal inferior tilt without removing more inferior bone—a bone preserving approach. This is particularly important in a large glenoid with a deep concavity. If an augmented glenoid is not used, an excessive amount of glenoid reaming may be necessary to create the appropriate inferior tilt.
The method has also revealed that augments ranging up to 20 degrees can accommodate 96% of glenoids undergoing reverse arthroplasty without the need for bone grafting. In a deformity up to 20 degrees, the surgeon can ream back to 10 degrees of superior tilt and use an augment with a 20 degree angle. This would create 10 degrees of inferior tilt. This method has also facilitated creation of an algorithm to manage superior glenoid wear. See Table 3 below.







TABLE 3







Reverse Shoulder- Glenoid Bone Preserving Technique











Inclination




Glenoid Wear
Correction
Treatment
Outcome





Slight or no wear
up to 10 degrees
10 degree
10 degrees


(0-10 degrees

augmented glenoid
inferior tilt


superior tilt)


Moderate wear
up to 10 degrees
15 degree
10 degrees


(10-15 degrees)

augmented glenoid
inferior tilt


Severe wear
up to 10 degrees
20 degree
10 degrees


(15-20 degrees)

augmented glenoid
inferior tilt









Use of the method described herein for superior wear and inclination has revealed the optimum range of augments necessary for reverse shoulder arthroplasty with a superior wear pattern. In addition, this method has helped identify a bone preserving technique of placing the glenoid baseplate in patients with minimal to no wear.
Thus, the invention provides a method for the optimization of shoulder arthroplasty component design. Use of this method and the data that it provides gives unique insight into the number, size and shape of glenoid components for total shoulder arthroplasty and reverse shoulder arthroplasty as well as humeral heads for shoulder arthroplasty and resurfacing arthroplasty. This method also provides valuable information for the optimal design, shape, and size of the proximal humeral body for a fracture stem to maximize tuberosity healing and humeral component design for hemiarthroplasty/total shoulder arthroplasty. A method for the optimization of an augmented glenoid design for shoulder arthroplasty is also provided. In the course of new product development, this method is a valuable resource that can be used to radiographically evaluate each new component design to ensure optimal fit prior to component production and product launch. While the invention is described herein as a method for the optimization of shoulder arthroplasty component design, it can be used for other joints (e.g., elbow, wrist, hand, spine, hip, knee, ankle, foot, etc. . . . ).
Although the present invention has been described in detail with reference to certain embodiments, one skilled in the art will appreciate that the present invention can be practiced by other than the described embodiments, which have been presented for purposes of illustration and not of limitation. Therefore, the scope of the appended claims should not be limited to the description of the embodiments contained herein.

## Claims

1. A method for manufacturing a prosthetic component for replacing a part of a bone of a joint in a subject, the method comprising:
forming the prosthetic component to include a body having a base surface, an outer surface opposite the base surface, a first side edge extending between the base surface and the outer surface, and a second side edge extending between the base surface and the outer surface, the second side edge being opposite the first side edge, wherein a first thickness of the first side edge is less than a second thickness of the second side edge by an augment thickness, and the augment thickness increases from the first side edge to the second side edge thereby defining an augment angle between the outer surface and the base surface, and the augment angle is determined by (i) obtaining an image of the bone of the joint, (ii) orienting on the image a neutral face plate line, (iii) orienting on the image a first reference line, the first reference line being parallel to the neutral face plate line, the first reference line extending from a first border of the bone to an opposite second border of the bone, (iv) orienting on the image a second reference line from the first reference line to a bone surface, the second reference line intersecting the first reference line a predetermined distance from the first border of the bone, (v) orienting on the image an angle reference line from the first border to where the second reference line intersects the bone surface, and (vi) selecting the augment angle based on a measured angle between the first reference line and the angle reference line.

2. The method of claim 1 wherein:
the bone is a scapula,
the joint is a shoulder, and
the prosthetic component is a glenoid component.

3. The method of claim 2 wherein:
the glenoid component is a glenoid baseplate dimensioned to be secured to a glenosphere of a reverse shoulder arthroplasty system.

4. The method of claim 3 wherein:
the first side edge is an inferior edge, and
the second side edge is a superior edge.

5. The method of claim 4 wherein:
the image is a computed tomography scan coronal slice.

6. The method of claim 1 wherein the joint is selected from elbow, wrist, hand, spine, hip, knee, ankle, and foot.

7. The method of claim 6 wherein:
when the joint is the elbow, the bone is selected from an ulna, a radius and a humerus,
when the joint is the wrist, the bone is selected from a radius, an ulna and carpal bones,
when the joint is the hand, the bone is selected from phalanges, metacarpals, and carpals,
when the joint is the spine, the bone is a vertebrae,
when the joint is the hip, the bone is selected from a femur and a pelvis,
when the joint is the knee, the bone is selected from a femur, a tibia, and a patella
when the joint is the ankle, the bone is selected from a talus, a tibia and a fibula, and
when the joint is the foot, the bone is selected from phalanges, tarsals, and metatarsals.

8. The method of claim 1 wherein:
when the measured angle is in the range of 0 to 10 degrees superior tilt, the augment angle is selected as about 10 degrees.

9. The method of claim 1 wherein:
when the measured angle is between 10 and 15 degrees superior tilt, the augment angle is selected as about 15 degrees.

10. The method of claim 1 wherein:
when the measured angle is in a range of 15 to 20 degrees superior tilt, the augment angle is selected as about 20 degrees.