Patent Application
20150250597
This disclosure relates to patient-adapted (e.g., patient-specific or patient-engineered) hip joint implant, implant systems, as well as related surgical instrumentation.
Historically, a diseased or damaged joint, e.g., a joint exhibiting osteoarthritis, has been repaired using standard off-the-shelf implants and other surgical devices. Hip arthroplasty has become a routine procedure in surgically repairing a diseased or damaged hip joint. Total hip replacement (THR) procedures typically involve the implantation of two main components: an femoral component and an acetabular component. The femoral component is anchored within the existing femur, usually through a rigid stem secured within a canal in the natural femur bone tissue, and includes a head that replaces the natural hip joint femoral head. The acetabular component is secured within the acetabulum of the patient and serves as a bearing surface for the femoral component.
Hip resurfacing has also been developed as a surgical alternative to THR. Conventionally, the procedure consists of placing a cap over the head of the femur while a matching cup is placed in the acetabulum, replacing the articulating surfaces of the patient's hip joint and removing less bone compared to a THR.
Certain existing hip replacement systems involve metal-on-metal articulating devices, that is, both femoral head and acetabular cup are made of metal. Recently, metal-on-metal hip replacement systems have been found to be failing within a few years instead of lasing more than 10 years. And the wear of metal bearing surfaces articulating against each other has been found to generate debris that could cause potential harm to the patients.
A partial hip replacement may be recommended if only one part of the hip joint is diseased or damaged. In most instances, the acetabulum is left intact and the head of the femur is replaced, using components similar to those used in a total hip replacement. The most common form of partial hip replacement is called a bipolar prosthesis, referring to a two-component prosthesis used for hemiarthroplasties in which one component is fixed rigidly in place on one side of the joint and the other component with which the first component articulates is inserted loosely on the other side of the joint. A hip prosthesis can also be unipolar, referring a prosthesis used for hemiarthoplasties with no across the joint articulating component.
Various hip prostheses have been developed over the years. For example, U.S. Pat. No. 6,262,948 to Storer et al. issued Sep. 30, 2003 discloses a femoral hip prosthesis that replaces the natural femoral head. U.S. Patent Publication Nos. 2002/0143402 and 2003/0120347 to Steinberg published Oct. 3, 2002 and Jun. 26, 2003, respectively, also disclose a hip prosthesis that replaces the femoral head and provides a member for communicating with the ball portion of the socket within the hip joint.
A variety of tools are available to assist surgeons in performing hip arthroplasty. For example, U.S. Pat. No. 5,578,037 to Sanders et al. issued Nov. 26, 1996 discloses a surgical guide for femoral resection. The guide enables a surgeon to resect a femoral neck during a hip arthroplasty procedure so that the femoral prosthesis can be implanted to preserve or closely approximate the anatomic center of rotation of the hip.
This disclosure relates to hip prostheses or implants and implant systems, in particular, those with features adapted to individual patients. This disclosure also provides patient-adapted surgical tools for placing the hip implants, and other related devices and methods.
The embodiments described herein include advancements in the area of patient-adapted articular implants that are tailored to address the needs of individual, single patients. More specifically, the patient-adapted articular implants and the patient-adapted surgical devices and methods are used in hip arthroplasty. Such patient-adapted hip replacement or resurfacing systems and related patient-adapted surgical tools offer advantages over the traditional one-size-fits-all approach, or a few-sizes-fit-all approach. The advantages include, for example, better fit, more natural movement of the repaired hip joint, better bone preservation (e.g., reduction in the amount of bone removed during surgery), reduction in blood loss during surgery, a less invasive procedure, maintaining or optimizing leg length, and accordingly less painful or shorter patient recovery and rehabilitation.
Such patient-adapted articular implants and implant systems can be created from images or electronic image data of the patient's joint, e.g., a diseased or damaged hip joint to be surgically repaired. Based on the images or image data, patient-adapted implants and implant systems can be selected or designed to include features (e.g., surface contours, curvatures, widths, lengths, thicknesses, and other shape, dimensional or structural features) that match existing features in the single, individual patient's joint and, optionally, features that approximate an ideal or healthy feature that may not exist in the patient prior to a procedure.
Similarly, patient-adapted surgical tools can be created from images or electronic image data of the patient's joint, e.g., a diseased or damaged hip joint to be surgically repaired. Based on the images or image data, patient-adapted surgical tools can designed to include features (e.g., surface contours, curvatures, widths, lengths, thicknesses, and other shape, dimensional or structural features) that match existing features in the single, individual patient's joint, and optionally, features that approximate an ideal or healthy feature that may not exist in the patient prior to a procedure. For example, a patient-specific surgical tool includes a patient-specific surface that is substantially a negative of at least a portion of the joint; the portion of the joint may include at least a portion of an articular surface, a non-articular surface, a cartilage surface, or a bone (e.g., subchondral bone or cortical bone) surface of the joint; the patient-specific may also include joint information (e.g., cartilage information) derived from image data of the patient's joint.
Patient-adapted features described herein can include either patient-specific or patient-engineered or both features. Further, patient-specific (or patient-matched) implant features can include features adapted to match one or more of the patient's biological features, for example, one or more biological or anatomical structures, alignments, kinematics, or soft tissue impingements. Patient-engineered (or patient-derived) features of an implant can be designed or manufactured (e.g., preoperatively designed and manufactured) based on patient-specific data to substantially enhance or improve one or more of the patient's anatomical or biological features.
The patient-adapted (e.g., patient-specific or patient-engineered) implants described herein can be selected (e.g., from a library), designed (e.g., preoperatively designed including, optionally, manufacturing the components or tools), or selected and designed (e.g., by selecting a blank component or tool having certain blank features and then altering the blank features to be patient-adapted). Moreover, related methods, such as designs and strategies for preparing or resecting a patient's biological structure can also be selected or designed for the individual patient. For example, an implant component's bone-facing surface and a preparing or resection strategy for the corresponding bone-facing surface can be selected or designed together so that at least one of an implant component's bone-facing surface matches the prepared or resected surface. In specific embodiments, the implant or implant component's bone-facing surface has at least one portion (e.g., a planar portion or a periphery) that matches a corresponding portion (e.g., a planar portion or a periphery or rim) of the prepared or resected surface. In addition, one or more surgical tools or guide tools optionally can be selected or designed to facilitate the preparation or resection cuts that are predetermined in accordance with preparation or resection strategy and implant component selection or design.
Certain embodiments relate to a hip implant system that includes a femoral implant or implant component and an acetabular implant or implant component. The femoral implant or acetabular implant may be comprised of single or multiple components, such as for example, a femoral shaft, a femoral neck, a femoral head, an acetabular cup, an acetabular insert. One or more the components can be standard or off-the-shelve components that are not adapted for any individual patient (e.g., patient-universal). At least one component of the hip implant system is patient-adapted or includes one or more features designed or selected for a particular patient, e.g., based on electronic image data of the patient.
Certain embodiments relate to a method of making a patient-adapted hip implant system and related surgical instrumentation as disclosed herein. The method can include one or more steps as detailed below. Sequence of the method steps can also be varied.
Further provided is a method of using the patient-adapted hip implant system and related surgical instrumentation. The method can also be patient-adapted based on individual surgeons' approaches and preferences.
Accordingly, this disclosure provides devices and methods for surgically repairing a hip joint, where the devices or methods are patient-adapted.
This disclosure is also related to U.S. application Ser. No. 13/397,457, filed on Feb. 15, 2012, published as U.S. Application Publication No. 20120209394, the entire content of which application is incorporated by reference herein.
It is to be understood that the features of the various embodiments described herein are not mutually exclusive and may exist in various combinations and permutations.
The foregoing and other objects, aspects, features, and advantages of embodiments will become more apparent and may be better understood by referring to the following description, taken in conjunction with the accompanying drawings, in which:
When a surgeon uses a traditional off-the-shelf implant to replace a patient's joint, certain features of the implant typically do not match the particular patient's biological features. These mismatches can cause various complications during and after surgery. For example, surgeons may need to extend the surgery time and apply estimates and rules of thumb during surgery to address the mismatches. For the patient, complications associated with these mismatches can include pain, discomfort, soft tissue impingement, and an unnatural feeling of the joint during motion as well as an altered range of movement and an increased likelihood of implant failure. In order to fit a traditional implant component to a patient's articular bone, surgeons typically remove substantially more of the patient's bone than is necessary to merely clear diseased bone from the site. This removal of substantial portions of the patient's bone frequently diminishes the patient's bone stock to the point that only one subsequent revision implant is possible.
Certain embodiments of the implants, surgical tools, and related methods (e.g., methods of designing, selecting or optimizing), and methods of using the implants and surgical tools (e.g., guide tools) described herein can be applied to any joint including a hip joint. Furthermore, various embodiments described herein can apply to methods and procedures, and the design of methods and procedures, for preparing, resectioning or otherwise revising the patient's anatomy in order to implant the implant components described herein or to using the surgical tools described herein.
In certain embodiments, an implant or implant components or related methods described herein can include a combination of patient-specific and patient-engineered features. In certain embodiments, an implant or implant components or related methods described herein can include a combination of patient adapted (patent specific or patient-engineered) features with standard features (i.e., designed or selected without reference to an individual patient or the patient intended to receive the implant or implant components). An implant, or one or more components of the implant, may include a joint-facing surface, at least a portion of which provides an articular surface upon implantation. Similarly, such a joint-facing surface can include a combination of patient-specific and patient-engineered features, which may be obtained or derived from patient-specific data, such as image data of a patient's joint, e.g., the diseased or damaged joint to be surgically repaired. An implant or implant component may be made of a single material. Alternatively, an implant or implant component may be made from at least two different materials. For example, the joint-facing surface of an implant or implant component may be made from a material such as ceramic, whereas the body or the rest of the implant or implant component may be made from a different material such as metal. As detailed below, different types of materials can be employed to manufacture an implant or implant component as described here. Further, an implant or implant component described herein can be modular or include modular parts.
Further, patient-specific data collected preoperatively can be used to engineer one or more optimized surgical cuts to the patient's bone and to design or select a corresponding implant component having or more bone-facing surfaces or facets (i.e., ‘bone cuts’) that specifically match one or more of the patient's resected bone surfaces. The surgical cuts to the patient's bone can be optimized (i.e., patient-engineered) to enhance one or more parameters, such as: (1) deformity correction and limb alignment (2) maximizing preservation of bone, cartilage, or ligaments, or (3) restoration or optimization of joint kinematics or biomechanics. Based on the optimized surgical cuts and, optionally, on other desired features of the implant component, the implant component's bone-facing surface can be designed or selected to, at least in part, negatively-match the shape of the patient's resected bone surface.
Also provided are tools, such as for example surgical tools including guide tools. Such tools may also have one or more patient-adapted (e.g., patient-specific or patient-engineered) features. A surgical tool may include a template that has at least a portion (e.g., a contact surface) for engaging a portion of a joint (e.g., a surface associated with a joint), and the portion (e.g., the contact surface) substantially conforms with (or is substantially a negative of) the portion (e.g., the surface) associated with a joint. The template may further include at least one guide (e.g., a guide aperture or cutting slot) for directing movement of a surgical instrument. The template may be a single component or may include two or more components or pieces. The two or more components or pieces can be linked reversibly or irreversibly when in use, e.g., in surgery, and such linkage can be an attachment mechanism or through cross-reference (e.g., a second component registers to or cross-references a portion of the joint prepared by a first component). In related embodiments, the surface associated with the joint may be an articular surface, a non-articular surface, a cartilage surface, a weight bearing surface, a non-weight surface or a bone surface. The contact surface may be made of different materials (e.g., a biocompatible material). The contact surface can sustain heat sterilization without deforming.
Further provided are methods of joint arthroplasty, in particular, methods of hip arthroplasty. The method may include obtaining patient-specific data, such as data from an image of a hip joint and optionally one or more images of other joints (ankle, knee, etc.) including data encompassing a surface, e.g., an articular surface or bone surface associated with the hip joint. Also included are data encompassing one or more acetabular or femoral dimensions (e.g., size, thickness, or curvature, including angles such as femoral neck angle), and desired leg length. The patient-specific data may also include the degree of anteversion or retroversion or rotation of a patient's hip joint and thus the degree of necessary correction. The patient-specific data may optionally include information on one or more abnormalities associated with the hip joint (e.g., osteophyte, protrusion acetabula).
Based on the patient-specific data, one or more surgical tools are created having at least one contact surface that substantially conforms with at least a portion of the surface associated with the hip joint. Other patient-adapted features can also be derived from the patient-specific data and built in the surgical tools, e.g., by including one or more guides in the surgical tools that have a predetermined position and orientation based on the patient-adapted features to define a predetermined path for directing movement of one or more surgical instruments.
Also based on the patient-specific data, an implant may be designed or selected, which may include one or more patient-adapted features. Such an implant may include a single component or multiple components. An implant component may be designed or selected to include one or more patient-adapted features. Alternatively, an implant component may be selected from a library of premade implant components, and such selection may be based on the individual patient-specific data or follow a standard applicable to different patients.
The patient-specific data may also allow a surgeon to determine the surgical approach, such as an anterior, lateral, or posterior approach. The patient-specific data may also allow a surgeon to evaluate the degree of anteversion or retroversion or rotation of the patient's hip joint and determine the degree of necessary correction, which may be determined in conjunction with the selection of the surgical approach.
Hip Replacement Systems Generally
Depending on a patient's hip conditions, total or partial hip arthroplasty may be recommended. Typical considerations on designing or selecting a hip replacement system may include bone preservation, different or patient-specific anatomy, (e.g., leg length, neck angle, e.g., “offset” and “short neck” stems), material selection (e.g., to ensure patient safety; to improve implant stability, etc.). The following subsections briefly describe certain, non-limiting commercial examples of hip replacement systems. Various embodiments of the disclosure can be adapted and utilized to improve existing designs or systems, to develop new hip replacement systems that may or may not include one or more existing components.
Total Hip Replacement
Total hip arthroplasty is intended to provide increased patient mobility and reduce pain by replacing the damaged hip joint articulation in patients where there is evidence of sufficient sound bone to seat and support the components. Total hip replacement is typically indicated in the following conditions: a severely painful or disabled joint from osteoarthritis, traumatic arthritis, rheumatoid arthritis, or congenital hip dysplasia, avascular necrosis of the femoral head, acute traumatic fracture of the femoral head or neck, failed previous hip surgery including joint reconstruction, internal fixation, arthrodesis, hemiarthroplasty, surface replacement arthroplasty, or total hip replacement, certain cases of ankylosis.
A total hip placement system may include modular components. An example of a modular hip replacement system is the S-ROM® Modular Hip System.
The modular nature allows the S-ROM® Modular Hip System to provide solutions for a full range of surgical scenarios, from primary total hip arthroplasty to the most complex revision or other challenges. In this modular system, the stem's independent neck and sleeve allows for 360 degrees of version adjustment and enables a surgeon to place the proximal sleeve in the best possible bone stock without affecting the stem biomechanics.
The S-ROM® prosthesis is a proximally modular cementless stem that separates the critical functions of intramedullary fixation and extramedullary biomechanics. The porous-coated proximal sleeve can be oriented and rotated to accommodate the best remaining calcar bone to optimize fixation. The slotted stem achieves rotational stability in the distal femur through its splines and proximally provides independent adjustment of version, height and offset. A variety of base neck lengths, along with a broad range of femoral head diameters and lengths, provide additional versatility in fine-tuning soft tissue balance around the hip.
Partial Hip Replacement or Hemi-Hip Arthroplasty
Hemi-hip arthroplasty is suitable when there is evidence of a satisfactory natural acetabulum and sufficient femoral bone to seat and support the femoral stem. Hemi-hip arthroplasty is typically indicated in the following conditions: acute fracture of the femoral head or neck that cannot be appropriately reduced and treated with internal fixation, fracture dislocation of the hip that cannot be appropriately reduced and treated with internal fixation, avascular necrosis of the femoral head, non-union of femoral neck fractures, certain high subcapital and femoral neck fractures in the elderly, degenerative arthritis involving only the femoral head in which the acetabulum does not require replacement, pathology involving only the femoral head/neck or proximal femur that can be adequately treated by hemi-hip arthroplasty.
An example of a bone-conserving, partial hip replacement approach, suitable for active patients who suffer from hip pain due to arthritis, dysplasia or avascular necrosis, can be shown through the BIRMINGHAM HIP Resurfacing System (BHR Hip). The implant of the BHR Hip closely matches the size of natural femoral head which is substantially larger than the femoral head of most total hip replacements to date. This increased size is supposed to provide greater stability in the repaired hip joint, and also decrease the chance of dislocation of the implant after surgery. The bearing surfaces of the ball and the socket are made from materials that can significantly reduce joint wear when compared to traditional hip implant materials (cobalt chrome metal and polyethylene).
Further, the BHR Hip implant allows for the conservation of substantially more bone than a typical total hip replacement. Since it is designed to preserve the patient's natural femoral neck and most of the natural femoral head, concerns about leg length discrepancy are addressed. The bone-conserving approach also allows for a regular total hip replacement surgery when needed in the future as opposed to revision surgery as is often the case when a traditional hip replacement needs to be replaced.
Current total hip replacement systems require the removal of the femoral head and the insertion of a hip stem down the shaft of the femur. In contrast, hip resurfacing preserves most, if not all, of the femoral head and the femoral neck; the BHR Hip requires that the femoral head be shaped by a few centimeters in order to fit tightly inside the implant.
Types of Hip Fixation
To date, there are two main types of hip fixation: cemented and porous. Both can be effective, thus, the physician (and the patient) usually chooses a solution that best fits the patient's needs.
A cemented hip implant is usually designed to be implanted using bone cement. For example, bone cement is injected into a prepared femoral canal during a hip arthroplasty surgery. The surgeon then positions the implant within the canal and the bone cement helps to hold it in the desired position.
Alternatively, a porous hip implant is designed to be inserted into a prepared femoral canal without the use of bone cement. Usually, the femoral canal is first prepared so that the implant fits tightly within it. The porous surfaces on the hip implant are designed to engage the bone within the canal and permit bone to grow into the porous surface. Eventually, this bone ingrowth can provide additional fixation to hold the implant in the desired position.
Current fixation mechanisms include 1) block stem as seen in Tri-Lock® (tapered-wedge design; anterior/posterior width of the stem helps provide intimate implant to bone contact to take place proximally at the medial and lateral endosteal cortices); 2) press-fit and cemented stem (femoral canal filling) that is tapered distally as seen in Summit® Basic Hip System; 3) distal fixation with an extensively coated stem (porous coating) as seen in AML® Total Hip System; 4) cementless stems as seen in S-ROM® Modular Hip System (stem's independent neck and sleeve allows for 360 degrees of version adjustment and enables a surgeon to place the proximal sleeve in the best possible bone stock without effecting the stem biomechanics); and 5) short stems, which are easy to insert particularly with an anterior approach; existing short-stem design styles can be categorized into 4 groups: those influenced by the Mayo Conservative stem (Zimmer, Warsaw, Indiana) (Money BF. Short-stemmed uncemented femoral component for primary hip arthroplasty. Clin Orthop Relat Res. 1989; (249):169-175), short and bulky but not neck sparing (eg, Proxima; DePuy, Warsaw, Indiana), neck-sparing curved designs (eg, CFP; Waldemar Link, Hamburg, Germany), and shortened tapered stems (eg, TaperLoc Microplasty; Biomet, Warsaw, Indiana).
Implants
Accordingly, the disclosure provides an implant for surgically repairing a diseased or damaged joint, and in particular, the implant includes one or more patient-adapted features. In certain embodiments, the implant is used to repair a hip joint.
An implant of the disclosure may include a single component or multiple components (i.e., two or more components). The term “implant component” as used herein can include: (i) one of two or more devices that work together in an implant or implant system, or (ii) a complete implant or implant system, for example, in embodiments in which an implant is a single, unitary device. The term “match” as used herein is envisioned to include one or both of a negative-match, as a convex surface fits a concave surface, and a positive-match, as one surface is identical to another surface.
Exemplary patient-adapted (i.e., patient-specific or patient-engineered) features of the implant components described herein are identified in Table 1. One or more of these implant component features can be selected or designed based on patient-specific data/parameters, such as information derived from electronic image data obtained from an image of a patient's joint and optionally other related anatomy.
Traditional implants and implant components can have surfaces and dimensions that are a poor match to a particular patient's biological feature(s). The patient-adapted implants, guide tools, and related methods described herein improve upon these deficiencies. The following two subsections describe two particular improvements, with respect to the bone-facing surface and the joint-facing surface of an implant component; however, the principles described herein are applicable to any aspect of an implant component.
Bone-Facing Surface of an Implant Component
In certain embodiments, the bone-facing surface of an implant can be designed to substantially negatively-match one more bone surfaces. For example, in certain embodiments at least a portion of the bone-facing surface of a patient-adapted implant component can be designed to substantially negatively-match the shape of subchondral bone, cortical bone, endosteal bone, or bone marrow. A portion of the implant also can be designed for resurfacing, for example, by negatively-matching portions of a bone-facing surface of the implant component to the subchondral bone or cartilage. Accordingly, in certain embodiments, the bone-facing surface of an implant component can include one or more portions designed to engage resurfaced or resected bone, for example, by having a surface that negatively-matches uncut subchondral bone or cartilage, and one or more portions designed to engage cut bone, for example, by having a surface that negatively-matches a cut subchondral bone.
In certain embodiments, the bone-facing surface of an implant component includes multiple surfaces, also referred to herein as bone cuts. One or more of the bone cuts on the bone-facing surface of the implant component can be selected or designed to substantially negatively-match one or more surfaces of the patient's joint, including one or more of a resected surface, a resurfaced surface, and an unaltered surface, including one or more of bone, cartilage, and other biological surfaces. For example, in certain embodiments, one or more of the bone cuts on the bone-facing surface of the implant component can be designed to substantially negatively-match (e.g., the number, depth, or angles or orientations of cut) one or more resected surfaces of the patient's bone. The bone-facing surface of the implant component can include any number of bone cuts, for example, two, three, four, less than five, five, more than five, six, seven, eight, nine or more bone cuts. In certain embodiments, the bone cuts of the implant component or the resection cuts to the patient's bone can include one or more facets on corresponding portions (e.g., medial and lateral portions) of an implant component. For example, the facets can be separated by a space or by a step cut connecting two corresponding facets that reside on parallel or non-parallel planes. These bone-facing surface features can be applied to various joint implants, including knee, hip, spine, and shoulder joint implants.
Any one or more bone cuts can include one or more facets. In some embodiments, medial and lateral facets of a bone cut can be coplanar and contiguous. Alternatively or in addition, facets can be separated by a space between corresponding regions of an implant component. Alternatively or in addition, facets of a bone cut can be separated by a transition such as a step cut, for example, a vertical or angled cut connecting two non-coplanar or non-collinear facets of a bone cut. In certain embodiments, one or more bone cut facets, bone cuts, or the entire bone-facing surface of an implant can be non-planar, for example, substantially curvilinear.
In certain embodiments, corresponding sections of an implant component can include different thicknesses (e.g., distance between the component's bone-facing surface and joint-facing surface), surface features, bone cut features, section volumes, or other features. For example, corresponding lateral and medial or sections of a tibial implant component surface can include different thicknesses, section volumes, bone cut angles, and bone cut surface areas. One or more of the thicknesses, section volumes, bone cut angles, bone cut surface areas, bone cut curvatures, numbers of bone cuts, peg placements, peg angles, and other features may vary between two or more sections (e.g., corresponding sections on lateral and medial condyles) of an implant component. Alternatively or in addition, one, more, or all of these features can be the same in corresponding sections of an implant component. An implant design that allows for independent features on different sections of an implant allows various options for achieving one or more goals, including, for example, (1) deformity correction and limb alignment (2) preserving bone, cartilage, or ligaments, (3) preserving or optimizing other features of the patient's anatomy, such as leg length, (4) restoring or optimizing joint kinematics or biomechanics, such as correcting anteversion or retroversion, femoral or acetabular, or achieving a desired degree of rotation of the hip implant; or (5) restoring or optimizing joint-line location or joint gap width.
Alternatively or in addition, corresponding sections of an implant component can be designed to include the same features, for example, the same thickness or at least a threshold thickness. For example, when the corresponding implant sections are exposed to similar stress forces, similar minimum thicknesses can be used in response to those stresses. Alternatively or in addition, an implant design can include a rule, such that a quantifiable feature of one section is greater than, greater than or equal to, less than, or less than or equal to the same feature of another section of the implant component. For example, in certain embodiments, an implant design can include a lateral portion that is thicker than or equal in thickness to the corresponding medial portion. Similarly, in certain embodiments, an implant design can include a lateral height that is higher than or equal to the corresponding medial height.
In certain embodiments, one or more of an implant component's bone cut or bone cut facet features (e.g., thickness, section volume, cut angle, surface area, or other features) can be patient-adapted. For example, as described more fully below, patient-specific data, such as imaging data of a patient's joint, can be used to select or design an implant component (and, optionally, a corresponding surgical procedure or surgical tool) that matches a patient's anatomy or optimizes a parameter of that patient's anatomy. Alternatively or in addition, one or more aspects of an implant component, for example, one or more bone cuts, can be selected or designed to match predetermined resection cuts. “Predetermined” as used herein includes, for example, preoperatively determined (e.g., preoperatively selected or designed). For example, predetermined resection cuts can include resection cuts determined preoperatively, optionally in conjunction with a selection or design of one or more implant component features or one or more guide tool features. Similarly, a surgical guide tool can be selected or designed to guide the predetermined resection cuts.
Joint-Facing Surface of an Implant Component
In various embodiments described herein, the outer, joint-facing surface of an implant component includes one or more patient-adapted (e.g., patient-specific or patient-engineered) features. For example, in certain embodiments, the joint-facing surface of an implant component can be designed to match the shape of the patient's biological structure or anatomy (i.e., to achieve a near anatomic fit). The joint-facing surface can include, for example, the bearing surface portion of the implant component that engages an opposing biological structure or implant component in the joint to facilitate typical movement of the joint. The patient's biological structure can include, for example, cartilage, bone, or one or more other biological structures. The patient's biological structure can also include one or more abnormalities associated with the joint to be repaired, such as for example, cartilage loss, osteophytes, flattening, eburnation, cyst formation, bone sclerosis, other arthritic or congenital deformity, and particular in a hip joint, protrusion acetabuli.
For example, in certain embodiments, the joint-facing surface of an implant component is designed to match the shape of the patient's articular cartilage. For example, the joint-facing surface can substantially positively-match one or more features of the patient's existing cartilage surface or healthy cartilage surface or a calculated cartilage surface, on the articular surface that the component replaces. Alternatively, it can substantially negatively-match one or more features of the patient's existing cartilage surface or healthy cartilage surface or a calculated cartilage surface, on the opposing articular surface in the joint. As described below, corrections can be performed to the shape of diseased cartilage by designing surgical steps (and, optionally, patient-adapted surgical tools) to re-establish a normal or near normal cartilage shape that can then be incorporated into the shape of the joint-facing surface of the component. These corrections can be implemented and, optionally, tested in virtual two-dimensional and three-dimensional models. The corrections and testing can include kinematic analysis or surgical steps.
In certain embodiments, the joint-facing surface of an implant component can be designed to positively-match the shape of subchondral bone. For example, the joint-facing surface of an implant component can substantially positively-match one or more features of the patient's existing subchondral bone surface or healthy subchondral bone surface or a calculated subchondral bone surface, on the articular surface that the component attaches to on its bone-facing surface. Alternatively, it can substantially negatively-match one or more features of the patient's existing subchondral bone surface or healthy subchondral bone surface or a calculated subchondral bone surface, on the opposing articular surface in the joint. Corrections can be performed to the shape of subchondral bone to re-establish a normal or near normal articular shape that can be incorporated into the shape of the component's joint-facing surface. A standard thickness can be added to the joint-facing surface, for example, to reflect an average cartilage thickness. Alternatively, a variable thickness can be applied to the component. The variable thickness can be selected to reflect a patient's actual or healthy cartilage thickness, for example, as measured in the individual patient or selected from a standard reference database.
In certain embodiments, the joint-facing surface of an implant component can include one or more standard features. The standard shape of the joint-facing surface of the component can reflect, at least in part, the shape of typical healthy subchondral bone or cartilage. For example, the joint-facing surface of an implant component can include a curvature having standard radii or curvature of in one or more directions. Alternatively or in addition, an implant component can have a standard thickness or a standard minimum thickness in select areas. Standard thickness(es) can be added to one or more sections of the joint-facing surface of the component or, alternatively, a variable thickness can be applied to the implant component.
Certain embodiments can include, in addition to a first implant component, a second implant component having an opposing joint-facing surface. The second implant component's bone-facing surface or joint-facing surface can be designed as described above. Moreover, in certain embodiments, the joint-facing surface of the second component can be designed, at least in part, to match (e.g., substantially negatively-match) the joint-facing surface of the first component. Designing the joint-facing surface of the second component to complement the joint-facing surface of the first component can help reduce implant wear and optimize kinematics. Thus, in certain embodiments, the joint-facing surfaces of the first and second implant components can include features that do not match the patient's existing anatomy, but instead negatively-match or nearly negatively-match the joint-facing surface of the opposing implant component.
However, when a first implant component's joint-facing surface includes a feature adapted to a patient's biological feature, a second implant component having a feature designed to match that feature of the first implant component also is adapted to the patient's same biological feature. By way of illustration, when a joint-facing surface of a first component is adapted to a portion of the patient's cartilage shape, the opposing joint-facing surface of the second component designed to match that feature of the first implant component also is adapted to the patient's cartilage shape. When the joint-facing surface of the first component is adapted to a portion of a patient's subchondral bone shape, the opposing joint-facing surface of the second component designed to match that feature of the first implant component also is adapted to the patient's subchondral bone shape. When the joint-facing surface of the first component is adapted to a portion of a patient's cortical bone, the joint-facing surface of the second component designed to match that feature of the first implant component also is adapted to the patient's cortical bone shape. When the joint-facing surface of the first component is adapted to a portion of a patient's endosteal bone shape, the opposing joint-facing surface of the second component designed to match that feature of the first implant component also is adapted to the patient's endosteal bone shape. When the joint-facing surface of the first component is adapted to a portion of a patient's bone marrow shape, the opposing joint-facing surface of the second component designed to match that feature of the first implant component also is adapted to the patient's bone marrow shape.
The opposing joint-facing surface of a second component can substantially negatively-match the joint-facing surface of the first component in one plane or dimension, in two planes or dimensions, in three planes or dimensions, or in several planes or dimensions. For example, the opposing joint-facing surface of the second component can substantially negatively-match the joint-facing surface of the first component in the coronal plane only, in the sagittal plane only, or in both the coronal and sagittal planes.
In creating a substantially negatively-matching contour on an opposing joint-facing surface of a second component, geometric considerations can improve wear between the first and second components. Similarly, the radii of a convex curvature on the opposing joint-facing surface of the second component can be selected to match or to be slightly smaller in one or more dimensions than the radii of a concave curvature on the joint-facing surface of the first component. In this way, contact surface area can be maximized between articulating convex and concave curvatures on the respective surfaces of first and second implant components.
The bone-facing surface of the second component can be designed to negatively-match, at least in part, the shape of articular cartilage, subchondral bone, cortical bone, endosteal bone or bone marrow (e.g., surface contour, angle, or perimeter shape of a resected or native biological structure). It can have any of the features described above for the bone-facing surface of the first component, such as having one or more patient-adapted bone cuts to match one or more predetermined resection cuts.
Many combinations of first component and second component bone-facing surfaces and joint-facing surfaces are possible. Table 2 provides illustrative combinations that may be employed.
1S = standard, off-the-shelf, P = patient-specific, PE = patient-engineered (e.g., constant coronal curvature, derived from the patient's coronal curvatures along articular surface)
2Each of the thirteen numbered implant features represents a different exemplary implant feature, for example, for a hip implant the thirteen features can include, but are not limited to: (1) acetabular component's bone facing surface, (2) acetabular component's joint-facing surface, (3) interlock cup or insert, (4) femoral component's bearing or joint-facing surface, (5) femoral component's head resection surface, (6) femoral component's neck resection surface, (7) femoral head resection angle, (8) femoral neck resection angle, (9) femoral neck angle, (10) femoral component length and resulting leg length, (11) femoral shaft medio-lateral dimension, (12) femoral shaft anterior-posterior dimension, (13) femoral shaft length.
Multiple-Component Implant
As described here in, an implant may include one or more implant components. For example, a hip implant of the disclosure may include an acetabular component and a femoral component, which may further include a femoral head component and a femoral shaft component. The implant may further include an interlock cup.
A multiple-component implant may include at least two components, each of which includes one or more patient-adapted features. Alternatively, one or more components may be selected from a library of premade implant components, and such section can be based on the patient-specific data as described herein.
Accordingly, the implants and implant systems described herein include any number of patient-adapted implant components and any number of non-patient-adapted implant components.
A multiple-component implant may include two components, each with one or more features, standard or patient-adapted, that accommodate each other so as to achieve the desired result (e.g., near anatomic fit) upon implantation. For example, an implant designed or selected for repairing a patient's hip joint can include an acetabular component and a femoral component, one or both of these components may include one or more patient-adapted features designed and configured to correct acetabular anteversion or retroversion, or femoral anteversion or retroversion associated with the a patient's hip joint.
In certain embodiments, the degree of acetabular anteversion or retroversion designed or selected for the acetabular component can directly relate to and work in a synchronized manner with the degree of femoral anteversion or retroversion designed or selected for the femoral component. For example, if a surgeon determines that 10 degrees of acetabular anteversion is necessary for the patient, the femoral component in an implant designed or selected for this patient may include 10 degrees of femoral retroversion or a different degree of femoral retroversion. Alternatively, if a surgeon determines that 10 degrees of acetabular anteversion is necessary for the patient, the femoral component in an implant designed or selected for this patient may include 10 degrees of femoral anteversion or a different degree of femoral anteversion.
Accordingly, the femoral component anteversion or retroversion or the acetabular component anteversion or retroversion can be adapted to or adjusted for the surgical approach, e.g. an anterior approach, lateral approach, or posterior approach. This can be included in the design of a patient-specific instrument (e.g. acetabular reaming jig or femoral neck cutting jig or femoral reaming jig). It can also be included in the selection of pre-manufactured or premade femoral or acetabular implant components with a desirable anteversion or retroversion. It can also be included in the design of the femoral component(s) or acetabular component.
In certain embodiments, the angle of the acetabular cup designed or selected for the acetabular component can directly relate to and work in a synchronized manner with the femoral neck angle designed or selected for the femoral component. For example, if a surgeon determines that 20 degrees of acetabular cup angle is necessary for the patient, the femoral component in an implant designed or selected for this patient may include a femoral neck angle of 70 degrees. Alternatively, if a surgeon determines that 25 degrees of acetabular anteversion is necessary for the patient, the femoral component in an implant designed or selected for this patient may include a femoral neck angle of 75 degrees.
The acetabular cup angle can be derived from or determined based on the patient-specific data. For example, the acetabular cup angle can be patient-matched or adapted to the patient's anatomy, but can be a result of compromising, for example, between a desirable acetabular angle for a particular implant design and the patient's native acetabular angle.
Similarly, the femoral neck angle can be derived from or determined based on the patient-specific data. For example, the femoral neck angle can be patient-matched or adapted to the patient's anatomy, but can be a result of compromising, for example, between a desirable femoral neck angle for a particular implant design and the patient's native femoral neck angle.
In certain embodiments, the acetabular cup angle and femoral neck angle can be adjusted relative to each other for and based on a particular implant design, and further based on the patient-specific data.
Accordingly, the femoral component neck angle or the acetabular component acetabular angle can be adapted to or adjusted for the surgical approach, e.g. an anterior approach, lateral approach, or posterior approach. This can be included in the design of a patient-specific instrument (e.g. acetabular reaming jig or femoral neck cutting jig or femoral reaming jig). It can also be included in the selection of pre-manufactured femoral or acetabular implant components with a desirable femoral neck or acetabular cup angle. It can also be included in the design of the femoral component(s) or acetabular component.
Similarly, in certain embodiments, the degree of acetabular cup rotation and the degree of femoral component rotation can be adjusted relative to each other for and based on a particular implant design, and further based on the patient-specific data.
Similarly, in certain embodiments, the orientation of the acetabular component and the orientation of the femoral component can be adjusted relative to each other for and based on a particular implant design, and further based on the patient-specific data.
Hip Implant
In certain embodiments, a hip implant is provided. The implant can include a femoral component that has a femoral head component and a femoral neck component. The femoral component may include one or more patient-adapted features as described herein.
In specific embodiments, the inner opening of a femoral head component may be larger in one or more dimensions (e.g., diameter) than a corresponding femoral neck component. In other embodiments, the inner opening of a femoral head component can be approximately the same in one or more dimensions (e.g., diameter) than a corresponding femoral neck component.
Certain hip resurfacing implants may include a femoral head component and a modular peg or stem, either attached (e.g., rigidly or removably) to or as a part of the femoral head component. The peg or stem can be selected or designed to extend through portions of the femoral neck into the proximal femoral diaphysis. The peg or stem can be selected or designed to be shorter in length and smaller in one or more dimensions (e.g., a cross-sectional diameter) than the stem of a standard total hip replacement implant.
A hip resurfacing implant may include one or more patient-adapted features. Such features can be derived from the patient-specific data as described herein. For example, an image of the patient's hip joint scan can be analyzed using a two-dimensional or three-dimensional models as described herein to determine one or more femoral head, neck and diaphysis dimensions, including, but not limited to, femoral head or neck resection surface, region; femoral head or neck resection angle, region; femoral neck angle (cortical or endosteal); femoral anteversion or retroversion; femoral neck diameter (cortical or endosteal); femoral shaft ML width ML (cortical or endosteal); femoral shaft AP dimension (cortical or endosteal); and femoral shaft length.
Optionally, templates or shapes or CAD rendering of standard hip replacement components can be superimposed onto the femur or the acetabulum image of a patient and a patient adapted or matched component(s) can be selected or designed that have at least one or more dimensions that are smaller than the dimension(s) of the standard component(s), thereby allowing for easier revision later due to preservation of bone stock in an area of potential future revision.
Collecting and Modeling Patient-Specific Data
As mentioned above, certain embodiments include implant components designed and made using patient-specific data that is collected preoperatively. The patient-specific data can include points, surfaces, or landmarks, collectively referred to herein as “reference points.” In certain embodiments, the reference points can be selected and used to derive a varied or altered surface, such as, without limitation, an ideal surface or structure. For example, the reference points can be used to create a model of the patient's relevant biological feature(s) or one or more patient-adapted surgical steps, tools, and implant components. Further, the reference points can be used to design a patient-adapted implant component having at least one patient-specific or patient-engineered feature, such as a surface, dimension, or other feature.
Sets of reference points can be grouped to form reference structures used to create a model of a joint or an implant design. Designed implant surfaces can be derived from single reference points, triangles, polygons, or more complex surfaces, such as parametric or subdivision surfaces, or models of joint material, such as, for example, articular cartilage, subchondral bone, cortical bone, endosteal bone or bone marrow. Various reference points and reference structures can be selected and manipulated to derive a varied or altered surface, such as, without limitation, an ideal surface or structure.
The reference points can be located on or in the joint that receive the patient-adapted implant. For example, the reference points can include weight-bearing surfaces or locations in or on the joint, a cortex in the joint, or an endosteal surface of the joint. The reference points also can include surfaces or locations outside of but related to the joint. Specifically, reference points can include surfaces or locations functionally related to the joint. For example, in embodiments directed to the hip joint, reference points can include one or more locations ranging from the hip down to knee, the ankle or foot. The reference points also can include surfaces or locations homologous to the joint receiving the implant. For example, in embodiments directed to a knee, a hip, or a shoulder joint, reference points can include one or more surfaces or locations from the contralateral knee, hip, or shoulder joint.
In certain embodiments, an imaging data collected from the patient, for example, imaging data from one or more of x-ray imaging, digital tomosynthesis, cone beam CT, non-spiral or spiral CT, non-isotropic or isotropic MRI, SPECT, PET, ultrasound, laser imaging, photo-acoustic imaging, is used to qualitatively or quantitatively measure one or more of a patient's biological features, one or more of normal cartilage, diseased cartilage, a cartilage defect, an area of denuded cartilage, protrusion acetabuli, osteophyte and other abnormalities, acetabular wall thickness, subchondral bone, cortical bone, endosteal bone, bone marrow, a ligament, a ligament attachment or origin, menisci, labrum, a joint capsule, articular structures, or voids or spaces between or within any of these structures. The qualitatively or quantitatively measured biological features can include, but are not limited to, one or more of length, width, height, depth or thickness; curvature, for example, curvature in two dimensions (e.g., curvature in or projected onto a plane), curvature in three dimensions, or a radius or radii of curvature; shape, for example, two-dimensional shape or three-dimensional shape; area, for example, surface area or surface contour; perimeter shape; or volume of, for example, the patient's cartilage, bone (subchondral bone, cortical bone, endosteal bone, or other bone), ligament, or voids or spaces between them.
In certain embodiments, measurements of biological features can include any one or more of the illustrative measurements identified in Table 3.
In certain embodiments, the model that includes at least a portion of the patient's joint also can include or display, as part of the model, one or more resection cuts, one or more drill holes, (e.g., on a model of the patient's femur), one or more guide tools, or one or more implant components that have been designed for the particular patient using the model. Moreover, one or more resection cuts, one or more drill holes, one or more guide tools, or one or more implant components can be modeled and selected or designed separate from a model of a particular patient's biological feature.
Modeling and Addressing Joint Defects
In certain embodiments, the reference points or measurements described above can be processed using mathematical functions to derive virtual, corrected features, which may represent a restored, ideal or desired feature from which a patient-adapted implant component can be designed. For example, one or more features, such as surfaces or dimensions of a biological structure can be modeled, altered, added to, changed, deformed, eliminated, corrected or otherwise manipulated (collectively referred to herein as “variation” of an existing surface or structure within the joint).
Variation of the joint or portions of the joint can include, without limitation, variation of one or more external surfaces, internal surfaces, joint-facing surfaces, uncut surfaces, cut surfaces, altered surfaces, or partial surfaces as well as osteophytes, subchondral cysts, geodes or areas of eburnation, joint flattening, contour irregularity, loss of normal shape, bone sclerosis, other arthritic or congenital deformity, and other abnormalities that may be particular to a joint (e.g., protrusion acetabuli in a hip joint). The surface or structure can be or reflect any surface or structure in the joint, including, without limitation, bone surfaces, ridges, plateaus, cartilage surfaces, ligament surfaces, or other surfaces or structures. The surface or structure derived can be an approximation of a healthy joint surface or structure or can be another variation. The surface or structure can be made to include pathological alterations of the joint. The surface or structure also can be made whereby the pathological joint changes are virtually removed in whole or in part.
Once one or more reference points, measurements, structures, surfaces, models, or combinations thereof have been selected or derived, the resultant shape can be varied, deformed or corrected. In certain embodiments, the variation can be used to select or design an implant component having an ideal or optimized feature or shape, e.g., corresponding to the deformed or corrected joint features or shape. For example, in one application of this embodiment, the ideal or optimized implant shape reflects the shape of the patient's joint before he or she developed arthritis.
Alternatively or in addition, the variation can be used to select or design a patient-adapted surgical procedure to address the deformity or abnormality. For example, the variation can include surgical alterations to the joint, such as virtual resection cuts, virtual drill holes, virtual removal of osteophytes, or virtual building of structural support in the joint that may be desired for a final outcome for the patient. Corrections can be used to address osteophytes, subchondral voids, and other patient-specific defects or abnormalities. In the case of osteophytes, a design for the bone-facing surface of an implant component or guide tool can be selected or designed after the osteophyte has been virtually removed. Alternatively, the osteophyte can be integrated into the shape of the bone-facing surface of the implant component or surgical tool (e.g., a guide tool).
In addition to osteophytes and subchondral voids, the methods, surgical strategies, guide tools, and implant components described herein can be used to address various other patient-specific joint defects or phenomena. In certain embodiments, correction can include the virtual removal of tissue, for example, to address an articular defect, to remove subchondral cysts, or to remove diseased or damaged tissue (e.g., cartilage, bone, or other types of tissue), such as osteochondritic tissue, necrotic tissue, or torn tissue. In such embodiments, the correction can include the virtual removal of the tissue (e.g., the tissue corresponding to the defect, cyst, disease, or damage) and the bone-facing surface of the implant component can be derived after the tissue has been virtually removed. In certain embodiments, the implant component can be selected or designed to include a thickness or other features that substantially matches the removed tissue or optimizes one or more parameters of the joint. Optionally, a surgical strategy or one or more guide tools can be selected or designed to reflect the correction and correspond to the implant component.
Certain embodiments described herein include collecting and using data from imaging tests to virtually determine in one or more planes one or more of an anatomic axis and a mechanical axis and the related misalignment of a patient's limb. The imaging tests that can be used to virtually determine a patient's axis and misalignment can include one or more of such as x-ray imaging, digital tomosynthesis, cone beam CT, non-spiral or spiral CT, non-isotropic or isotropic MRI, SPECT, PET, ultrasound, laser imaging, and photoacoustic imaging, including studies utilizing contrast agents. Data from these tests can be used to determine anatomic reference points or limb alignment, including alignment angles within the same and between different joints or to simulate normal limb alignment. Using the image data, one or more mechanical or anatomical axes, angles, rotations, anteversion/retroversion, orientations, planes or combinations thereof can be determined In certain embodiments, such axes, angles, or planes can include, or be derived from, one or more of a Whiteside's line, Blumensaat's line, transepicondylar line, femoral shaft axis, femoral neck axis, acetabular angle, lines tangent to the superior and inferior acetabular margin, lines tangent to the anterior or posterior acetabular margin, femoral shaft axis, tibial shaft axis, transmalleolar axis, posterior condylar line, tangent(s) to the trochlea of the knee joint, tangents to the medial or lateral patellar facet, lines tangent or perpendicular to the medial and lateral posterior condyles, lines tangent or perpendicular to a central weight-bearing zone of the medial and lateral femoral condyles, lines transecting the medial and lateral posterior condyles, for example through their respective centerpoints, lines tangent or perpendicular to the tibial tuberosity, lines vertical or at an angle to any of the aforementioned lines, or lines tangent to or intersecting the cortical bone of any bone adjacent to or enclosed in a joint. Moreover, estimating a mechanical axis, an angle, or plane also can be performed using image data obtained through two or more joints, such as the knee and ankle joint, for example, by using the femoral shaft axis and a centerpoint or other point in the ankle, such as a point between the malleoli.
As one example, if surgery of the hip is contemplated, the imaging test can include acquiring data through at least one of, or several of, a hip joint, knee joint or ankle joint. As another example, if surgery of the hip joint is contemplated, an acetabular center axis (ACA) can be determined. Conventionally, the anterior pelvic plane (APP) is used to identify the cup and acetabular orientation in navigated THR. As known in the art, the APP is based on the two anterior superior iliac spines (ASIS) and the two pubic tubercles. It has been shown that ACA registration (e.g., 3 points on the acetabular rim) is more accurate with respect to an individual patient than APP registration.
Similarly, any of these determinations can be made in any desired planes, e.g., sagittal or coronal, in two or three dimensions.
Cartilage loss in one compartment can lead to progressive joint deformity. In certain embodiments, cartilage loss can be estimated in the affected compartments. The estimation of cartilage loss can be performed using an ultrasound MRI or CT scan or other imaging modality, optionally with intravenous or intra-articular contrast. The estimation of cartilage loss can be as simple as measuring or estimating the amount of joint space loss seen on x-rays. For the latter, typically standing x-rays are preferred. If cartilage loss is measured from x-rays using joint space loss, cartilage loss on one or two opposing articular surfaces can be estimated by, for example, dividing the measured or estimated joint space loss by two to reflect the cartilage loss on one articular surface. Other ratios or calculations are applicable depending on the joint or the location within the joint. Subsequently, a normal cartilage thickness can be virtually established on one or more articular surfaces by simulating normal cartilage thickness. In this manner, a normal or near normal cartilage surface can be derived. Normal cartilage thickness can be virtually simulated using a computer, for example, based on computer models, for example using the thickness of adjacent normal cartilage, cartilage in a contralateral joint, or other anatomic information including subchondral bone shape or other articular geometries. Cartilage models and estimates of cartilage thickness can also be derived from anatomic reference databases that can be matched, for example, to a patient's weight, sex, height, race, gender, or articular dimension(s), geometry(ies) or shape(s).
In certain embodiments, a patient's limb alignment can be virtually corrected by realigning the knee after establishing a normal cartilage thickness or shape in the affected compartment by moving the joint bodies, for example, femur and tibia, so that the opposing cartilage surfaces including any augmented or derived or virtual cartilage surface touch each other, typically in the preferred contact areas. These contact areas can be simulated for various degrees of flexion or extension.
Leg/Limb Length
In a hip replacement procedure, one important consideration is the resultant leg length of the patient after the surgery. For example, leg-length discrepancy has been a known complication after total hip arthroplasty. Such discrepancy has been associated with complications including nerve palsy, low back pain, and abnormal gait. Further, patients undergoing THR usually require limb lengthening. Conventional methods of intra-operative limb length measurement are based on the distance between two reference points marked on the pelvis and the femur. However, the location of the reference point on the pelvis varies in each case and the line between the two reference points is generally not parallel to the limb lengthening axis, resulting in a discrepancy between intraoperative limb length and post-operative radiographic measurement.
Accordingly, hip implant components and surgical instruments including patient-adapted instruments or jigs can be selected or designed to achieve a desired leg length, for example the same leg length that the patient had in the affected extremity prior to the surgery, the desired lengthened leg length, or the desired length equality between the two limbs.
Leg length can be determined preoperatively, for example with use of a clinical examination, an x-ray, a CT scan, a CT scout scan, or an MRI scan or any other technology. Leg length can be determined using anatomic landmarks known in the art, e.g. location of the ankle joint line, knee joint line, hip joint line, center of the femoral head.
To illustrate, a best fitting implant or implant components can be selected or a patient-adapted implant or implant components can be designed based the patient-specific data. A composite thickness of the acetabular component of the implant can then be determined. A composite length of femoral component can also be determined, based on a combination of stem length, femoral neck length, femoral neck angle, femoral ante or retroversion (as planned or desired).
A virtual simulation of the surgical procedure is then conducted. The surgical approach may begin with the acetabulum or alternatively the femur. The following factors may contribute to the resultant leg length: length of femoral diaphysis or neck reaming to accommodate stem; location of femoral head or neck resection; angle of femoral head or neck resection. The virtual modeling can optimize one or more of these factors so that the resultant leg length accounting for composite femoral and acetabular component thickness or length is identical or similar to desired leg length, e.g. leg length prior to resection, or leg length of contralateral side or combinations thereof, or either with a surgeon selected offset applied.
Patient-specific jigs can be adapted or designed for the above simulations. For example, the angle of any resection guides can be designed to accommodate the desired resection angles, e.g. femoral neck resection angle, or to accommodate a desired resection level, e.g. femoral neck resection angle.
In certain embodiments, the leg length can determined or maintained by referencing one or more anatomic landmarks.
Preserving Bone, Cartilage or Ligament
Traditional orthopedic implants incorporate bone cuts. These bone cuts achieve two objectives: they establish a shape of the bone that is adapted to the implant and they help achieve a normal or near normal axis alignment. With a traditional implant, multiple bone cuts are placed. However, since traditional implants are manufactured off-the-shelf without use of patient-specific information, these bone cuts are pre-set for a given implant without taking into consideration the unique shape of the patient. Thus, by cutting the patient's bone to fit the traditional implant, more bone is discarded than is necessary with an implant that is specifically designed or selected to address the particularly patient's structures and deficiencies.
In certain embodiments, resection cuts are optimized to preserve the maximum amount of bone for each individual patient, based on a series of two-dimensional images or a three-dimensional representation of the patient's articular anatomy and shape or geometry and the desired limb alignment or desired deformity correction. Resection cuts on two opposing articular surfaces can be optimized to achieve the minimum amount of bone resected from one or both articular surfaces.
By adapting resection cuts in the series of two-dimensional images or the three-dimensional representation or model on two opposing articular surfaces such as, for example, a femoral head and an acetabulum, one or both femoral condyle(s) and a tibial plateau, a trochlea and a patella, a glenoid and a humeral head, a talar dome and a tibial plafond, a distal humerus and a radial head or an ulna, or a radius and a scaphoid, certain embodiments allow for patient individualized, bone-preserving implant designs that can assist with proper ligament balancing and that can help avoid “overstuffing” of the joint, while achieving optimal bone preservation on one or more articular surfaces in each patient.
Any implant component can be selected or adapted in shape so that it stays clear of ligament structures. Imaging data can help identify or derive shape or location information on such ligamentous structures. For example, in a shoulder, the glenoid component can include a shape or concavity or divot to avoid a subscapularis tendon or a biceps tendon. In a hip, the femoral component can be selected or designed to avoid an iliopsoas or adductor tendons.
Establishing Normal or Near-Normal Joint Kinematics
In certain embodiments, bone cuts and implant shape including at least one of a bone-facing or a joint-facing surface of the implant can be designed or selected to achieve normal joint kinematics.
In certain embodiments, a computer program simulating biomotion of one or more joints, such as, for example, a knee joint, or a knee and ankle joint, or a hip, knee or ankle joint can be utilized. In certain embodiments, patient-specific imaging data can be fed into this computer program. For example, a series of two-dimensional images of a patient's hip joint or a three-dimensional representation of a patient's hip joint can be entered into the program. Additionally, two-dimensional images or a three-dimensional representation of the patient's corresponding knee joint or ankle joint may be added.
Optionally, other data including anthropometric data may be added for each patient. These data can include but are not limited to the patient's age, gender, weight, height, size, body mass index, and race. Desired limb alignment, leg length or deformity correction can be added into the model. The position of bone cuts on one or more articular surfaces as well as the intended location of implant bearing surfaces on one or more articular surfaces can be entered into the model.
A patient-specific biomotion model can be derived that includes combinations of parameters listed above. The biomotion model can simulate various activities of daily life including normal gait, stair climbing, descending stairs, running, kneeling, squatting, sitting and any other physical activity. The biomotion model can start out with standardized activities, typically derived from reference databases. These reference databases can be, for example, generated using biomotion measurements using force plates and motion trackers using radiofrequency or optical markers and video equipment.
The biomotion model can then be individualized with use of patient-specific information including at least one of, but not limited to the patient's age, gender, weight, height, body mass index, and race, the desired limb alignment or deformity correction, and the patient's imaging data, for example, a series of two-dimensional images or a three-dimensional representation or model of the joint for which surgery is contemplated.
An implant shape including associated bone cuts generated in the preceding optimizations, for example, limb alignment, leg length, deformity correction, bone preservation on one or more articular surfaces, can be introduced into the model. The resultant biomotion data can be used to further optimize the implant design with the objective to establish normal or near normal kinematics. The implant optimizations can include one or multiple implant components. Implant optimizations based on patient-specific data including image based biomotion data include, but are not limited to: changes to external, joint-facing implant shape in coronal plane; changes to external, joint-facing implant shape in sagittal plane; changes to external, joint-facing implant shape in axial plane; changes to external, joint-facing implant shape in multiple planes or three dimensions; changes to internal, bone-facing implant shape in coronal plane; changes to internal, bone-facing implant shape in sagittal plane; changes to internal, bone-facing implant shape in axial plane; changes to internal, bone-facing implant shape in multiple planes or three dimensions; changes to one or more bone cuts, for example with regard to depth of cut, orientation of cut.
Any single one or combinations of the above or all of the above on at least one articular surface or implant component or multiple articular surfaces or implant components.
When changes are made on multiple articular surfaces or implant components, these can be made in reference to or linked to each other. For example, in the knee, a change made to a femoral bone cut based on patient-specific biomotion data can be referenced to or linked with a concomitant change to a bone cut on an opposing tibial surface, for example, if less femoral bone is resected, the computer program may elect to resect more tibial bone.
Similarly, in a hip implant, if an acetabular component shape is changed, for example on an external or joint-facing surface, this can be accompanied by a change in the femoral component shape. This is, for example, particularly applicable when at least portions of the femoral head bearing surface negatively-match the acetabular joint-facing surface.
Similarly, in a hip implant, if a femoral component shape is changed, for example on an external surface, this can be accompanied by a change in an acetabular component shape. This is, for example, particularly applicable when at least portions of the acetabular joint-facing surface substantially negatively-match the femoral joint-facing surface. For example, the acetabular rim can be altered, for example via reaming or cutting. These surgical changes and resultant change on cortical bone profile can be virtually simulated and a new resultant peripheral margin(s) can be derived. The derived peripheral bone margin or shape can then be used to design or select an implant that substantially matches, in at least a portion, the altered rim or joint margin or edge.
By optimizing implant shape in this manner, it is possible to establish normal or near normal kinematics. Moreover, it is possible to avoid implant related complications, including but not limited to anterior notching, notch impingement, posterior femoral component impingement in high flexion, and other complications associated with existing implant designs.
Biomotion models for a particular patient can be supplemented with patient-specific data or finite element modeling or other biomechanical models known in the art.
Complex Modeling
As described herein, certain embodiments can apply modeling, for example, virtual modeling or mathematical modeling, to identify optimum implant component features and measurements, and optionally resection features and measurements, to achieve or advance one or more parameter targets or thresholds. For example, a model of patient's joint or limb can be used to identify, select, or design one or more optimum features or feature measurements relative to selected parameters for an implant component and, optionally, for corresponding resection cuts or guide tools. In certain embodiments, a physician, clinician, or other user can select one or more parameters, parameter thresholds or targets, or relative weightings for the parameters included in the model. Alternatively or in addition, clinical data, for example obtained from clinical trials, or intraoperative data, can be included in selecting parameter targets or thresholds, or in determining optimum features or feature measurements for an implant component, resection cut, or guide tool.
Any combination of one or more of the above-identified parameters or one or more additional parameters can be used in the design or selection of a patient-adapted (e.g., patient-specific or patient-engineered) implant component and, in certain embodiments, in the design or selection of corresponding patient-adapted resection cuts or patient-adapted guide tools. In particular assessments, a patient's biological features and feature measurements are used to select or design one or more implant component features and feature measurements, resection cut features and feature measurements, or guide tool features and feature measurements.
The optimization ofjoint kinematics can include, as another parameter, the goal of not moving the joint line postoperatively or minimizing any movements of the joint line, or any threshold values or cut off values for moving the joint line superiorly or inferiorly. The optimization ofjoint kinematics can also include ligament loading or function during motion.
As described herein, implants of various sizes, shapes, curvatures and thicknesses with various types and locations and orientations and number of bone cuts can be selected or designed and manufactured. The implant designs or implant components can be selected from, catalogued in, or stored in a library. The library can be a virtual library of implants, or components, or component features that can be combined or altered to create a final implant. The library can include a catalogue of physical implant components. In certain embodiments, physical implant components can be identified and selected using the library. The library can include previously-generated implant components having one or more patient-adapted features, or components with standard or blank features that can be altered to be patient-adapted. Accordingly, implants or implant features can be selected from the library.
Accordingly, in certain embodiments an implant can include one or more features designed patient-specifically and one or more features selected from one or more library sources.
In certain embodiments, a library can be generated to include images from a particular patient at one or more ages prior to the time that the patient needs a joint implant. For example, a method can include identifying patients eliciting one or more risk factors for a joint problem, such as low bone mineral density score, and collecting one or more images of the patient's joints into a library. In certain embodiments, all patients below a certain age, for example, all patients below 40 years of age can be scanned to collect one or more images of the patient's joint. The images and data collected from the patient can be banked or stored in a patient-specific database. For example, the articular shape of the patient's joint or joints can be stored in an electronic database until the time when the patient needs an implant. Then, the images and data in the patient-specific database can be accessed and a patient-specific or patient-engineered partial or total joint replacement implant using the patient's originally anatomy, not affected by arthritic deformity yet, can be generated. This process results is a more functional and more anatomic implant.
Locking Mechanisms
An implant or implant component as disclosed herein may have at least two parts, made of the same or different materials, such as metal or polymeric material (e.g., oxidation resistant UHMWPE). Various embodiments of implants herein can include a scaffold or stage with one or more polymer inserts that can be inserted and locked into the scaffold. One exemplary embodiment is an acetabular cup implant for a hip joint that is configured to be implanted onto a patient's acetabulum for receiving the femoral head or femoral implant. The acetabular implant comprises at least two components: a first component that engages the acetabulum/socket, which can be made of metal; and a second component that is configured to articulate with the femoral head component of a femoral implant, which can be made of non-metal, e.g., plastic polymer, to provide a non-metal articulating surface.
The first acetabular component can be shaped generally as a hemisphere that fits the patient's acetabulum. In certain embodiments, the first acetabular component includes a first surface that engages with the acetabulum and a second surface that engages the femoral implant and provides the articulating surface. The first surface is preferably designed or selected with one or more patient-adapted features (e.g., size, shape, curvature) and provides an anatomic or near anatomic fit with the patient's acetabulum.
The second surface of the first acetabular component can be substantially flat or can have at least one or more curved portions. There can be a wall that spans the perimeter (anterior, posterior, medial, or lateral) of the second surface. This wall can optionally contain grooves along the inner surface for accepting an insert component of the implant, e.g., the second acetabular component. The wall can extend into the middle of the second surface of the first acetabular component from the posterior side towards the anterior side, approximately halfway between the medial and lateral sides, creating a peninsular wall on the second surface. The outward facing sides of this peninsular wall can optionally be sloped for mating with the insert component of the implant. Towards the end of the peninsular wall, receptacles can optionally be cut into either side of the wall for receiving an optional locking member formed into the surface of the insert of the implant. Perpendicular to the peninsular wall there can be one or more grooves cut into the second surface of the first acetabular component for accepting a notched portion extending from a surface of the insert of the implant. One (e.g., anterior) side of the second surface of the first acetabular component can contain at least one slanted surface that acts as a ramp to assist with proper alignment and engagement of the insert component with the first acetabular component.
The articulating component, or insert component, has a first surface and a second surface. The first surface of the insert component can be shaped to align with the shape or geometry of the joint or the bearing surface of the opposite implant component by having one or more concave surfaces that are articulate with the convex surfaces of the femoral implant.
The lower surface of the insert component can be flat and is configured to mate with the second surface of the first component of the implant. The posterior side of the implant can be cut out from approximately halfway up the medial side of the implant to approximately halfway down the lateral side of the implant to align with the geometrically matched wall of the second surface of the first acetabular component. The remaining structure on the lower surface of the implant can have a ledge extending along the medial and posterior sides of the surface for lockably mating with the grooves of the interior walls of the second surface of the first acetabular component. Approximately halfway between the medial side and the lateral side of the implant, a canal can be formed from the posterior side of the implant towards the anterior side of the implant, for mating with the peninsular wall of the second surface of the first acetabular component. This canal can run approximately ¾ the length of the implant from the posterior to anterior of the lower surface of the implant. The exterior walls of this canal can be sloped inward from the bottom of the canal to the top of the canal creating a surface that dovetails with the sloped peninsular walls of the second surface of the first acetabular component. This dovetail joint can assist with proper alignment of the insert into the first acetabular component and then locks the insert into the first acetabular component once fully inserted. At the anterior end of the canal, there can be a locking mechanism consisting of bendable fingers that snap optionally into the receptacles cut into the interior of the peninsular walls upon insertion of the insert into the first acetabular component of the implant, thereby locking the implant component into the first acetabular component. Perpendicular to the canal running ¾ the length of the lower surface of the insert can be at least one notch for mating with the at least one groove cut out of the upper surface of the first acetabular component. Engagement between the first acetabular component and the second acetabular component can be fixed or reversible
Similarly, a femoral implant or implant component in certain embodiments includes two components, with a first femoral component engages the patient's femur and a second femoral component that engages the first femoral component and provides the articulating surface to engage with the articulating surface of the acetabular implant component. The first femoral component can be made of metal, whereas the second femoral component can include or provide a non-metal articulating surface. Engagement between the first femoral component and the second femoral component can be fixed or reversible.
Thus, multiple locking mechanisms can be designed into the opposing surfaces of the walls and canal of the insert and the implant component, as well as the notch and groove and they can help to lock the insert into place on the first acetabular or femoral component and resist against various motions within the joint.
Manufacturing and Machining
The implants and implant components of this disclosure can be machined, molded, casted, manufactured through additive techniques such as laser sintering or electron beam melting or otherwise constructed out of a metal or metal alloy such as cobalt chromium. Similarly, an insert component may be machined, molded, manufactured through rapid prototyping or additive techniques or otherwise constructed out of a plastic polymer such as ultra high molecular weight polyethylene.
An example of such a plastic polymer is vitamin E-infused or cross-linked high or ultra-high molecular weight polyethylene. Other examples of plastic polymers can be found in the art, such as those described in U.S. Patent Application Publication Nos. 20110112646 20110109017, 20070004818, etc. Ultra-high molecular weight polyethylene (UHMWPE) generally refers to linear non-branched chains of ethylene having molecular weights in excess of about 500,000, preferably above about 1,000,000, and more preferably above about 2,000,000. Often the molecular weights can reach about 8,000,000 or more. Oxidation resistant cross-linked polymeric material, such as ultra-high molecular weight polyethylene (UHMWPE), is desired in medical devices because it significantly increases the wear resistance of the devices. The conventional method of crosslinking is by exposing the UHMWPE to ionizing radiation. Other methods also include doping the UHMWPE with antioxidants, such as vitamin E.
Other known materials, such as ceramics including ceramic coating, may be used as well, for one or both components, or in combination with the metal, metal alloy and polymer described above. It can be appreciated by those of skill in the art that an implant may be constructed as one piece out of any of the above, or other, materials, or in multiple pieces out of a combination of materials. For example, an implant may include one or more surfaces, particularly joint-facing surfaces or bearing surfaces that includes a coating of a material other than metal (e.g., a ceramic coating or a plastic polymer coating or insert component), whereas the implant or implant component includes a metal backing. For example, an implant or implant component constructed of a polymer with a two-piece insert component constructed one piece out of a metal alloy and the other piece constructed out of ceramic.
Each of the components may be constructed as a “standard” or “blank” in various sizes or may be specifically formed for each patient based on the patient-specific data. Computer modeling may be used and a library of virtual standards may be created for each of the components. A library of physical standards may also be amassed for each of the components.
Imaging data including shape, geometry, e.g., radius (or radii) (e.g., of the acetabulum), M-L, A-P, and S-I dimensions, then can be used to select the standard component, e.g., a femoral component or an acetabular component that most closely approximates the select features of the patient's anatomy. Typically, these components are selected so that they are slightly larger than the patient's articular structure that are be replaced in at least one or more dimensions. The standard component is then adapted to the patient's unique anatomy, for example by removing overhanging material, e.g. using machining or other further shaping.
Thus, referring to the flow chart shown in
As illustrated in
The obtained patient's biological features and feature measurements, implant component features and feature measurements, and, optionally, resection cut and/or guide tool features and/or feature measurements then can be assessed to determine the optimum implant component features and/or feature measurements, and optionally, resection cut and/or guide tool features and/or feature measurements, that achieve one or more target or threshold values for parameters of interest 2630 (e.g., by maintaining or restoring a patient's healthy joint feature). As noted, parameters of interest can include, for example, one or more of (1) joint deformity correction; (2) limb alignment correction; (3) bone, cartilage, and/or ligaments preservation at the joint; (4) preservation, restoration, or enhancement of one or more features of the patient's biology, for example, trochlea and trochlear shape; (5) preservation, restoration, or enhancement of joint kinematics, including, for example, ligament function and implant impingement; (6) preservation, restoration, or enhancement of the patient's joint-line location and/or joint gap width; and (7) preservation, restoration, or enhancement of other target features. This step can be repeated as desired. For example, the assessment step 2630 can be reiteratively repeated after obtaining various feature and feature measurement information 2600, 2610, 2620.
Once the one or more optimum implant component features and/or feature measurements are determined, the implant component(s) can be selected 2640, designed 2650, or selected and designed 2640, 2650. For example, an implant component having some optimum features and/or feature measurements can be designed using one or more CAD software programs or other specialized software to optimize additional features or feature measurements of the implant component. One or more manufacturing techniques described herein or known in the art can be used in the design step to produce the additional optimized features and/or feature measurements. This process can be repeated as desired.
Optionally, one or more resection cut features and/or feature measurements can be selected 2660, designed 2670, or selected and further designed 2660, 2670. For example, a resection cut strategy selected to have some optimum features and/or feature measurements can be designed further using one or more CAD software programs or other specialized software to optimize additional features or measurements of the resection cuts, for example, so that the resected surfaces substantially match optimized bone-facing surfaces of the selected and designed implant component. This process can be repeated as desired.
Moreover, optionally, one or more guide tool features and/or feature measurements can be selected, designed, or selected and further designed. For example, a guide tool having some optimum features and/or feature measurements can be designed further using one or more CAD software programs or other specialized software to optimize additional features or feature measurements of the guide tool. One or more manufacturing techniques described herein or known in the art can be used in the design step to produce the additional, optimized features and/or feature measurements, for example, to facilitate one or more resection cuts that, optionally, substantially match one or more optimized bone-facing surfaces of a selected and designed implant component. This process can be repeated as desired.
As will be appreciated by those of skill in the art, the process of selecting and/or designing an implant component feature and/or feature measurement, resection cut feature and/or feature measurement, and/or guide tool feature and/or feature measurement can be tested against the information obtained regarding the patient's biological features, for example, from one or more MRI or CT or x-ray images from the patient, to ensure that the features and/or feature measurements are optimum with respect to the selected parameter targets or thresholds. Testing can be accomplished by, for example, superimposing the implant image over the image for the patient's joint. In a similar manner, load-bearing measurements and/or virtual simulations thereof may be utilized to optimize or otherwise alter a derived implant design. For example, where a proposed implant for a hip implant has been designed, it may then be virtually inserted into a biomechanical model or otherwise analyzed relative to the load-bearing conditions (or virtually simulations thereof) it may encounter after implantation. These conditions may indicate that one or more features of the implant are undesirable for varying reasons (i.e., the implant design creates unwanted anatomical impingement points, the implant design causes the joint to function in an undesirable fashion, the joint design somehow interferes with surrounding anatomy, the joint design creates a cosmetically-undesirable feature on the repaired limb or skin covering thereof, FEA or other loading analysis of the joint design indicates areas of high material failure risk, FEA or other loading analysis of the joint design indicates areas of high design failure risk, FEA or other loading analysis of the joint design indicates areas of high failure risk of the supporting or surrounding anatomical structures, etc.). In such a case, such undesirable features may be accommodated or otherwise ameliorated by further design iteration and/or modification that might not have been discovered without such analysis relative to the “real world” measurements and/or simulation.
Such load-bearing/modeling analysis may also be used to further optimize or otherwise modify the implant design, such as where the implant analysis indicates that the current design is “over-engineered” in some manner than required to accommodate the patient's biomechanical needs. In such a case, the implant design may be further modified and/or redesigned to more accurately accommodate the patient's needs, which may have an unintended (but potentially highly-desirable) consequence of reducing implant size or thickness, increasing or altering the number of potential implant component materials (due to altered requirements for material strength and/or flexibility), increasing estimate life of the implant, reduce wear or otherwise altering one or more of the various design “constraints” or limitations currently accommodated by the present design features of the implant.
Once optimum features and/or feature measurements for the implant component, and optionally for the resection cuts and/or guide tools, have been selected and/or designed, the implant site can be prepared, for example by removing cartilage and/or resectioning bone from the joint surface, and the implant component can be implanted into the joint 2680.
The joint implant component bone-facing surface, and optionally the resection cuts and guide tools, can be selected and/or designed to include one or more features that achieve an anatomic or near anatomic fit with the existing surface or with a resected surface of the joint. Moreover, the joint implant component joint-facing surface, and optionally the resection cuts and guide tools, can be selected and/or designed, for example, to replicate the patient's existing joint anatomy, to replicate the patient's healthy joint anatomy, to enhance the patient's joint anatomy, and/or to optimize fit with an opposing implant component. Accordingly, both the existing surface of the joint and the desired resulting surface of the joint can be assessed. This technique can be particularly useful for implants that are not anchored into the bone.
As will be appreciated by those of skill in the art, the physician, or other person can obtain a measurement of a biological feature (e.g., a hip joint) 2600 and then directly select 2640, design, 2650, or select and design 2640, 2650 a joint implant component having desired patient-adapted features and/or feature measurements. Designing can include, for example, design and manufacturing.
In the step 2640, one or more standard components, e.g., a femoral component or an acetabular component or acetabular insert, are selected. These are selected so that they are at least slightly greater than one or more of the derived patient-specific articular dimensions and so that they can be shaped to the patient-specific articular dimensions. Alternatively, these are selected so that they do not interfere with any adjacent soft-tissue structures. Combinations of both are possible.
If an implant component is used that includes an insert, e.g., a polyethylene insert and a locking mechanism in a metal or ceramic base, the locking mechanism can be adapted to the patient's specific anatomy in at least one or more dimensions. The locking mechanism can also be patient adapted in all dimensions. The location of locking features can be patient adapted while the locking feature dimensions, for example between an acetabular cup and an acetabular insert, can be fixed. Alternatively, the locking mechanism can be pre-fabricated; in this embodiment, the location and dimensions of the locking mechanism also is considered in the selection of the pre-fabricated components, so that any adaptations to the metal or ceramic backing relative to the patient's articular anatomy do not compromise the locking mechanism. Thus, the components can be selected so that after adaptation to the patient's unique anatomy a minimum material thickness of the metal or ceramic backing is maintained adjacent to the locking mechanism.
In some embodiments, a pre-manufactured metal backing blank can be selected so that its exterior dimensions are slightly greater than the derived patient-specific dimensions or geometry in at least one or more directions, while, optionally, at the same time not interfering with ligaments. The pre-manufactured metal backing blank can include a pre-manufactured locking mechanism for an insert, e.g. a polyethylene insert. The locking mechanism can be completely pre-manufactured, i.e. not requiring any patient adaptation. Alternatively, the locking mechanism can have pre-manufactured components, e.g. an anterior locking tab or feature, with other locking features that will be machined later based on patient-specific dimensions, e.g. a posterior locking tab or feature at a distance from the anterior locking feature that is derived from patient-specific imaging data. In this setting, the pre-manufactured metal blank will be selected so that at least the anterior locking feature will fall inside the derived patient-specific articular dimensions. In a specific embodiment, all pre-manufactured locking features on the metal backing and an insert will fall inside the derived patient-specific articular dimensions. Thus, when the blank is adapted to the patient's specific geometry, shape, or dimensions (e.g., size, thickness, or curvature), the integrity of the lock is not compromised and will remain preserved. An exemplary, by no means limiting, process flow is provided below:
Those of skill in the art will appreciate that not all of these process steps will be required to design, select or adapt an implant to the patient's anatomy, geometry, shape, or one or more dimensions. Moreover, additional steps may be added, for example kinematic adaptations or finite element modeling of implant components including locks. Finite element modeling can be performed based on patient-specific input data including patient-specific articular shape or geometry and virtually derived implant component shapes.
It is contemplated that all combinations of pre-manufactured and patient adapted lock features are possible, including pre-manufactured lock features on a medial insert and patient-specific lock features on a lateral insert or the reverse. Other locations of lock features are possible.
Those of skill in the art can appreciate that a combination of standard and customized components may be used in conjunction with each other. For example, a standard tray component may be used with an insert component that has been individually constructed for a specific patient based on the patient's anatomy and joint information.
An implant component can include a fixed bearing design or a mobile bearing design. With a fixed bearing design, a platform of the implant component is fixed and does not rotate. However, with a mobile bearing design, the platform of the implant component is designed to rotate e.g., in response to the dynamic forces and stresses on the joint during motion. In certain embodiments, an implant can include a mobile-bearing implant that includes one or more patient-specific features, one or more patient-engineered features, or one or more standard features.
The step of designing or selecting an implant or surgical tool as described herein can include both configuring one or more features, measurements, or dimensions of the implant or surgical tool (e.g., derived from patient-specific data from a particular patient and adapted for the particular patient) and manufacturing the implant. In certain embodiments, manufacturing can include making the implant or guide tool from starting materials, for example, metals or polymers or other materials in solid (e.g., powders or blocks) or liquid form. In addition or alternatively, in certain embodiments, manufacturing can include altering (e.g., machining) an existing implant component or guide tool, for example, a standard blank implant component or guide tool or an existing implant or guide tool (e.g., selected from a library). The manufacturing techniques to making or altering an implant component or guide tool can include any techniques known in the art today and in the future. Such techniques include, but are not limited to additive as well as subtractive methods, i.e., methods that add material, for example to a standard blank, and methods that remove material, for example from a standard blank.
Various technologies appropriate for this purpose are known in the art, for example, as described in Wohlers Report 2009, State of the Industry Annual Worldwide Progress Report on Additive Manufacturing, Wohlers Associates, 2009 (ISBN 0-9754429-5-3), available from the web www.wohlersassociates.com; Pham and Dimov, Rapid manufacturing, Springer-Verlag, 2001 (ISBN 1-85233-360-X); Grenda, Printing the Future, The 3D Printing and Rapid Prototyping Source Book, Castle Island Co., 2009; Virtual Prototyping & Bio Manufacturing in Medical Applications, Bidanda and Bartolo (Eds.), Springer, Dec. 17, 2007 (ISBN: 10: 0387334297; 13: 978-0387334295); Bio-Materials and Prototyping Applications in Medicine, Bartolo and Bidanda (Eds.), Springer, Dec. 10, 2007 (ISBN: 10: 0387476822; 13: 978-0387476827); Liou, Rapid Prototyping and Engineering Applications: A Toolbox for Prototype Development, CRC, Sep. 26, 2007 (ISBN: 10: 0849334098; 13: 978-0849334092); Advanced Manufacturing Technology for Medical Applications: Reverse Engineering, Software Conversion and Rapid Prototyping, Gibson (Ed.), Wiley, January 2006 (ISBN: 10: 0470016884; 13: 978-0470016886); and Branner et al., “Coupled Field Simulation in Additive Layer Manufacturing,” 3rd International Conference PMI, 2008 (10 pages).
Rapid Prototyping, other Manufacturing Techniques
Rapid prototyping is a technique for fabricating a three-dimensional object from a computer model of the object. A special printer is used to fabricate the prototype from a plurality of two-dimensional layers. Computer software sections the representations of the object into a plurality of distinct two-dimensional layers and then a three-dimensional printer fabricates a layer of material for each layer sectioned by the software. Together the various fabricated layers form the desired prototype. More information about rapid prototyping techniques is available in US Patent Publication No. 2002/0079601A1 to Russell et al., published Jun. 27, 2002. An advantage to using rapid prototyping is that it enables the use of free form fabrication techniques that use toxic or potent compounds safely. These compounds can be safely incorporated in an excipient envelope, which reduces worker exposure.
A powder piston and build bed are provided. Powder includes any material (metal, plastic, etc.) that can be made into a powder or bonded with a liquid. The power is rolled from a feeder source with a spreader onto a surface of a bed. The thickness of the layer is controlled by the computer. The print head then deposits a binder fluid onto the powder layer at a location where it is desired that the powder bind. Powder is again rolled into the build bed and the process is repeated, with the binding fluid deposition being controlled at each layer to correspond to the three-dimensional location of the device formation. For a further discussion of this process see, for example, US Patent Publication No 2003/017365A1 to Monkhouse et al. published Sep. 18, 2003.
The rapid prototyping can use the two dimensional images obtained, as described above herein, to determine each of the two-dimensional shapes for each of the layers of the prototyping machine. In this scenario, each two dimensional image slice would correspond to a two dimensional prototype slide. Alternatively, the three-dimensional shape of the defect can be determined, as described herein, and then broken down into two dimensional slices for the rapid prototyping process. The advantage of using the three-dimensional model is that the two-dimensional slices used for the rapid prototyping machine can be along the same plane as the two-dimensional images taken or along a different plane altogether.
Rapid prototyping can be combined or used in conjunction with casting techniques. For example, a shell or container with inner dimensions corresponding to an articular repair system including surgical instruments, molds, alignment guides or surgical guides, can be made using rapid prototyping. Plastic or wax-like materials are typically used for this purpose. The inside of the container can subsequently be coated, for example with a ceramic, for subsequent casting. Using this process, personalized casts can be generated.
Rapid prototyping can be used for producing articular repair systems including implants and components, surgical tools, molds, alignment guides, cut guides etc. Rapid prototyping can be performed at a manufacturing facility. Alternatively, it may be performed in the operating room after an intraoperative measurement has been performed.
Alternatively, milling techniques can be utilized for producing articular repair systems including surgical tools, molds, alignment guides, cut guides etc.
Alternatively, laser based techniques can be utilized for producing articular repair systems including surgical tools, molds, alignment guides, cut guides etc.
Surgical Tools
Surgical assistance can be provided by using a device applied to the outer surface of the articular cartilage or the bone, including the subchondral bone, in order to match the alignment of the articular repair system and the recipient site or the joint. The device can be round, circular, oval, ellipsoid, curved or irregular in shape. The shape can be selected or adjusted to match or enclose an area of diseased cartilage or an area slightly larger than the area of diseased cartilage or substantially larger than the diseased cartilage. The area can encompass the entire articular surface or the weight bearing surface. Such devices are typically preferred when replacement of a majority or an entire articular surface is contemplated.
Mechanical devices can be used for surgical assistance (e.g., surgical tools), for example using gels, molds, plastics or metal. One or more electronic images or intraoperative measurements can be obtained providing object coordinates that define the articular or bone surface and shape. These objects' coordinates can be utilized to either shape the device, e.g. using a CAD/CAM technique, to be adapted to a patient's articular anatomy or, alternatively, to select a typically pre-made device that has a good fit with a patient's articular anatomy. The device can have a surface and shape that will match all or at least a portion of the articular cartilage, subchondral bone or other bone surface and shape, e.g. similar to a substantial negative of the corresponding joint surface. The device can include, without limitation, one or more guides such as cut planes, apertures, slots or holes to accommodate surgical instruments such as drills, reamers, curettes, k-wires, screws and saws.
The device may have a single component or multiple components. The components may be attached to the unoperated and operated portions of the intra- or extra-articular anatomy. For example, one component may be attached to the femoral neck, while another component may be in contact with the greater or lesser trochanter. Typically, the different components can be used to assist with different parts of the surgical procedure. When multiple components are used, one or more components may also be attached to a different component rather than the articular cartilage, subchondral bone or other areas of osseous or non-osseous anatomy.
Components may also be designed to fit to the joint after an operative step has been performed. For example, in a hip, one component may be used to perform an initial cut, for example through the femoral neck, while another subsequently used component may be designed to fit on the femoral neck after the cut, for example covering the area of the cut with a central opening for insertion of a reamer. Using this approach, subsequent surgical steps may also be performed with high accuracy, e.g. reaming of the marrow cavity.
In another embodiment, a guide may be attached to a mold to control the direction and orientation of surgical instruments. For example, after the femoral neck has been cut, a mold may be attached to the area of the cut, whereby it fits portions or all of the exposed bone surface. The mold may have an opening adapted for a reamer. Before the reamer is introduced a femoral reamer guide may be inserted into the mold and advanced into the marrow cavity. The position and orientation of the reamer guide may be determined by the femoral mold. The reamer can then be advanced over the reamer guide and the marrow cavity can be reamed with improved accuracy. Similar approaches are feasible in other joints.
All surgical tool components may be disposable. Alternatively, some components may be re-usable. In certain embodiments, one or more single use, disposable components in a surgical kit created for a particular patient may be patient-adapted, and certain single use, disposable components are standard and not adapted for the particular patient. In certain embodiments, reusable components are included in the surgical kit. Typically, these components applied after a surgical step such as a cut as been performed can be reusable, since a reproducible anatomic interface will have been established.
Interconnecting or bridging components may be used. For example, such interconnecting or bridging components may couple the mold attached to the joint with a standard, preferably unmodified or only minimally modified cut block used during hip surgery. Interconnecting or bridging components may be made of plastic or metal. When made of metal or other hard material, they can help protect the joint from plastic debris, for example when a reamer or saw would otherwise get into contact with the mold.
The accuracy of the attachment between the component or mold and the cartilage or subchondral bone or other osseous structures is typically better than 2 mm, more preferred better than 1 mm, more preferred better than 0.7 mm, more preferred better than 0.5 mm, or even more preferred better than 0.5 mm. The accuracy of the attachment between different components or between one or more molds and one or more surgical instruments is typically better than 2 mm, more preferred better than 1 mm, more preferred better than 0.7 mm, more preferred better than 0.5 mm, or even more preferred better than 0.5 mm.
The angular error of any attachments or between any components or between components, molds, instruments or the anatomic or biomechanical axes is preferably less than 2 degrees, more preferably less than 1.5 degrees, more preferably less than 1 degree, and even more preferably less than 0.5 degrees. The total angular error is preferably less than 2 degrees, more preferably less than 1.5 degrees, more preferably less than 1 degree, and even more preferably less than 0.5 degrees.
Typically, a position will be chosen that will result in an anatomically desirable cut plane, drill hole, or general instrument orientation for subsequent placement of an articular repair system or for facilitating placement of the articular repair system. Moreover, the device can be designed so that the depth of the drill, reamer or other surgical instrument can be controlled, e.g., the drill cannot go any deeper into the tissue than defined by the device, and the size of the hole in the block can be designed to essentially match the size of the implant. Information about other joints or axis and alignment information of a joint or extremity can be included when selecting the position of these slots or holes. Alternatively, the openings in the device can be made larger than needed to accommodate these instruments. The device can also be configured to conform to the articular shape. The guides (e.g., apertures, or openings) provided can be wide enough to allow for varying the position or angle of the surgical instrument, e.g., reamers, saws, drills, curettes and other surgical instruments. An instrument guide, typically comprised of a relatively hard material, can then be applied to the device. The device helps orient the instrument guide relative to the three-dimensional anatomy of the joint.
The mold may contact the entire articular surface. In various embodiments, the mold can be in contact with only a portion of the articular surface. Thus, the mold can be in contact, without limitation, with: 100% of the articular surface; 80% of the articular surface; 50% of the articular surface; 30% of the articular surface; 30% of the articular surface; 20% of the articular surface; or 10% or less of the articular surface. An advantage of a smaller surface contact area is a reduction in size of the mold thereby enabling cost efficient manufacturing and, more important, minimally invasive surgical techniques. The size of the mold and its surface contact areas have to be sufficient, however, to ensure accurate placement so that subsequent drilling and cutting can be performed with sufficient accuracy.
In various embodiments, the maximum diameter of the mold is less than 10 cm. In other embodiments, the maximum diameter of the mold may be less than: 8 cm; 5 cm; 4 cm; 3 cm; or even less than 2 cm.
The mold may be in contact with three or more surface points rather than an entire surface. These surface points may be on the articular surface or external to the articular surface. By using contact points rather than an entire surface or portions of the surface, the size of the mold may be reduced.
Reductions in the size of the mold can be used to enable minimally invasive surgery (MIS) in the hip, the knee, the shoulder and other joints. MIS technique with small molds will help to reduce intraoperative blood loss, preserve tissue including possibly bone, enable muscle sparing techniques and reduce postoperative pain and enable faster recovery. Thus, in one embodiment of the disclosure the mold is used in conjunction with a muscle sparing technique. In another embodiment of the disclosure, the mold may be used with a bone sparing technique. In another embodiment of the disclosure, the mold is shaped to enable MIS technique with an incision size of less than 15 cm, or, more preferred, less than 13 cm, or, more preferred, less than 10 cm, or, more preferred, less than 8 cm, or, more preferred, less than 6 cm.
The mold may be placed in contact with points or surfaces outside of the articular surface. For example, the mold can rest on the acetabular rim or the lesser or greater trochanter. Optionally, the mold may only rest on points or surfaces that are not articular surface or external to the articular surface. Furthermore, the mold may rest on points or surfaces within the weight-bearing surface, or on points or surfaces external to the weight-bearing surface.
The mold may be designed to rest on bone or cartilage outside the area to be worked on, e.g. cut, drilled etc. In this manner, multiple surgical steps can be performed using the same mold. For example, in the hip, the mold may be attached external to the acetabular fossa, providing a reproducible reference that is maintained during a procedure, for example total hip arthroplasty. The mold may be affixed to the underlying bone, for example with pins or drills etc.
In additional embodiments, the mold may rest on the articular cartilage. The mold may rest on the subchondral bone or on structures external to the articular surface that are within the joint space or on structures external to the joint space. If the mold is designed to rest on the cartilage, an imaging test demonstrating the articular cartilage can be used in one embodiment. This can, for example, include ultrasound, spiral CT arthrography, MRI using, for example, cartilage displaying pulse sequences, or MRI arthrography. In another embodiment, an imaging test demonstrating the subchondral bone, e.g. CT or spiral CT, can be used and a standard cartilage thickness can be added to the scan. The standard cartilage thickness can be derived, for example, using an anatomic reference database, age, gender, and race matching, age adjustments and any method known in the art or developed in the future for deriving estimates of cartilage thickness. The standard cartilage thickness may, in some embodiments, be uniform across one or more articular surfaces or it can change across the articular surface.
The mold may be adapted to rest substantially on subchondral bone. In this case, residual cartilage can create some offset and inaccurate result with resultant inaccuracy in surgical cuts, drilling and the like. In one embodiment, the residual cartilage is removed in a first step in areas where the mold is designed to contact the bone and the subchondral bone is exposed. In a second step, the mold is then placed on the subchondral bone.
With certain diseases such as advanced osteoarthritis, significant articular deformity can result. The articular surface(s) can become flattened. There can be cyst formation or osteophyte formation. “Tram track” like structures can form on the articular surface. In one embodiment of the disclosure, osteophytes or other deformities may be removed by the computer software prior to generation of the mold. The software can automatically, semi-automatically or manually with input from the user simulate surgical removal of the osteophytes or other deformities, and predict the resulting shape of the joint and the associated surfaces. The mold can then be designed based on the predicted shape. Intraoperatively, these osteophytes or other deformities can then also optionally be removed prior to placing the mold and performing the procedure. Alternatively, the mold can be designed to avoid such deformities. For example, the mold may only be in contact with points on the articular surface or external to the articular surface that are not affected or involved by osteophytes. The mold can rest on the articular surface or external to the articular surface on three or more points or small surfaces with the body of the mold elevated or detached from the articular surface so that the accuracy of its position cannot be affected by osteophytes or other articular deformities. The mold can rest on one or more tibial spines or portions of the tibial spines. Alternatively, all or portions of the mold may be designed to rest on osteophytes or other excrescences or pathological changes.
The surgeon can, optionally, make fine adjustments between the alignment device and the instrument guide. In this manner, an optimal compromise can be found, for example, between biomechanical alignment and joint laxity or biomechanical alignment and joint function, e.g. in a hip joint anteverion, retroversion, abduction or adduction. By oversizing the openings in the alignment guide, the surgeon can utilize the instruments and insert them in the instrument guide without damaging the alignment guide. Thus, in particular if the alignment guide is made of plastic, debris will not be introduced into the joint. The position and orientation between the alignment guide and the instrument guide can be also be optimized with the use of, for example, interposed spacers, wedges, screws and other mechanical or electrical methods known in the art.
A surgeon may desire to influence joint laxity as well as joint alignment. This can be optimized for different flexion and extension, abduction, or adduction, internal and external rotation angles. For this purpose, for example, spacers can be introduced that are attached or that are in contact with one or more molds. The surgeon can intraoperatively evaluate the laxity or tightness of a joint using spacers with different thickness or one or more spacers with the same thickness. Ultimately, the surgeon will select an optimal combination of spacers for a given joint and mold. A surgical cut guide can be applied to the mold with the spacers optionally interposed between the mold and the cut guide. In this manner, the exact position of the surgical cuts can be influenced and can be adjusted to achieve an optimal result. Thus, the position of a mold can be optimized relative to the joint, bone or cartilage for soft-tissue tension, ligament balancing or for flexion, extension, rotation, abduction, adduction, anteversion, retroversion and other joint or bone positions and motion. The position of a cut block or other surgical instrument may be optimized relative to the mold for soft-tissue tension or for ligament balancing or for flexion, extension, rotation, abduction, adduction, anteversion, retroversion and other joint or bone positions and motion. Both the position of the mold and the position of other components including cut blocks and surgical instruments may be optimized for soft-tissue tension or for ligament balancing or for flexion, extension, rotation, abduction, adduction, anteversion, retroversion and other joint or bone positions and motion.
Someone skilled in the art will recognize other means for optimizing the position of the surgical cuts or other interventions. As stated above, expandable or ratchet-like devices may be utilized that can be inserted into the joint or that can be attached or that can touch the mold. Such devices can extend from a cutting block or other devices attached to the mold, optimizing the position of drill holes or cuts for different joint positions or they can be integrated inside the mold. Integration in the cutting block or other devices attached to the mold is preferable, since the expandable or ratchet-like mechanisms can be sterilized and re-used during other surgeries, for example in other patients. Optionally, the expandable or ratchet-like devices may be disposable. The expandable or ratchet like devices may extend to the joint without engaging or contacting the mold; alternatively, these devices may engage or contact the mold. Hinge-like mechanisms are applicable. Similarly, jack-like mechanisms are useful. In principal, any mechanical or electrical device useful for fine-tuning the position of the cut guide relative to the molds may be used. These embodiments are helpful for soft-tissue tension optimization and ligament balancing in different joints for different static positions and during joint motion.
The template and any related instrumentation such as spacers or ratchets can be combined with a tensiometer to provide a better intraoperative assessment of the joint. The tensiometer can be utilized to further optimize the anatomic alignment and tightness of the joint and to improve post-operative function and outcomes. Optionally, local contact pressures may be evaluated intraoperatively, for example using a sensor like the ones manufactured by Tekscan, South Boston, Mass. The contact pressures can be measured between the mold and the joint or between the mold and any attached devices such as a surgical cut block.
The template may be a mold that can be made of a plastic or polymer. The mold may be produced by rapid prototyping technology, in which successive layers of plastic are laid down, as known in the art. In other embodiments, the template or portions of the template can be made of metal. The mold can be milled or made using laser based manufacturing techniques.
The template may be casted using rapid prototyping and, for example, lost wax technique. It may also be milled. For example, a preformed mold with a generic shape can be used at the outset, which can then be milled to the patient-specific dimensions. The milling may only occur on one surface of the mold, preferably the surface that faces the articular surface. Milling and rapid prototyping techniques may be combined.
Curable materials may be used which can be poured into forms that are, for example, generated using rapid prototyping. For example, liquid metal may be used. Cured materials may optionally be milled or the surface can be further refined using other techniques.
Metal inserts may be applied to plastic components. For example, a plastic mold may have at least one guide aperture to accept a reaming device or a saw. A metal insert may be used to provide a hard wall to accept the reamer or saw. Using this or similar designs can be useful to avoid the accumulation of plastic or other debris in the joint when the saw or other surgical instruments may get in contact with the mold. Other hard materials can be used to serve as inserts. These can also include, for example, hard plastics or ceramics.
In another embodiment, the mold does not have metallic inserts to accept a reaming device or saw. The metal inserts or guides may be part of an attached device, that is typically in contact with the mold. A metallic drill guide or a metallic saw guide may thus, for example, have metallic or hard extenders that reach through the mold thereby, for example, also stabilizing any devices applied to the mold against the physical body of the mold.
The template may not only be used for assisting the surgical technique and guiding the placement and direction of surgical instruments. In addition, the templates can be utilized for guiding the placement of the implant or implant components. For example, in the hip joint, tilting of the acetabular component is a frequent problem with total hip arthroplasty. A template can be applied to the acetabular wall with an opening in the center large enough to accommodate the acetabular component that the surgeon intends to place. The template can have receptacles or notches that match the shape of small extensions that can be part of the implant or that can be applied to the implant. For example, the implant can have small members or extensions applied to the twelve o'clock and six o'clock positions. By aligning these members with notches or receptacles in the mold, the surgeon can ensure that the implant is inserted without tilting or rotation. These notches or receptacles can also be helpful to hold the implant in place while bone cement is hardening in cemented designs.
One or more templates can be used during the surgery. For example, in the hip, a template can be initially applied to the proximal femur that closely approximates the 3D anatomy prior to the resection of the femoral head. The template can include an opening to accommodate a saw. The opening is positioned to achieve an optimally placed surgical cut for subsequent reaming and placement of the prosthesis. A second template can then be applied to the proximal femur after the surgical cut has been made. The second template can be useful for guiding the direction of a reamer prior to placement of the prosthesis. As can be seen in this, as well as in other examples, templates can be made for joints prior to any surgical intervention. However, it is also possible to make templates that are designed to fit to a bone or portions of a joint after the surgeon has already performed selected surgical procedures, such as cutting, reaming, drilling, etc. The template can account for the shape of the bone or the joint resulting from these procedures. Exemplary surgical tools are disclosed in U.S. Pat. Nos. 8,066,708 and 8,083,745.
In certain embodiments, the surgical assistance device comprises an array of adjustable, closely spaced pins (e.g., plurality of individually moveable mechanical elements). One or more electronic images or intraoperative measurements can be obtained providing object coordinates that define the articular or bone surface and shape. These objects' coordinates can be entered or transferred into the device, for example manually or electronically, and the information can be used to create a surface and shape that will match all or portions of the articular or bone surface and shape by moving one or more of the elements. The device can include slots and holes to accommodate surgical instruments such as drills, curettes, k-wires, screws and saws. The position of these slots and holes may be adjusted by moving one or more of the mechanical elements. Typically, a position will be chosen that will result in an anatomically desirable cut plane, reaming direction, or drill hole or instrument orientation for subsequent placement of an articular repair system or for facilitating the placement of an articular repair system.
Information about other joints or axis and alignment information of a joint or extremity can be included when selecting the position of the, without limitation, cut planes, apertures, slots or holes on the template, in accordance with an embodiment of the disclosure. The biomechanical or anatomic axes may be derived as described above.
In another embodiment, the biomechanical axis may be established using non-image based approaches including traditional surgical instruments and measurement tools such as intramedullary rods, alignment guides and also surgical navigation. For example, in a hip joint, optical or radiofrequency markers can be attached to the patient. The lower limb may then be rotated around the hip joint and the position of the markers can be recorded for different limb positions. The center of the rotation will determine the center of the femoral head. Similar reference points may be determined in the ankle joint etc. The position of the templates or, more typically, the position of surgical instruments relative to the templates may then be optimized for a given biomechanical load pattern, for example in abduction or adduction. Thus, by performing these measurements pre- or intraoperatively, the position of the surgical instruments may be optimized relative to the molds and the cuts can be placed to correct underlying axis errors such as varus or valgus malalignment or ante- or retroversion.
Upon imaging, a physical template of a hip joint is generated, in accordance with an embodiment herein. The template can be used to perform image guided surgical procedures such as partial or complete joint replacement, articular resurfacing, or ligament repair. The template may include reference points or opening or apertures for surgical instruments such as drills, saws, burrs and the like.
In order to derive the preferred orientation of drill holes, cut planes, saw planes, reaming depth and diameter, depth and diameter of broaching and the like, openings or receptacles in said template or attachments will be adjusted to account for at least one axis. The axis can be anatomic or biomechanical, for example, for a knee joint, a hip joint, an ankle joint, a shoulder joint or an elbow joint.
In one embodiment, only a single axis is used for placing and optimizing such drill holes, saw planes, cut planes, and or other surgical interventions. This axis may be, for example, an anatomical or biomechanical axis. In a specific embodiment, a combination of axis or planes can be used for optimizing the placement of the drill holes, saw planes, cut planes or other surgical interventions. For example, two axes (e.g., one anatomical and one biomechanical) can be factored into the position, shape or orientation of the 3D guided template and related attachments or linkages. For example, two axes, (e.g., one anatomical and biomechanical) and one plane (e.g., the top plane defined by the tibial plateau), can be used. Alternatively, two or more planes can be used (e.g., a coronal and a sagittal plane), as defined by the image or by the patients anatomy.
Angle and distance measurements and surface topography measurements may be performed in these one or more, preferably two or more, preferably three or more multiple planes, as necessary. These angle measurements can, for example, yield information on varus or valgus deformity, flexion or extension deficit, hyper or hypo-flexion or hyper- or hypo-extension, abduction, adduction, internal or external rotation deficit, or hyper-or hypo-abduction, hyper- or hypo-adduction, hyper- or hypo-internal or external rotation.
Single or multi-axis line or plane measurements can then be utilized to determine preferred angles of correction, e.g., by adjusting surgical cut or saw planes or other surgical interventions. Typically, two axis corrections will be preferred over a single axis correction, a two plane correction will be preferred over a single plane correction and so forth.
In accordance with another embodiment of the disclosure, more than one drilling, cut, boring or reaming or other surgical intervention is performed for a particular treatment such as the placement of a joint resurfacing or replacing implant, or components thereof These two or more surgical interventions (e.g., drilling, cutting, reaming, sawing) are made in relationship to a biomechanical axis, or an anatomical axis or an implant axis. The 3D guidance template or attachments or linkages thereto include two or more openings, guides, apertures or reference planes to make at least two or more drillings, reamings, borings, sawings or cuts in relationship to a biomechanical axis, an anatomical axis, an implant axis or other axis derived therefrom or related thereto.
While in simple embodiments it is possible that only a single cut or drilling will be made in relationship to a biomechanical axis, an anatomical axis, an implant axis or an axis related thereto, in most meaningful implementations, two or more drillings, borings, reamings, cutting or sawings will be performed or combinations thereof in relationship to a biomechanical, anatomical or implant axis.
For example, an initial cut may be placed in relationship to a biomechanical axis of particular joint. A subsequent drilling, cut or other intervention can be performed in relation to an anatomical axis. Both can be designed to achieve a correction in a biomechanical axis or anatomical axis. In another example, an initial cut can be performed in relationship to a biomechanical axis, while a subsequent cut is performed in relationship to an implant axis or an implant plane. Any combination in surgical interventions and in relating them to any combination of biomechanical, anatomical, implant axis or planes related thereto is possible. In many embodiments of the disclosure, it is desirable that a single cut or drilling be made in relationship to a biomechanical or anatomical axis. Subsequent cuts or drillings or other surgical interventions can then be made in reference to said first intervention. These subsequent interventions can be performed directly off the same 3D guidance template or they can be performed by attaching surgical instruments or linkages or reference frames or secondary or other templates to the first template or the cut plane or hole and the like created with the first template.
In another embodiment, a frame can be applied to the bone or the cartilage in areas other than the diseased bone or cartilage. The frame can include holders and guides for surgical instruments. The frame can be attached to one or preferably more previously defined anatomic reference points. Alternatively, the position of the frame can be cross-registered relative to one, or more, anatomic landmarks, using an imaging test or intraoperative measurement, for example one or more fluoroscopic images acquired intraoperatively. One or more electronic images or intraoperative measurements including using mechanical devices can be obtained providing object coordinates that define the articular or bone surface and shape. These objects' coordinates can be entered or transferred into the device, for example manually or electronically, and the information can be used to move one or more of the holders or guides for surgical instruments. Typically, a position will be chosen that will result in a surgically or anatomically desirable cut plane or drill hole orientation for subsequent placement of an articular repair system. Information about other joints or axis and alignment information of a joint or extremity can be included when selecting the position of these slots or holes.
Furthermore, re-useable tools (e.g., molds) can be also be created and employed. Non-limiting examples of re-useable materials include putties and other deformable materials (e.g., an array of adjustable closely spaced pins that can be configured to match the topography of a joint surface). In other embodiments, the molds may be made using balloons. The balloons can optionally be filled with a hardening material. A surface can be created or can be incorporated in the balloon that allows for placement of a surgical cut guide, reaming guide, drill guide or placement of other surgical tools. The balloon or other deformable material can be shaped intraoperatively to conform to at least one articular surface. Other surfaces can be shaped in order to be parallel or perpendicular to anatomic or biomechanical axes. The anatomic or biomechanical axes can be found using an intraoperative imaging test or surgical tools commonly used for this purpose in hip, knee or other arthroplasties.
In various embodiments, the template may include a reference element, such as a pin, that upon positioning of the template on the articular surface, establishes a reference plane relative to a biomechanical axis or an anatomical axis or plane of a limb. In other embodiments, the reference element may establish an axis that subsequently be used a surgical tool to correct an axis deformity.
In these embodiments, the template can be created directly from the joint during surgery or, alternatively, created from an image of the joint, for example, using one or more computer programs to determine object coordinates defining the surface contour of the joint and transferring (e.g., dialing-in) these co-ordinates to the tool. Subsequently, the tool can be aligned accurately over the joint and, accordingly, the surgical instrument guide or the implant will be more accurately placed in or over the articular surface.
In both single-use and re-useable embodiments, the tool can be designed so that the instrument controls the depth or direction of the drill, i.e., the drill cannot go any deeper into the tissue than the instrument allows, and the size of the hole or aperture in the instrument can be designed to essentially match the size of the implant.
These surgical tools (devices) can also be used to remove an area of diseased cartilage and underlying bone or an area slightly larger than the diseased cartilage and underlying bone. In addition, the device can be used on a “donor,” e.g., a cadaveric specimen, to obtain implantable repair material. The device is typically positioned in the same general anatomic area in which the tissue was removed in the recipient. The shape of the device is then used to identify a donor site providing a seamless or near seamless match between the donor tissue sample and the recipient site. This can be achieved by identifying the position of the device in which the articular surface in the donor, e.g. a cadaveric specimen, has a seamless or near seamless contact with the inner surface when applied to the cartilage.
The device can be molded, rapid prototyped, machine or formed based on the size of the area of diseased cartilage and based on the curvature of the cartilage or the underlying subchondral bone or a combination of both or using adjacent structures inside or external to the joint space. The device can take into consideration surgical removal of, for example, the meniscus, in arriving at a joint surface configuration.
In certain embodiments, a surgical tool includes a reamer for preparing an implantation site in a patient's acetabulum. The reamer can be standard and not adapted to any individual patient. Alternatively, the reamer can be adapted to particular patient, e.g., configured to create a site on the patient's acetabulum to receive a patient-adapted acetabular implant (e.g., an acetabular cup with an insert, the cup having a patient-adapted rim). A patient-adapted, single use, disposable reamer can be manufactured according to the manufacturing methods described herein.
In certain embodiments, a surgical tool includes a broach for preparing an implantation site in a patient's femur. The broach can be standard and not adapted to any individual patient. Alternatively, the broach can be adapted to particular patient, e.g., configured to create a site on the patient's acetabulum to receive a patient-adapted femoral implant (e.g., a femoral stem with an integrated femoral head and neck or a modular femoral head and neck components). A patient-adapted, single use, disposable broach can be manufactured according to the manufacturing methods described herein.
The implant site can be prepared with use of a robotic device. The robotic device can use information from an electronic image for preparing the recipient site.
Identification and preparation of the implant site and insertion of the implant can be supported by a surgical navigation system. In such a system, the position or orientation of a surgical instrument with respect to the patient's anatomy can be tracked in real-time in one or more 2D or 3D images. These 2D or 3D images can be calculated from images that were acquired preoperatively, such as MR or CT images. Non-image based surgical navigation systems that find axes or anatomical structures, for example with use of joint motion, can also be used. The position and orientation of the surgical instrument as well as the mold including alignment guides, surgical instrument guides, reaming guides, drill guides, saw guides, etc. can be determined from markers attached to these devices. These markers can be located by a detector using, for example, optical, acoustical or electromagnetic signals.
Identification and preparation of the implant site and insertion of the implant can also be supported with use of a C-arm system. The C-arm system can afford imaging of the joint in one or, preferably, multiple planes. The multiplanar imaging capability can aid in defining the shape of an articular surface. This information can be used to selected an implant with a good fit to the articular surface. Currently available C-arm systems also afford cross-sectional imaging capability, for example for identification and preparation of the implant site and insertion of the implant. C-arm imaging can be combined with administration of radiographic contrast.
In various embodiments, the surgical devices described herein can include one or more materials that harden to form a mold of the articular surface. In specific embodiments, the materials used are biocompatible, such as, without limitation, acylonitrile butadiene styrene, polyphenylsulfone and polycarbonate. As used herein “biocompatible” shall mean any material that is not toxic to the body (e.g., produces a negative reaction under ISO 10993 standards, incorporated herein by reference). In various embodiments, these biocompatible materials may be compatible with rapid prototyping techniques.
In further embodiments, the mold material is capable of heat sterilization without deformation. An exemplary mold material is polyphenylsulfone, which does not deform up to a temperature of 207° C. Alternatively, the mold may be capable of sterilization using gases, e.g. ethyleneoxide. The mold may be capable of sterilization using radiation, e.g. □-radiation. The mold may be capable of sterilization using hydrogen peroxide or other chemical means. The mold may be capable of sterilization using any one or more methods of sterilization known in the art or developed in the future.
A wide-variety of materials capable of hardening in situ include polymers that can be triggered to undergo a phase change, for example polymers that are liquid or semi-liquid and harden to solids or gels upon exposure to air, application of ultraviolet light, visible light, exposure to blood, water or other ionic changes. (See, also, U.S. Pat. No. 6,443,988 to Felt et al. issued Sep. 3, 2002 and documents cited therein). Non-limiting examples of suitable curable and hardening materials include polyurethane materials (e.g., U.S. Pat. No. 6,443,988 to Felt et al., U.S. Pat. No. 5,288,797 to Khalil issued Feb. 22, 1994, U.S. Pat. No. 4,098,626 to Graham et al. issued Jul. 4, 1978 and U.S. Pat. No. 4,594,380 to Chapin et al. issued Jun. 10, 1986; and Lu et al. (2000) BioMaterials 21(15):1595-1605 describing porous poly(L-lactide acid foams); hydrophilic polymers as disclosed, for example, in U.S. Pat. No. 5,162,430; hydrogel materials such as those described in Wake et al. (1995) Cell Transplantation 4(3):275-279, Wiese et al. (2001) J. Biomedical Materials Research 54(2):179-188 and Marler et al. (2000) Plastic Reconstruct. Surgery 105(6):2049-2058; hyaluronic acid materials (e.g., Duranti et al. (1998) Dermatologic Surgery 24(12):1317-1325); expanding beads such as chitin beads (e.g., Yusof et al. (2001) J. Biomedical Materials Research 54(1):59-68); crystal free metals such as Liquidmetals™, or materials used in dental applications (See, e.g., Brauer and Antonucci, “Dental Applications” pp. 257-258 in “Concise Encyclopedia of Polymer Science and Engineering” and U.S. Pat. No. 4,368,040 to Weissman issued Jan. 11, 1983). Any biocompatible material that is sufficiently flowable to permit it to be delivered to the joint and there undergo complete cure in situ under physiologically acceptable conditions can be used. The material can also be biodegradable.
The curable materials can be used in conjunction with a surgical tool as described herein. For example, the surgical tool can be a template that includes one or more apertures therein adapted to receive injections and the curable materials can be injected through the apertures. Prior to solidifying in situ the materials will conform to the articular surface (subchondral bone or articular cartilage) facing the surgical tool and, accordingly, will form a mirror image impression of the surface upon hardening, thereby recreating a normal or near normal articular surface.
In addition, curable materials or surgical tools can also be used in conjunction with any of the imaging tests and analysis described herein, for example by molding these materials or surgical tools based on an image of a joint. For example, rapid prototyping may be used to perform automated construction of the template. The rapid prototyping may include the use of, without limitation, 3D printers, stereolithography machines or selective laser sintering systems. Rapid prototyping is a typically based on computer-aided manufacturing (CAM). Although rapid prototyping traditionally has been used to produce prototypes, they are now increasingly being employed to produce tools or even to manufacture production quality parts. In an exemplary rapid prototyping method, a machine reads in data from a CAD drawing, and lays down successive millimeter-thick layers of plastic or other engineering material, and in this way the template can be built from a long series of cross sections. These layers are glued together or fused (often using a laser) to create the cross section described in the CAD drawing.
For resurfacing of the femoral head of a hip joint, a milling apparatus can include patient-specific dimensions. For example, the mill can be printed using EBM or SLM techniques, with a cylindrical opening. The cylindrical opening can have, optionally, a patient-specific diameter optimized for the patient's femoral head shape or geometry. It can include on its inner surface teeth or rasp like structures that were generated during the 3D printing process.
A flow chart illustrating the steps involved in designing a mold for use in preparing a joint surface is shown in
The following examples illustrate various embodiments of designing or selecting a patient-adapted hip replacement or resurfacing system. Any of the embodiments herein are applicable to cemented and non-cemented hip replacement or resurfacing systems. While certain embodiments are described with a number of sequential steps, the same or similar steps can vary in sequence to achieve the same or substantially the same outcome. The steps between different illustrative embodiments are also exchangeable, e.g., to meet the design or selection criteria of a particular patient-adapted hip replacement system. Further, the designing or selecting process can be iterative, that is, one or more steps described herein can be repeated.
As described herein, various designing, determining and selecting steps are carried out with patient-specific image data and optionally additional patient information (e.g., the patient's body habitus). The patient's body habitus includes one or more physical and constitutional characteristics of an individual, such as for example, the patient's weight, height, bone density, and soft tissue thickness).
An exemplary process, shown in
The image data is collected from images through acetabulum and proximal femur of the patient's hip joint(s). Optionally, images through the patient's corresponding knee joint(s) are also obtained. Further, images through the patient's corresponding ankle joint(s) may also be obtained. Image data of the knee/ankle joints may help optimize the hip replacement system, e.g., by optimizing leg length for the patient.
Step 2800 may also include planning the surgical procedure with the image data and optionally other data, such as for example, additional patient information (e.g., the patient's body habitus). Optionally, the surgical planning includes step 2801 of determining one or more axes of the hip joint to be replaced, such as for example, an anatomical axis of the femur of the hip joint, a biomechanical axis of the femur of the hip joint, an anatomical axis of the acetabulum of the hip joint, a biomechanical axis of the acetabulum of the hip joint.
Optionally, the surgical planning includes step 2802 of determining or selecting a desired acetabular cup position or orientation, such as for example, anteversion. Optionally, the surgical planning includes designing or selecting a desired acetabular cup size, shape or geometry, e.g., the rim of the acetabular cup matching the patient's acetabulum rim (preferably after virtually reamed to a desired depth).
Optionally, the surgical planning includes step 2803 of determining or selecting a desired femoral implant or implant component position or orientation, such as for example, anteversion, the femoral shaft angle the femoral neck angle. The desired femoral implant or implant component position/orientation can be determined in connection with the acetabular cup position/orientation, as described herein.
Optionally, the surgical planning includes step 2804 of determining a desired reaming depth for the acetabulum. The surgical planning may further include virtual reaming of the acetabulum and optionally after virtual removal of one or more deformities, e.g., osteophytes. Alternatively, instead of virtual removal of the one or more deformities, the implant components can be designed or selected by omitting the one or more deformities in the image data.
Optionally, the surgical planning includes step 2805 of calculating the offset of the acetabular bearing surface and resultant radii by estimating the ream depth for the acetabulum and taking into account the added acetabular implant or implant component thickness.
Optionally, the surgical planning includes step 2806, step 2809 or step 28012, including determining or selecting a femoral head size (e.g. outer diameter) based on the offset of acetabular bearing surface and resultant radii. For example, a larger offset of the acetabular bearing surface, as compared to a smaller offset, requires a smaller femoral head.
Optionally, the surgical planning includes steps 2807, step 2810 or step 2813, including determining or selecting a femoral neck length or angle or both. Such determination or selection references the patient's anatomy, e.g., based on the patient's image data, and optionally other patient information. Optionally, such determination or selection is based on the offset of the acetabular bearing surface.
Optionally, the surgical planning includes determining or selecting one or more parameters, e.g., step 2808, step 2811 or step 2814, including determining or selecting a femoral shaft length, a femoral shaft width, the angle between the femoral neck and shaft. Such determination or selection references the patient's anatomy, e.g., based on the patient's image data, and optionally other patient information.
Optionally, femoral neck length or angle or combinations thereof can be selected, designed, adapted/optimized (step 2807, 2810 or 2813) based on the offset of the acetabular bearing surface calculated according to step 2805.
Optionally, femoral shaft including its length, width or neck shaft angle or combinations thereof can be selected, designed, or adapted/optimized (step 2808, 2811 or 2814) based on patient-specific parameters (e.g., obtained by the methods described herein including, e.g., step 2800 and optionally step 2801).
Optionally, femoral head size can be selected, designed or adapted/optimized with patient-specific parameters (step 2806, 2809 or 2812) and based on the offset of the acetabular bearing surface and the resultant radii calculated according to step 2805.
As described above, the hip replacement system is designed or adapted by determining a desired reaming depth of the acetabulum, followed by determining the offset of acetabular bearing surface and subsequently, determining or selecting a femoral head size (e.g. outer diameter), femoral neck (e.g., angle), or femoral shaft (e.g., length or angle) based on the offset of acetabular bearing surface and resultant radii. Alternatively, the hip replacement system can be designed or selected by first determining or selecting one or more of a desired femoral neck and shaft (e.g., size and angle) and femoral head size (e.g., outer diameter), followed by determining or selecting the offset of acetabular bearing surface and subsequently, determining the desired reaming depth of the acetabulum. That alternative process is illustrated in
An exemplary process, shown in
The image data is collected from images through acetabulum and proximal femur of the patient's hip joint(s). Optionally, images through the patient's corresponding knee joint(s) are also obtained. Further, images through the patient's corresponding ankle joint(s) may also be obtained. Image data of the knee/ankle joints may help optimize the hip implant system, e.g., by optimizing leg length for the patient.
The surgical procedure is then planned with the image data and optionally additional patient information or patient-specific data/parameters (e.g., the patient's body habitus) (step 3000). The patient's body habitus includes one or more physical and constitutional characteristics of an individual, such as for example, the patient's weight, height, bone density, and soft tissue characteristics such as thickness).
Optionally, the surgical planning includes step 3001 of determining one or more axes of the hip joint to be resurfaced or replaced, such as for example, an anatomical axis of the femur of the hip joint, a biomechanical axis of the femur of the hip joint, an anatomical axis of the acetabulum of the hip joint, a biomechanical axis of the acetabulum of the hip joint.
Optionally, the surgical planning includes step 3002 of determining or selecting a desired acetabular cup position or orientation, such as for example, anteversion. Optionally, the surgical planning includes designing or selecting a desired acetabular cup size, shape or geometry, e.g., the rim of the acetabular cup matching the patient's acetabulum rim (preferably after virtually reamed to a desired depth). Such determination or selection references the patient's anatomy, e.g., based on the patient's image data, and optionally other patient information.
Optionally, the surgical planning includes step 3003 of determining or selecting a desired femoral implant or implant component position or orientation, such as for example, anteversion, the femoral shaft angle the femoral neck angle. The desired femoral implant or implant component position/orientation can be determined in connection with the acetabular cup position/orientation, as described herein.
Optionally, the surgical planning includes step 3004 of determining a desired reaming depth for the acetabulum. The surgical planning may further include virtual reaming of the acetabulum and optionally after virtual removal of one or more deformities, e.g., osteophytes. Alternatively, instead of virtual removal of the one or more deformities, the implant components can be designed or selected by omitting the one or more deformities in the image data.
Optionally, the surgical planning includes step 3005 of calculating the offset of the acetabular bearing surface and resultant radii by estimating the ream depth for the acetabulum and taking into account the added acetabular implant or implant component thickness.
Optionally, the surgical planning includes step 3006, step 3011 or step 3017, including determining or selecting a femoral head size (e.g. outer diameter) based on the offset of acetabular bearing surface and resultant radii. For example, a larger offset of the acetabular bearing surface, as compared to a smaller offset, requires a smaller resurfacing femoral head.
The surgical planning may also include step 3007 or 3012 or 3018 of determining or selecting a necessary material thickness of the resurfacing femoral head component. Such material thickness can be predetermined without reference to the patient's hip joint anatomy. Alternatively, such material thickness can be determined or selected based on the patient's hip joint anatomy.
The surgical planning also includes step 3009, step 3015 or step 3021, including determining or selecting a desired central peg length of the femoral implant or implant component. The central peg length can be designed for the individual patient or selected from a library of premade femoral head components with varying central peg lengths (e.g., step 3010, 3016 or 3022). The central peg length of the selected, premade femoral head component can be further adapted (e.g., by adding or removing materials with CNC machining or laser melting) to the individual patient.
The surgical planning further includes step 3008, steps 3013 and 3014, or steps 3019 and 3020, including designing or selecting one or more surgical tool(s) for preparing the femoral head of the hip joint to be resurfaced or replaced in order to receive the resurfacing femoral head component. For example, one or more milling or broaching tool(s) can be designed or selected, and as described above, a larger offset of the acetabular bearing surface requires more milling or broaching (more bone removal) of the femoral head in order to receive a smaller resurfacing femoral head component. The resurfacing femoral head component can be designed for the individual patient or selected from a library of premade femoral head components. The selected, premade femoral head component can be further adapted (e.g., by adding or removing materials with CNC machining or laser melting) to the individual patient.
As described herein, the size of a femoral head can be designed or adapted based on the offset of the acetabular bearing surface and the resultant radii. The necessary material thickness of the resurfacing femoral head component can be adapted based on the patient's anatomy (e.g., using patient's image data) or additional patient information. Alternatively, the necessary material thickness of the resurfacing femoral head component is predetermined. Optionally, various predetermined material thicknesses are available, and a predetermined thickness is selected based on the patient's anatomy or additional patient information.
As described herein, the necessary amount of bone removal, e.g., milling or broaching of the femoral head or reaming of the acetabulum can be patient-adapted, e.g., determined or designed with reference to the patient's anatomy. The surgical tools for milling, broaching or reaming can be customized and optimized for the individual patient.
As described above, the hip implant system is designed or selected by determining a desired reaming depth of the acetabulum, followed by determining the offset of acetabular bearing surface and subsequently, determining or selecting a femoral head size (e.g. outer diameter) based on the offset of acetabular bearing surface and resultant radii. Alternatively, the hip implant system can be designed or selected by determining a desired femoral head size (e.g., outer diameter), followed by determining or selecting the offset of acetabular bearing surface and subsequently, determining the desired reaming depth of the acetabulum.
Various hip implant and implant component configurations are illustrated in the drawings.
For example, the implant illustrated in
An alternative femoral implant with a long stem is shown in
To illustrate patient-to-patient variations, a resected hip femur of a smaller patient (e.g., shorter, thinner, etc.) is shown in
Similarly a femoral implant as implanted on a resected hip femur of a smaller patient is shown in
A step ladder design can be used on the medial, lateral, anterior or posterior surface of the femoral implant component or combinations thereof. A step ladder design can be advantageous to convert shear forces to compressive forces.
The step ladder design can be used along portions or the entire length of the implant. In one embodiment, the step ladder design is used in the area of the femoral neck and portions of the entry into the femoral shaft.
The step ladder design and shape can be generic, pre-selected. It can be selected on the basis of an imaging test by analyzing the curvature of the endosteal or cortical bone.
The step ladder design can also be patient specific. For example, the curvature of the endosteal or cortical bone, can be measured in an individual patient and a step ladder design can be superimposed. The length (L) and height (H) of each step can be patient-specific. Alternatively, some steps can be patient-specific while others can be generic.
A partially or completely patient-specific step ladder design can be manufactured using any technique known in the art, e.g. CNC machining or casting, e.g. near net casting. In one embodiment of the invention, the patient-specific step ladder design is part of a CAD file that is transferred into an additive manufacturing process such as electron beam melting or selective laser melting. The additive manufacturing process will then generate the patient-specific step ladder design.
In another embodiment, a patient-specific step ladder design is part of a CAD file that is transferred to an additive 3D printer that is printing with wax or nylon. A near net shape of the step ladder and implant is created which is then used during casting using a lost wax or similar technique.
In most hip replacements, the femoral neck is cut at an angle that is near perpendicular to the femoral neck axis. In one embodiment of the invention, the biomechanical axis is determined based on scan or other data. The biomechanical axis information is then entered into a surgical plan that is designed to cut the femoral neck perpendicular or near perpendicular to the biomechanical axis.
By cutting the femoral neck perpendicular or near perpendicular to the biomechanical axis, the contact area and support area for the collar portion of a short stem or long stem femoral component can be increased, thereby increasing bone support. In addition, loading can be favorably converted from shear type stresses to more compressive loading and stresses. If the cut is perpendicular to the biomechanical axis, compressive stress will predominate.
If intervening structures such as a high greater trochanter or a low femoral head (in case of a short neck) would interfere with a cut that is perpendicular to the mechanical axis, the cut can be optionally adjusted so that it remains near the biomechanical axis, but stays clear of these or other interfering structures.
As shown in
As shown in
In certain embodiments, an acetabular cup includes a non-metal, e.g., cross-linked and oxidation resistant UHMWPE, bearing surface. The acetabular cup further includes a metal backing component for a non-metal component presenting the non-metal bearing surface. The bone-facing surface of the metal backing component negatively matches the shape of the reamed acetabulum. In an illustrative embodiment, the acetabulum is subjected to 1 mm reaming, the metal backing component is 2 mm thick, and the non-metal component is 4 mm. Accordingly, the acetabular cup requires 5 mm additional joint space. When the corresponding femoral head component, e.g., made of metal, includes another 3 mm material thickness, the femur must be resected to provide enough joint surface to accommodate the composite requirements of the acetabular cup and femoral head component (e.g., in the illustrative example, 8 mm of bone removal would be required). Material thicknesses of each component or composite thicknesses can be used to determine bone removal. Alternatively, a desired level of bone removal is determined first, with or without reference to the patient, and material thickness of each component can then be derived. Material thickness can be customized to each individual patient, e.g., based on patient-specific Finite Element Analysis (FEA). Material selection can also be customized to each individual patient, e.g., based on patient-specific bone structural or density parameters.
The following exemplary parameters of illustrative hip implant system can be optimized for or adapted to each individual patient: shape or geometry of the acetabular cup component (e.g., radius), driven by the patient's acetabulum; shape or geometry of the femoral head component (e.g., cylinder width and height), driven by the femoral resection level, patient's bone characteristics (e.g., trabecular microarchitecture, bone density), etc.; size or shape of the central peg (e.g., width, length or thickness) of the femoral head component.
As shown in
Examples of various aspects of the femoral sleeve can be designed or selected based on the individual patient's anatomy or additional patient information include, but are not limited to, its material thickness, its widths or radii along the femoral neck, and its length. The femoral sleeve includes an outer surface for engaging the prepared femoral bone surface; the outer surface has a curvature that matches the curvature of the patient's prepared femoral bone surface and is configured to convert shear force to compression when the femoral head cylinder component engages the femoral sleeve. Material thickness can be optimized with patient-specific FEA.
As shown in the drawings herein, e.g.,
The exemplary femoral implant shown in
The patient-specific design, selection or adaptation/optimization of the femoral collar can be based on one or more of the following parameters: the shape of the cut femur (e.g., matching the shape of the cut cortical bone), the shape of the greater trochanter, the shape of the lesser trochanter, endosteal bone of the femur, trabecular bone of the femur (including distance of the collar position adjacent to the trabecular bone), trabecular bone microarchitecture and macroarchitecture, and other bone quality parameters such as bone mineral density.
The illustrative resurfacing system optionally includes one or more patient-adapted surgical tools having one or more guides. One such surgical tool may include guide to accommodate a k-wire configured to extend into the femoral canal to achieve the desired alignment of the femoral head component.
Referring to
As illustrated in
As shown in
As shown in
As shown in
The following example illustrates the calculation of various implant parameters:
O=AML+AI−AR−AC
In the above example: O=2 mm+4 mm−2 mm−2 mm=2 mm, and therefore, the acetabular bearing surface will be moved distally by 2 mm.
The distal displacement of the acetabular bearing surface means that the resultant diameter and radius of the femur facing bearing surface of the acetabular insert will be smaller than the diameter and radius of the native bearing surface of the patient. Typically, the diameter will be smaller by 2×O and the radius will be smaller by 1×O and plus additional reductions/offsets needed to allow sufficient play between the femoral and the acetabular implant bearing surface.
In the above example, the diameter of the femur facing bearing surface of the acetabular insert (DAI) will be 5.8 cm−0.4 cm=5.4 cm.
The implication is that the matching bearing surface of the femoral head component will need to be slightly smaller than 5.4 cm in this patient. A matching component can be selected, adapted to this size or designed for these dimensions.
Amount of bone to be removed (BR) near fovea capitis region (and optionally other femoral head regions):
BR=(FHD−DAI)+P+MMT=(5.7 cm−5.4 cm)+0.1 cm+0.3 cm=6.5 mm
If a cylindrical mill is used, the amount of bone to be removed medially and laterally can, for example, be determined by the femoral neck width at the head neck junction (FNW_J).
In the above example, FNW_J of this particular patient is: 4.4 cm;
Femoral head component diameter (FHCD): FHCD=DAI−P=5.3 cm;
Diameter of the mill for amount of bone removed medially and laterally from femoral head to match to FNW_J: 4.4 cm;
Amount of bone removed medially from femoral head: (5.7 cm−4.4 cm)/2=0.65 cm; and
Amount of bone removed laterally from femoral head: (5.7 cm−4.4 cm)/2=0.65 cm.
These calculations and optimizations for implant selection, adaptation or design as described above can be initiated from the femoral side and then carried through on the acetabular side. Thus, the amount or depth of acetabular remaining can be determined based on the desired amount of femoral bone removal or the desired femoral implant component thickness or combinations thereof. If the resultant acetabular reaming would be excessive, both the amount of femoral bone removal (including medial and lateral bone removal with, for example, a mill and removal of bone near the fovea capitis region) and the depth of acetabular reaming can be optimized against each other for a given material thickness of the different components. The material thickness can include a desirable threshold value including a minimum material thickness, e.g. of polyethylene as a means of allowing for or compensation for future wear or of metal as a means of avoiding component fractures. The material thickness of each component can be adjusted based on patient-specific information or parameters including weight, height, sex, age, femoral head size, acetabular size or dimensions etc. In addition, the component thickness can be adjusted using kinematic modeling and finite element modeling, both of which can include patient-specific parameters (e.g. the preceding parameters as well as bone shape, dimensions, bone density, trabecular structure etc.).
While this example is directed to a metal-on-polyethylene system, the same design or selection rationale can be applied to design or select a metal-on-ceramic, all-polyethylene or all-ceramic system. Various material combinations are possible. Some of the following exemplary combinations can be used to avoid metal on metal bearings.
It will be apparent to those skilled in the art that various modifications and variations can be made to the disclosed devices and methods. Other embodiments will be apparent to those skilled in the art from consideration of the specification and practice of the disclosed embodiments. It is intended that the specification and examples be considered as exemplary only, with a true scope being indicated by the following claims and their equivalents.
This application claims the benefit of U.S. Provisional Patent Application Ser. No. 61/596,197, entitled “Methods and Devices Related to Patient-Adapted Hip Joint Implants,” filed Feb. 7, 2012, from which priority is claimed under 35 U.S.C. 119, and the disclosure of which is hereby incorporated herein by reference in its entirety.
| Number | Date | Country | |
|---|---|---|---|
| 61596197 | Feb 2012 | US |
