US20100070045A1 - System and Method for Joint Resurface Repair - Google Patents
System and Method for Joint Resurface Repair Download PDFInfo
- Publication number
- US20100070045A1 US20100070045A1 US12/620,309 US62030909A US2010070045A1 US 20100070045 A1 US20100070045 A1 US 20100070045A1 US 62030909 A US62030909 A US 62030909A US 2010070045 A1 US2010070045 A1 US 2010070045A1
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- implant
- exemplary
- bone
- articular
- view
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- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0058—Additional features; Implant or prostheses properties not otherwise provided for
- A61F2250/0092—Means for cleaning prostheses
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00017—Iron- or Fe-based alloys, e.g. stainless steel
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00023—Titanium or titanium-based alloys, e.g. Ti-Ni alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00029—Cobalt-based alloys, e.g. Co-Cr alloys or Vitallium
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00035—Other metals or alloys
- A61F2310/00059—Chromium or Cr-based alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00035—Other metals or alloys
- A61F2310/00089—Zirconium or Zr-based alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00035—Other metals or alloys
- A61F2310/00095—Niobium or Nb-based alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00179—Ceramics or ceramic-like structures
- A61F2310/00185—Ceramics or ceramic-like structures based on metal oxides
- A61F2310/00203—Ceramics or ceramic-like structures based on metal oxides containing alumina or aluminium oxide
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00179—Ceramics or ceramic-like structures
- A61F2310/00185—Ceramics or ceramic-like structures based on metal oxides
- A61F2310/00239—Ceramics or ceramic-like structures based on metal oxides containing zirconia or zirconium oxide ZrO2
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00389—The prosthesis being coated or covered with a particular material
- A61F2310/00592—Coating or prosthesis-covering structure made of ceramics or of ceramic-like compounds
- A61F2310/00796—Coating or prosthesis-covering structure made of a phosphorus-containing compound, e.g. hydroxy(l)apatite
Definitions
- This invention relates to devices and methods for the repair of defects that occur in articular cartilage on the surface of bones, particularly the knee.
- hyaline cartilage found at the ends of articulating bone in the body, is typically composed of hyaline cartilage, which has many unique properties that allow it to function effectively as a smooth and lubricious load-bearing surface.
- hyaline cartilage cells are not typically replaced by new hyaline cartilage cells.
- healing is dependent upon the occurrence of bleeding from the underlying bone and formation of scar or reparative cartilage called fibrocartilage. While similar, fibrocartilage does not possess the same unique aspects of native hyaline cartilage and tends to be far less durable.
- Hyaline cartilage problems are generally caused by disease such as occurs with rheumatoid arthritis or wear and tear (osteoarthritis), or secondary to an injury, either acute (sudden), or recurrent and chronic (ongoing).
- Such cartilage disease or deterioration can compromise the articular surface causing pain and further deterioration of joint function.
- various methods have been developed to treat and repair damaged or destroyed articular cartilage.
- abrasion arthroplasty e.g., oral medication or medication by injection into the joint
- abrasion chondralplasty e.g., abrasion chondralplasty.
- the principle behind this procedure is to attempt to stimulate natural healing.
- the bone surface is abraded, removing approximately 1 mm. or less using a high-speed rotary bun or shaving device. This creates an exposed subchondral bone bed that will bleed and will initiate a fibrocartilage healing response.
- this procedure has been widely used over the past two decades and can provide good short term results, (1-3 years), the resulting fibrocartilage surface is seldom able to support long-term weight bearing, particularly in high-activity patients, and is prone to wear.
- microfracture incorporates similar concepts of creating exposed subchondral bone.
- the cartilage layer of the chondral defect is removed.
- Several pathways or “microfractures” are created to the subchondral bleeding bone bed by impacting a metal pick or surgical awl at a minimum number of locations within the lesion.
- a fibrocartilage healing response is initiated, forming a replacement surface.
- Results for this technique are generally similar to abrasion chondralplasty.
- a cartilage transplant referred to as a Mosaicplasty or osteoarticular transfer system (OATS) technique.
- OATS osteoarticular transfer system
- a series of plugs By repeating this process, transferring a series of plugs, and by placing them in close proximity to one another, in mosaic-like fashion, a new grafted hyaline cartilage surface can be established.
- the result is a hyaline-like surface interposed with a fibrocartilage healing response between each graft.
- U.S. Pat. No. 5,782,835 to Hart et al. discloses an apparatus and method for repair of articular cartilage including a bone plug removal tool, and a bone plug emplacement tool.
- the method of repairing defective articular cartilage includes the steps of removing the defective cartilage and forming a hole of sufficient depth at the site. A bone plug comprising intact bone and cartilage adhering thereto is removed from a bone lacking defective cartilage is placed in the hole at the site of the damage.
- U.S. Pat. No. 5,413,608 to Keller discloses a knee joint endoprosthesis for replacing the articular surfaces of the tibia comprising a bearing part which is anchored on the bone having an upper bearing surface and a rotatable plateau secured on the bearing surface and forming a part of the articular surface to be replaced.
- a journal rises from the bearing surface and cooperates with a bore in the plateau to provide lateral support.
- U.S. Pat. No. 5,632,745 to Schwartz describes a method of surgically implanting into a site a bio-absorbable cartilage repair assembly.
- the assembly includes a bio-absorbable polygonal T-shaped delivery unit having radial ribs to be mounted in the removed area and a porous bio-absorbable insert supported by and in the delivery unit.
- the method comprises the steps of preparing the site to receive the assembly by removing a portion of the damaged cartilage and preparing the site to receive the assembly by drilling and countersinking the bone.
- the assembly is inserted and seated using an impactor in the drilled and countersunk hole in the bone until the assembly is flush with the surrounding articular surface.
- U.S. Pat. No. 5,683,466 to Vitale illustrates an articular joint surface replacement system having two opposing components.
- Each component has a tapered head piece for covering the end of a bone and for acting as an articular surface, an integrally formed screw stem of sufficient length to extend into the bone and inwardly angled bone grips on the underside of the head piece to allow fixation to the bone by compression fit.
- the partially spherical convex shaped exterior of the first component complements the partially spherical concave shaped exterior of the second component.
- U.S. Pat. No. 5,702,401 to Shaffer discloses an intra-articular measuring device including a hollow handle defining a first passageway and a hollow tube having a second passageway extending from the handle, the hollow tube carrying a projection at its distal end for seating on a fixed site and a probe disposed at the distal end of the hollow tube which may be directed to a second site, to enable measurement of the distance between the first and second sites.
- U.S. Pat. No. 5,771,310 to Vannah describes a method of mapping the three-dimensional topography of the surface of an object by generating digital data points at a plurality of sample points on said surface, each digital data point including a property value and a position value corresponding to a particular point representing the properties of the surface of the object.
- a 3-D transducer probe e.g., a digitizer
- the sample points are digitized to generate a real-time topography or map on a computer screen of selected properties of the object, including without limitation, surface elevation, indentation stiffness, elevation of sub-surface layers and temperature.
- Prosthetics for total knee replacement whereby the entire knee joint or a single compartment of the knee joint is replaced can be a common eventuality for the patient with a large focal defect.
- these patients are also managed with anti-inflammatory medications, eventual erosion of the remaining articular cartilage results in effusion, pain, and loss of mobility and/or activity for the patient.
- Problems encountered after implanting such prostheses are usually caused by the eventual loosening of the prosthetic due to osteolysis, wear, or deterioration of the cements used to attach the device to the host bones.
- some prostheses used are actually much larger than the degenerated tissue that needs to be replaced, so that extensive portions of healthy bone are typically removed to accommodate the prostheses.
- Patients who undergo TKR often face a long and difficult rehabilitation period, and the life span of the TKR is accepted to be approximately 20 years. Accordingly, efforts are made to forgo the TKR procedure for as long as possible.
- An implant consistent with the invention for installation into a portion of an articular surface includes: a bone-facing distal surface; a proximal surface; and a protrusion formed by an extension of the bone-facing distal surface and the proximal surface.
- Another implant consistent with the invention for installation into a portion of an articular surface includes: a bone-facing distal surface configured to mate with an implant site created by excising a portion of the articular surface; a proximal surface having a contour based on an original surface contour of the excised portion of the articular surface; and a cavity configured to allow an un-excised portion of the articular surface proximate to the implant to remodel over a perimeter edge of the proximal surface.
- Another implant consistent with the invention for installation into a portion of an articular surface having an anterior portion, a posterior portion, a medial portion and a lateral portion includes: a bone-facing distal surface configured to mate with an implant site created by excising a portion of the articular surface; and a proximal surface having a contour based on an original surface contour of the excised portion of the articular surface, and at least two side surfaces each having a concentric arcuate shape with a common center, wherein the implant has an elongate arcuate geometric shape.
- a method for replacing a portion of an articular surface of bone consistent with the invention includes: establishing a working axis substantially normal to an articular surface of bone; excising a portion of the articular surface adjacent to the axis, thereby creating an implant site, the implant site having a first and second opposing arcuate shaped sides; and installing an implant to the implant site.
- Another method of replacing a portion of an articular surface of bone consistent with the invention includes: locating an existing defect in the articular surface; establishing a working axis substantially normal to the articular surface and substantially centered with the existing defect; excising a portion of the articular surface adjacent to the axis, thereby creating an implant site; and installing an implant in the implant site, wherein at least a portion of the existing defect is exposed around a perimeter of the implant.
- Another implant for installation into a portion of an articular surface includes: a bone-facing distal surface configured to mate with an implant site created by excising a portion of the articular surface; a proximal surface having a contour based on an original surface contour of the excised portion of the articular surface; at least one arcuate shaped side surface configured to abut an edge of the excised portion of the articular surface, the arcuate shaped side surface having a radial extension configured to cover an un-excised portion of the articular surface proximate to the implant.
- Another method for replacing a portion of an articular surface of bone consistent with the invention includes: establishing a working axis substantially normal to an articular surface of bone, the articular surface having a medial side and lateral side defining a width of the articular surface; excising a portion of the articular surface adjacent to the axis, thereby creating an implant site, wherein the excising is performed using a cutting tool that rotates about the axis, the cutting tool having a circular blade portion, the circular blade portion having a diameter greater than the width of the articular surface; and installing an implant to the implant site.
- Another implant consistent with the invention for installation into a portion of an articular surface includes: a bone-facing distal surface configured to mate with an implant site created by excising a portion of the articular surface; and a proximal surface having a contour based on an original surface contour of the excised portion of the articular surface, wherein the proximal surface has at least one indentation formed in the proximal surface configured to promote remodeling of articular cartilage over a portion of the proximal surface of the implant once seated.
- FIG. 1 is a fragmentary side view of a knee having therein an exemplary assembled fixation device and implant of the joint surface repair system surgically implanted by the method in one embodiment of the present invention
- FIG. 2 a is an exploded side view of an exemplary fixation screw and hex-shaped proximal extension in one embodiment of the present invention
- FIG. 2 b is an exploded perspective view of an exemplary fixation screw and hex-shaped proximal extension in one embodiment of the present invention
- FIG. 3 a is a side view of an exemplary assembled fixation screw and hex shaped extension in one embodiment of the present invention
- FIG. 3 b is an exploded perspective view of another exemplary fixation screw and implant in one embodiment of the present invention.
- FIG. 4 a is a perspective view of the upper surface of an exemplary implant in one embodiment of the present invention.
- FIG. 4 b is a side view of an exemplary implant in one embodiment of the present invention.
- FIG. 4 c is a perspective view of the lower surface of an exemplary implant in one embodiment of the present invention.
- FIG. 5 a is a side view of an exemplary assembled fixation device and implant in one embodiment of the present invention.
- FIG. 5 b is a perspective view of an assembled fixation device and implant in one embodiment of the present invention.
- FIG. 5 c is a perspective view of the upper surface of an exemplary implant, in one embodiment of the present invention.
- FIG. 5 d is a perspective view of the lower surface of an exemplary implant, in one embodiment of the present invention.
- FIG. 6 a is a sectional view of a knee having damaged articular cartilage, showing an exemplary guide pin drilled into the central portion of the defect and an arthroscope being disposed adjacent thereto, in a surgical procedure consistent with one embodiment of the present invention
- FIG. 6 b is a side view of the distal tip of an exemplary drill device for boring a pilot hole to receive an exemplary fixation screw, in one embodiment of the present invention
- FIG. 7 a is a sectional view of a knee having damaged articular cartilage, showing an exemplary fixation screw being driven into the defect by an exemplary socket type driver arranged on the guide pin, in a surgical procedure consistent with one embodiment of the present invention
- FIG. 7 b is a side view of the exemplary fixation screw, socket type driver and guide pin of FIG. 7 a , illustrating the hex shaped proximal extension in a cross-sectional view, in a surgical procedure consistent with one embodiment of the present invention
- FIG. 8 a is a perspective view of a knee having damaged articular cartilage, showing an exemplary fixation screw and hex-shaped proximal extension implanted in the defect after removal of an exemplary socket type driver and guide pin, in a surgical procedure consistent with one embodiment of the present invention
- FIG. 8 b is a sagital view of the exemplary fixation screw and hex-shaped proximal extension of FIG. 8 a implanted in the defect after removal of an exemplary socket type driver and guide pin, in a surgical procedure consistent with one embodiment of the present invention
- FIG. 8 c is a perspective view of an exemplary fixation screw, proximal extension and cover, in one embodiment of the present invention.
- FIG. 9 a is a sectional view of an exemplary fixation screw and hex-shaped proximal extension implanted in the defect with the exemplary guide pin replaced and an exemplary measuring tool arranged thereon, in a surgical procedure consistent with one embodiment of the present invention
- FIG. 9 b is a side partial cross-sectional view of the exemplary fixation screw and hex-shaped proximal extension of FIG. 9 a implanted in the defect with the exemplary guide pin replaced and an exemplary measuring tool arranged thereon, in a surgical procedure consistent with one embodiment of the present invention
- FIG. 9 c is a perspective view of an exemplary fixation screw and proximal extension, with the cover removed, in one embodiment of the present invention.
- FIG. 10 a is a sectional view of an exemplary fixation screw and hex-shaped proximal extension implanted in the defect, after removal of the hex-shaped proximal extension, with an exemplary pin and suture strands placed therethrough, in a surgical procedure consistent with one embodiment of the present invention
- FIG. 10 b is a side partial cross-sectional view of the exemplary fixation screw and hex-shaped proximal extension of FIG. 10 a , implanted in the defect, with an exemplary pin and suture strands placed therethrough, in a surgical procedure consistent with one embodiment of the present invention
- FIG. 11 a is a sectional view of an exemplary fixation screw implanted in the defect, with an exemplary pin and suture strands placed therethrough, showing the implanted fixation screw with the implant being tensioned on the suture strands, in a surgical procedure consistent with one embodiment of the present invention
- FIG. 11 b is a partial cross-sectional view of the exemplary fixation screw of FIG. 9 a implanted in the defect, showing the implant positioned in the interchondular notch, in a surgical procedure consistent with one embodiment of the present invention
- FIG. 12 is a sectional view of an exemplary fixation screw implanted in the defect, wherein, after placement of the implant and removal of the suture strands, the implant is driven into place with an impactor and hammer, in a surgical procedure consistent with one embodiment of the present invention
- FIG. 13 is a side cross-sectional view of an exemplary fixation screw implanted in the defect, after placement of the implant, wherein, after removal of the impactor and hammer, cement is injected between the implant and the bone, in a surgical procedure consistent with one embodiment of the present invention
- FIG. 14 a is a schematic representation of the two datum curves used to define a patient-specific three-dimensional surface for construction of the articular or lower surface of an implant in one embodiment of the present invention
- FIG. 14 b is a top view of an exemplary hex-shaped proximal extension in one embodiment of the present invention.
- FIG. 14 c is a perspective view of the bone-contacting or upper surface of an exemplary implant, in one embodiment of the present invention.
- FIG. 15 a is a perspective view of an exemplary compass instrument, in one embodiment of the present invention.
- FIG. 15 b is a perspective view of the distal offset arm of an exemplary compass instrument and cutting blade to be mounted thereon, in one embodiment of the present invention
- FIG. 15 c is a perspective view of an exemplary driver, showing an exemplary implant on an exemplary tether element, in one embodiment of the present invention
- FIG. 15 d is a perspective view of an exemplary driver, showing an exemplary implant tensioned on an exemplary tether element, in one embodiment of the present invention
- FIG. 16 is a perspective view of an exemplary compass instrument and cutting blade mounted on an exemplary guide pin, in one embodiment of the present invention.
- FIG. 17 a is a perspective view of another exemplary cutting blade, in one embodiment of the present invention.
- FIG. 17 b is a perspective view of an exemplary measuring probe, in one embodiment of the present invention.
- FIG. 17 c is a perspective view of an exemplary multi-faced blade mounted in the distal offset arm of an exemplary compass instrument, in one embodiment of the present invention.
- FIG. 18 a is a perspective view of an exemplary site preparation and cutting device, in one embodiment of the present invention.
- FIG. 18 b is a cross sectional view of the exemplary site preparation and cutting device of FIG. 18 a, in one embodiment of the present invention
- FIG. 18 c is a perspective view of another exemplary site preparation and cutting device, in one embodiment of the present invention.
- FIG. 18 d is a side view of another exemplary site preparation and cutting device, in one embodiment of the present invention.
- FIG. 18 e is a perspective view of another exemplary site preparation and cutting device, in one embodiment of the present invention.
- FIG. 19 a is a sectional view of the upper surface of an exemplary implant, in one embodiment of the present invention.
- FIG. 19 b is a side view of a portion of the exemplary implant of FIG. 19 a , in one embodiment of the present invention.
- FIG. 19 c is a perspective view of the upper surface of the exemplary implant of FIG. 19 a , in one embodiment of the present invention.
- FIG. 19 d is an exploded perspective view of another exemplary implant with taper lock ring, washer and suture, in one embodiment of the present invention.
- FIG. 19 e is a top perspective view of the exemplary implant of FIG. 19 d seated in the taper lock ring, in one embodiment of the present invention.
- FIG. 19 f is a bottom perspective view of the exemplary implant of FIG. 19 d seated in the taper lock ring, with washer and suture, disposed within an incision near the defect site, in one embodiment of the present invention
- FIG. 19 g is a perspective view of the exemplary implant of FIG. 19 d seated in the taper lock ring, with washer and suture, wherein the suture is threaded through an aperture at the distal end of a seating tool, at a first point in time during the process of seating the implant into the defect site, in one embodiment of the present invention
- FIG. 19 h is another perspective view of the exemplary implant of FIG. 19 d seated in the taper lock ring, with washer and suture, wherein the suture is threaded through an aperture at the distal end of a seating tool, at a second point in time during the process of seating the implant into the defect site, in one embodiment of the present invention
- FIG. 19 i is another perspective view of the exemplary implant of FIG. 19 d seated in the taper lock ring, wherein the distal end of a seating tool is disposed onto the implant, at a third point in time during the process of seating the implant into the defect site, in one embodiment of the present invention
- FIG. 20 a is a perspective view of an exemplary inner recording element of an exemplary measuring device, in one embodiment of the present invention.
- FIG. 20 b is a perspective view of an exemplary outer marking element of an exemplary measuring device, in one embodiment of the present invention.
- FIG. 20 c is a cross-sectional perspective view of an exemplary measuring device showing an exemplary inner recording element and an exemplary outer marking element, in one embodiment of the present invention
- FIG. 20 d is an exploded perspective view of another exemplary measuring device, in one embodiment of the present invention.
- FIG. 20 e is a perspective view of the exemplary measuring device of FIG. 20 d , illustrating an exemplary scroll alignment feature, in one embodiment of the present invention
- FIGS. 20 f and 20 g are side views of the exemplary measuring device of FIG. 20 d illustrating the translational motion of the handle with respect to the tip of the device, in one embodiment of the present invention
- FIG. 20 h is a perspective view of the distal end of the exemplary measuring device of
- FIG. 20 d in one embodiment of the present invention.
- FIG. 20 i is a perspective view of the distal end of the exemplary measuring device of FIG. 20 d with outer element, disposed upon the inner element engaging a mating feature of the screw, in one embodiment of the present invention
- FIG. 21 is a perspective view of an exemplary unitary implant, in one embodiment of the present invention.
- FIG. 22 is a perspective view of a defect site with a keyed aperture for receiving the exemplary unitary implant of FIG. 21 , in one embodiment of the present invention
- FIG. 23 is a perspective view of an exemplary composite implant, in one embodiment of the present invention.
- FIG. 24 is a perspective view of another exemplary composite implant, in one embodiment of the present invention.
- FIG. 25 is a perspective view of an exemplary implant illustrating the geometry of said implant for use in an algorithm for establishing minimum implant thickness, in one embodiment of the invention
- FIG. 26 is a perspective view of an exemplary implant illustrating the geometry of said implant for use in an algorithm for establishing minimum implant thickness, in one embodiment of the invention
- FIG. 27 a is a perspective view of an exemplary drill guide device in an exemplary generic bone implant embodiment of the present invention.
- FIG. 27 b is a perspective view of another exemplary drill guide device in an exemplary generic bone implant embodiment of the present invention.
- FIG. 28 a is a top sectional view of the anterior-posterior plane of an articulating surface in an exemplary generic bone implant embodiment of the present invention
- FIG. 28 b is a side sectional view of the medial-lateral plane of an articulating surface in an exemplary generic bone implant embodiment of the present invention.
- FIG. 29 is a perspective view of the use of an exemplary drill guide in an exemplary generic bone implant embodiment of the present invention, as the drill guide is brought up to a lesion site of the articulating surface;
- FIG. 30 is a perspective view of the use of an exemplary drill guide in an exemplary generic bone implant embodiment of the present invention, as the drill guide is seated into position and a guide pin is driven through the drill guide;
- FIG. 31 is a perspective view of the articulating surface in an exemplary generic bone implant embodiment of the present invention, as a bone drill is passed over the guide pin to create a pilot hole for the screw;
- FIG. 32 is a cross-sectional view of the articulating surface in an exemplary generic bone implant embodiment of the present invention, as the screw is driven into the pilot hole with a cap positioned into the screw;
- FIG. 33 is a cross-sectional view of the articulating surface in an exemplary generic bone implant embodiment of the present invention, as the cap is removed and a rod is inserted into the screw, and the guide is positioned back over the rod and returned to its position in contact with the articular surface;
- FIG. 34 is a side perspective view of the articulating surface in an exemplary generic bone implant embodiment of the present invention, as the guide is used to take a depth measurement needed for implant geometry;
- FIG. 35 is a top perspective view of the lower surface of an exemplary implant in an exemplary generic bone implant embodiment of the present invention.
- FIG. 36 is a side perspective view of an exemplary implant in an exemplary generic bone implant embodiment of the present invention.
- FIG. 37 is a side perspective view of another exemplary implant in an exemplary generic bone implant embodiment of the present invention.
- FIG. 38 is a perspective view of the articulating surface in an exemplary generic bone implant embodiment of the present invention, as the implant site is reamed with a cutting/reaming tool in preparation for receiving an implant;
- FIG. 39 is a top perspective view of an alternative exemplary cutting/reaming tool in an exemplary generic bone implant embodiment of the present invention.
- FIG. 40 is a side perspective view of an exemplary cleaning tool for cleaning the female taper of the screw prior to delivery of the implant, in an exemplary generic bone implant embodiment of the present invention
- FIG. 41 is a side perspective view of an exemplary suction tool for holding and delivering the implant, in an exemplary generic bone implant embodiment of the present invention.
- FIG. 42 is a side perspective view of an exemplary suction tool holding an implant in place, in an exemplary generic bone implant embodiment of the present invention.
- FIG. 43 is a side cross-sectional view of an exemplary suction tool holding an implant in place, with an implant in place, in an exemplary generic bone implant embodiment of the present invention
- FIG. 44 is a top perspective view of the articulating surface in an exemplary generic bone implant embodiment of the present invention, with the implant driven into its final position;
- FIG. 45 is a side perspective view of an exemplary removal/revision tool in an exemplary generic bone implant embodiment of the present invention.
- FIG. 46 is a side perspective view of an exemplary removal/revision tool, with an implant in place, in an exemplary generic bone implant embodiment of the present invention
- FIG. 47 illustrates an exemplary alternatively-keyed embodiment of the screw and the exemplary alternatively-keyed implant to which it is adapted to mate, in an exemplary embodiment of the present invention
- FIG. 48 illustrates a side cross-sectional view of an exemplary alternatively-keyed embodiment of the screw, in an exemplary embodiment of the present invention
- FIG. 49 illustrates a side perspective view of the articular surface of a lesion site and an exemplary biaxial measuring tool for developing an axis normal to the articular surface, in one embodiment of the present invention
- FIG. 50 illustrates another side perspective view of the articular surface of a lesion site and an exemplary biaxial measuring tool for developing an axis normal to the articular surface, in one embodiment of the present invention
- FIG. 51 illustrates a side exploded view of an exemplary biaxial measuring tool, in one embodiment of the present invention
- FIG. 52 illustrates a top perspective view of the distal end of an exemplary biaxial measuring tool in a first position, in one embodiment of the present invention
- FIG. 53 illustrates a top perspective view of the distal end of an exemplary biaxial measuring tool in a second position, in one embodiment of the present invention
- FIG. 54 illustrates an exemplary digital measuring system in one embodiment of the present invention
- FIG. 55 illustrates an exploded perspective view of an exemplary handpiece in an exemplary digital measuring system in one embodiment of the present invention
- FIG. 55 a illustrates a top perspective cutaway view of an exemplary printed linear index strip passing through an exemplary linear head for reading, in an exemplary handpiece in an exemplary digital measuring system in one embodiment of the present invention
- FIG. 55 b illustrates a top perspective cutaway view of an exemplary printed rotary index strip passing through an exemplary rotary head for reading, in an exemplary handpiece in an exemplary digital measuring system in one embodiment of the present invention
- FIG. 55 c illustrates an exemplary linear index strip in an exemplary handpiece in an exemplary digital measuring system in one embodiment of the present invention
- FIG. 55 d illustrates an exemplary rotary index strip in an exemplary handpiece in an exemplary digital measuring system in one embodiment of the present invention
- FIG. 56 a illustrates a side perspective view of an exemplary handpiece with the probe assembly removed, in an exemplary digital measuring system in one embodiment of the present invention
- FIG. 56 b illustrates a side perspective view of an exemplary handpiece, including the probe assembly, in an exemplary digital measuring system in one embodiment of the present invention
- FIG. 57 illustrates a top perspective view of an assembled exemplary handpiece, in an exemplary digital measuring system in one embodiment of the present invention
- FIG. 58 illustrates a side perspective view of an assembled exemplary handpiece, in an exemplary digital measuring system in one embodiment of the present invention
- FIG. 59 illustrates a top cross-sectional view of an assembled exemplary handpiece, in an exemplary digital measuring system in one embodiment of the present invention
- FIG. 60 illustrates a side cross-sectional view of an assembled exemplary handpiece, in an exemplary digital measuring system in one embodiment of the present invention
- FIG. 61 illustrates a side cutaway perspective view of an exemplary base unit, in an exemplary digital measuring system in one embodiment of the present invention
- FIG. 62A is a top perspective view an alternative exemplary embodiment of a substantially round implant having a protrusion
- FIG. 62B is a cross sectional view of the implant of FIG. 62A taken along the line B-B of FIG. 62A ;
- FIG. 62C is a side perspective view of the implant of FIG. 62A ;
- FIG. 63A is a side perspective view of another implant embodiment consistent with the invention having protuberances
- FIG. 63B is a cross sectional view of the implant of FIG. 63A taken along the line B-B of FIG. 63A ;
- FIG. 64A is an alternative embodiment of an implant having a cavity to allow an unexcised portion of articular surface proximate to the implant to grow over the perimeter edge of the implant;
- FIG. 64B is a cross sectional view of the implant of FIG. 64A taken along the line B-B of FIG. 64A ;
- FIG. 65A is another alterative embodiment of an elongated implant consistent with the invention.
- FIG. 65B is a perspective view of an implant site and a reaming tool for preparing the implant site to accept the implant of FIG. 65A ;
- FIG. 65C is a cross sectional view of the bottom surface of the implant site of FIG. 65B ;
- FIG. 65D is a perspective view of the implant of FIG. 65A being seated or placed into the implant site of FIG. 65B ;
- FIG. 66A is a top perspective view of alternative elongated implant embodiment having protrusions for covering proximate portions of un-excised articular surface when the implant is seated;
- FIG. 66B is a top perspective view of the implant of FIG. 66A being seated or placed into a matching implant site;
- FIG. 67 is a perspective view of an implant being seated into an existing defect without cutting the borders of the defect
- FIG. 68A is a top perspective view of an implant having grooves to promote remodeling of articular cartilage over a proximal surface of the implant;
- FIG. 68B is a cross sectional view of the implant of FIG. 68A ;
- FIG. 68C is a perspective view of a portion of the perimeter edge of the implant of FIG. 68A illustrating particular edge geometry to also promote remodeling of articular cartilage over a proximal surface of the implant;
- FIG. 68D is a top perspective view of the implant of FIG. 68A seated in an articular surface illustrating the remodeling of articular cartilage over a portion of the proximal surface of the implant.
- FIG. 1 shows a surgically implanted articular joint surface repair system consistent with the present invention.
- the assembled fixation device includes fixation screw 10 , implant 40 , and anchoring pin 5 , implanted in the defect in the medial femoral chondral surface 55 of knee 50 .
- Implant 40 is configured so that bearing or bottom surface 41 of the implant reproduces the anatomic contours of the surrounding articular surface of the knee 50 .
- fixation screw 10 comprises threads 12 running the length of the screw from tapered distal tip 11 to hex-shaped drive 15 .
- the screw includes a tapered distal end 11 , and aggressive distal threads 12 , so that, as screw 10 is driven into the subchondral bone 100 (as shown in FIG. 7 a ) the screw dilates open and radially compress the subchondral bone, increasing its local density and thereby increasing the fixation strength of the screw.
- the screw 10 may taper down to the distal end 11 , and the diameter of the screw may become greater and more uniform at the center thereof, so that adjustment of the depth of the screw 10 with respect to the subchondral bone 100 does not significantly further increase or decrease the compression of the subchondral bone.
- One or more milled slots 13 run the length of the uniform diameter portion of the screw 10 . Slots 13 ensure that as healing or tissue in-growth begins, migrational or rotational movement of the screw is inhibited.
- the screw 10 is configured to be driven by a female or socket type driver 2 as shown in FIG. 7 b , which engages a hex-shaped drive 15 located toward the proximal end 17 of the screw.
- a cylindrical proximal extension 14 (which may, alternatively, be a recess 303 which mates with a plug or other protrusion on the implant surface, as shown in FIG. 8 c ) extends from hex-shaped drive 15 , which eventually serves as a fixation element for surface prosthetic implant 40 .
- Hex-shaped cover 30 (which may, alternatively, be a plug 301 , for mating with a fixation element 302 having a recess, as shown, e.g., in FIGS. 3 b , 8 c , and 9 c , and described in the following paragraph) is configured to engage the cylindrical proximal extension 14 of the screw 10 to prevent exposure of the cylindrical extension from inadvertent contact or damage.
- the hex-shaped cover 30 is finished with a radiused proximal end 31 that assists in the visual determination of the correct depth setting of the screw.
- Through hole 32 in the hex-shaped cover 30 corresponds with through hole 16 in the fixation screw 10 .
- the female-shaped cover may instead be a plug 301 having a male-shaped mating component 305 , for mating with a fixation element 302 of a screw 10 ′ having a recess 303 .
- the shape of the cover and plug, or other recessed, protruding, or mating components may be other than hexagonal, and those in the art will recognize that one of any number of shapes or configurations for such components may be employed in a device or method consistent with the invention.
- a suture 313 or other flexible element, or other guide feature may be used in place of a guide rod, or a guide rod or wire may be eliminated altogether from one or more steps consistent with the invention described herein.
- the suture 313 may be fixedly or removably attached to the plug 301 .
- implant 40 comprises lower bearing surface 41 , top surface 42 and protrusion 45 located centrally on the bottom surface.
- top surface 42 of the implant 40 is not a bearing surface, and instead is fixed into subchondral bone 100 , a series of stepped machine cuts 43 following the contours of the defect are created.
- stepped machine cuts 43 a contoured contact surface matching the defect in the subchondral bone 100 is created. This contact surface results in an increased surface area that should enhance resistance to loosening of the implant 40 via rotational or translational loading.
- the stepped cuts are shown as square cross-section cuts, but the cuts may be circular, triangular, or another configuration.
- precision taper 44 is machined into or onto a protrusion 45 on the top surface 42 of the implant.
- the precision taper 44 is configured to engage the cylindrical proximal extension 14 of the screw 10 , once the hex-shaped cover 30 has been removed therefrom. Taper 44 may be mated with extension 14 so that a friction fit is provided between these surfaces.
- the assembled fixation device is shown in FIGS. 5 a and 5 b .
- other engagement mechanisms such as snap-fits, press-fits, threads, or coupling elements, for example, may also be used.
- leading pin 47 arranged on the protrusion 45 assists penetration into subchondral bone.
- guide aperture 46 passes through the top 42 and bottom 41 surfaces of the implant 40 , just slightly off center of the reference axis 20 A.
- guide aperture 46 may be located in the center of the implant 40 and corresponds to through hole 16 running through the central lumen in the fixation screw 10 .
- Bone cement may be injected through guide aperture 46 on the surface of the implant 40 and through hole 16 in the fixation screw 10 , to enhance the contact surface between the device and the subchondral bone.
- the implant is constructed of cobalt chromium, although other materials may be used, including implantable plastics.
- biologically active coatings or surface treatments may be utilized or combined as laminates, particularly with respect to the bearing surfaces and bone contacting surfaces.
- biologically active coatings or surface treatments e.g., to enhance bone ingrowth or improve wear properties
- surface treatments e.g., to enhance bone ingrowth or improve wear properties
- precision taper 44 may be a male-shaped component 304 instead of the above-described female component 44 .
- the male-shaped component 304 of the implant 40 ′ is configured for mating with a fixation element 302 of the screw 10 ′ having a recess 303 adapted to receive the male-shaped component 304 .
- FIGS. 6 a - 13 depict one exemplary joint surface methodology of the present invention.
- FIG. 6 a shows a focal defect 1 of the articular surface 55 of the femoral chondyle bone of the knee 50 .
- This defect is identified by arthroscope 25 inserted in the area of the defect 1 during a diagnostic arthroscopy or surgical arthroscopy.
- the disclosed surgical intervention begins by drilling a guide pin 20 defining reference axis 20 A into the central portion of the defect 1 via an incision 200 typical of arthroscopic procedures. Placement of this pin may be done using visual, freehand techniques, or may be located centrally by using outer element 71 of a measuring tool 70 (as shown in FIGS.
- This reference axis 20 A serves to establish a working axis located central to the defect 1 for the procedures that follow, and arthroscope 25 may be used to view the joint for purposes of establishing a reference axis 20 A generally perpendicular to and bisecting the existing articular surface 55 defined by radii 60 and 61 , as shown in FIG. 8 b .
- arthroscope 25 may be used to view the joint for purposes of establishing a reference axis 20 A generally perpendicular to and bisecting the existing articular surface 55 defined by radii 60 and 61 , as shown in FIG. 8 b .
- fixation screw 10 and hex-shaped cover 30 are driven into the defect 1 in the subchondral bone 100 by socket-type driver 2 mounted over (i.e., about) guide pin 20 located on reference axis 20 A.
- the depth of fixation screw 10 may be adjusted by driver 2 so that the bottom of the radiused surface 31 of the hex-shaped cover 30 is positioned tangent to the radii 60 and 61 that define the existing articular surface 55 .
- the guide pin 20 is removed and the knee 50 is articulated through its range of motion to ensure that the height of the radiused surface 31 of the hex-shaped cover 30 is proper, since the prosthetic surface 41 of the implant 40 is created also to be tangent to this radiused surface 31 .
- the depth positioning of the radiused surface 31 of the hex-shaped cover 30 establishes a point of origin or a reference point for all future measuring and machining operations. Arthroscopic examination may be carried out from multiple arthroscopic views to confirm positioning.
- a drill mechanism 306 may be used to bore a pilot hole for receiving a fixation screw 10 (as shown, e.g., in FIGS. 2 a , 2 b and 3 a ).
- the drill may have a shank portion 307 and a bit portion 308 .
- the bit portion 308 may include a spiral or parabolic fluted tip 309 having proximal 310 , medial 311 , and distal 312 portions.
- the root diameter at the medial portion 311 is substantially equal to the diameter of the fixation screw 10 , and the diameter decreases as the distal portion 312 tapers away from the shank 307 .
- the proximal portion 310 of the bit 308 may be used as a visual indicator during drilling, to determine the point at which the proper bore depth has been attained.
- the drill mechanism may have a central lumen (not shown) having a diameter slightly greater than the diameter of the guide pin 20 (as illustrated in FIG. 6 a ) running along its length, so that, with the guide pin 20 in place, the drill 306 may be disposed about the guide pin 20 during drilling to ensure proper location of the pilot hole with respect to the articular surface 55 .
- a self-drilling or self-tapping screw may be used, as those skilled in the art will recognize.
- instrument 120 For surface preparation and accurate measurement of the implant site and the subsequent sizing of the implant, instrument 120 is provided.
- the compass instrument 120 may be configured to serve as a mounting tool for a number of functional blades or tips and when located about the axis 20 A, via guide rod 20 , may be used for measuring and cutting operations.
- compass instrument 120 includes handle 110 , a cannulated shaft 111 that extends through the handle, and a cannulated distal offset arm 112 .
- the instrument may be rigid in construction and may be a durable reusable and resterilizable instrument.
- the distal offset arm 112 is configured so that it can be introduced into a site through an incision 200 typical of an arthroscopic procedure.
- shaft 111 can be angularly repositioned so that it becomes more coaxial to the reference axis 20 A and advanced in-line with the reference axis 20 A towards the implant target site. While performing this maneuver to position the compass instrument 120 , the guide pin 20 should be removed from its position in the defect 1 . When compass 120 is in its proper position at or near the implant target site, the guide pin 20 is delivered through the instrument cannulation 113 , re-establishing the working (reference) axis 20 A used to define the implant geometry.
- a slotted surface 114 for engaging a series of cutting blades 121 , boring blades 124 , or measuring probes 122 .
- the slots 115 are configured so that said series of cutting blades 121 , boring blades 124 ( FIG. 17 c ), measuring probes 122 , 123 ( FIGS. 17 a , 17 b ), or like elements may be partially constrained or fixed in position such that they may be adjusted linearly along the length of the slotted surface 114 over a defined distance of travel. Intersecting the plane of travel defined by slotted surface 114 and slots 115 , is the cannulation 113 .
- the blade's position becomes fully constrained.
- a fixed length from the rotational or reference axis 20 A to the cutting surface 117 of cutting blade 121 is established. This defines the radius that is effected as the instrument 120 is rotated around the guide pin 20 , and corresponds to the overall diameter of the implant 40 that is delivered to the fully prepared site.
- the cutting blade 121 is used to circumscribe and cleanly cut the surrounding articular cartilage.
- blade 123 and measuring probe 122 may have multiple holes 118 that defines that probe/blade's functional diameter.
- the blades may be specifically configured so that staged or sequential cuts of varying depths and diameters can be performed within the procedure.
- such a blade can be configured by providing a readable scale 119 corresponding to the hole 118 pattern, so that the surgeon may determine and set the appropriate diameter as needed by positioning the guide pin 20 in the corresponding hole.
- the readable scale 119 may be located on the blade 123 with respect to the blade's cutting surface 117 , a high degree of positional accuracy may be achieved as the scale may be defined specifically for each type of blade.
- rounded tip 109 of measuring probe 122 can be used to determine the appropriate diameter and can be similarly sized and secured in the compass instrument 120 .
- the tip 109 may be rounded to prevent marring of the articular surface.
- FIG. 17 c shows a boring bit or bone cutting blade 124 with multiple cutting surfaces 107 and 108 configured in this fashion.
- a measuring tool 70 is inserted so that the reference axis 20 A is utilized.
- a central element of the measuring tool 70 is a post 75 that is static, establishes the axial location of the point of origin 80 , and mates with a rotational location feature within the screw 14 .
- an axial displacement or Z dimension can be established relative to the point of origin 80 for any point along the sweep of the outrigger.
- Each such Z dimension may be recorded in real time with conventional dial gauge indicators 72 or with a digital recording device, such as disclosed in U.S. Pat. No.
- the measuring tool may comprise a spring or other tensioning device (not shown), for urging the outrigger distally with respect to the handle of the tool.
- the outrigger is manually pressed against the articular cartilage, so as to maximally compress the articular cartilage upon recording data points, so that the data points taken are of a maximally “loaded” or “compressed” dimension.
- FIGS. 20 a , 20 b and 20 c show an alternative measuring and mapping device 210 for obtaining the articular surface dimension, comprising housing 217 and a recording element 218 .
- recording element 218 includes upper portion 219 , flange 222 and calibrated lower portion 220 .
- Key-shaped surface 221 located at distal end 225 of recording element 218 is configured to engage a reciprocal key-shaped surface in the proximal extension 14 of fixation screw 10 , or, for example, a key shaped cover arranged on the proximal end of the screw (not shown).
- the upper portion 219 of recording element 218 may be constructed of a relatively soft or other deformable material that can be marked with patient data.
- Cannulated shaft 223 runs through the central lumen of the recording element 218 .
- housing 217 includes a marking mechanism 224 located on the upper portion 226 of the housing, at or within window or aperture 230 .
- An indexing indicator 228 is located on the lower portion 227 of the housing 217 , at window or opening 229 .
- recording element 218 is inserted in housing 217 of measuring and mapping device 210 , so that the distal end 225 of recording element 218 appears through opening 232 .
- Tensioning means (not shown) in the device 210 , enables recording element 218 to move longitudinally within housing 218 .
- the measuring device 210 is inserted on the guide pin on reference axis 20 A so that key-shaped surface 221 engages the corresponding keyed surface of the screw and is maintained in static position thereby.
- key-shaped surfaces establish the rotational position of the articular surface points to be mapped relative to the screw.
- the surgeon rotates housing 217 and outer arm or outrigger 231 located at the distal end 235 of housing.
- marking mechanism 224 By depressing marking mechanism 224 , a series of depressions or marked points 240 is established in the relatively soft surface of the upper portion 219 of the recording element 218 , which deforms at these marked points so that they can be utilized as patient data.
- Indexing indicator 228 and calibrated lower portion 220 of recording element 217 allow for controlled rotational movement between housing 217 and recording element 218 .
- the measuring tool 70 is constructed so that it can be accurately indexed from a fixed starting point along 90 degree intervals to capture or map said four points 81 a , 81 b , 82 a and 82 b , over the course of its revolution.
- Locating surfaces or features created on the radius cover 30 , or along some length of the fixation screw 10 , hex-shaped drive surface of the screw 14 or on the cylindrical proximal extension (or recess) of the screw 14 correlate to some surface or feature on the measuring tool 70 and allow the measurement of the rotational position of the four measured points 81 a , 81 b , 82 and 82 b , about the reference axis 20 A with respect to said locating surfaces.
- This data becomes important in configuring the implant 40 with respect to the fixation screw 10 so that the proper orientation of said measured points to fabricated geometry is maintained.
- such measuring tool can be configured to measure any number of points at any interval desired.
- FIGS. 9 a and 9 b While the measurements are illustrated in FIGS. 9 a and 9 b as being taken from the bottom of the radiused surface 31 of the hex-shaped cover 30 of the screw, the measurements may alternatively be taken from the top of the screw 10 ′ itself, as shown in FIG. 9 b .
- a key 315 or other alignment feature may be provided, to indicate the starting point for taking measurements.
- the measuring tool used, as well as the implant manufactured both have a mating feature matching the key 315 , for properly locating the starting point of the measurements taken and thereby subsequently properly aligning the implant with respect to the defect.
- measuring tool 210 ′ comprises a handle 316 , outer shaft 333 , inner shaft 330 , scroll 317 , a tactile feedback portion 318 , ring 320 having a button 321 in communication with a sharp marking point 326 thereunder, a rotating portion 322 having a rotational lock 323 which prevents rotation of the rotating portion 322 when engaged, and an outrigger portion 324 .
- the handle 316 remains fixed during rotation and does not move while the tool 210 ′ is used for measuring.
- the scroll 317 is configured with a notch 325 or similar mating feature to align with a corresponding mating feature (not shown) of the handle 316 , such that the scroll can only align at one rotational point, at 0 degrees, with respect to the handle 316 upon loading into the tool 210 ′, e.g., by “snapping” into place.
- the sharp marking point 326 located inside the ring 320 under the sharp marking point 326 , marks a point of depression into the scroll 317 while first button 321 is being depressed. Instead of marking by making depressions on a scroll or spool, marking could alternatively be made upon nearly any surface, e.g., using ink to record on a paper spool, or by digital means.
- outer shaft 333 which is fixedly coupled to rotating portion 322 , outrigger 324 and ring 320 , is freely rotatably disposed about inner shaft 330 and slidably disposed about inner shaft 330 within a range bounded by points 334 and 337 .
- the outrigger 324 is retracted, and outer shaft 333 is located at a position of origin along a z-axis parallel to the inner 330 and outer 333 shafts, such that the proximal end of the ring 320 is located at position 335 .
- the outrigger 324 is extended, and outer shaft 333 is located at a position 0.250 in. (0.64 cm.) from the origin of the z-axis parallel to the inner 330 and outer 333 shafts, such that the proximal end of the ring 320 is located at position 335 ′.
- the motion of the sliding of the outer shaft 333 about inner shaft 330 during marking is translated via the outer shaft 333 , rotating portion 322 and ring 320 (including marking button 321 and marking point 326 ) to a location along the scroll 317 .
- the outrigger moves along the articular surface proximally or distally with respect to the inner shaft, and the displacement of the outrigger 324 along a z-axis parallel to the inner 330 and outer 333 shafts may be marked on the scroll 317 by depression of the button 323 at various points along the rotation of the outrigger 324 .
- the tactile feedback portion 318 has a series of depressions 319 or other tactile feedback means, e.g.
- a keyed mating feature 331 may be disposed at the distal end of the inner shaft 330 with respect to the outrigger portion, for mating with a key feature 315 on the screw 10 ′ (as shown in FIGS. 9 c and 20 i ), so as to locate properly the starting point of the measurements taken with respect to the screw, and the scroll 317 .
- FIG. 20 h illustrates a more detailed view of the distal end of the marking tool 210 ′, with outer shaft 333 , inner shaft 330 with keyed mating feature 331 , and outrigger 324 with rounded end 338 , which travels along the path of circle 339 .
- FIG. 20 i illustrates the measuring tool 210 ′, with the keyed mating feature 331 inserted into the recessed portion 303 of the screw 10 ′ at its fixation element 302 .
- data recorded during the mapping procedure described above can then be entered into a known parametric engineering design software or similar algorithm, as four values, 85 a , 85 b , 85 c , and 85 d , corresponding to the four measured points, 81 a , 81 b , 82 a and 82 b , with the origin 80 defining a reference plane.
- These four values 85 a , 85 b , 85 c and 85 d are represented by line elements that are geometrically constrained to lie upon a circle 90 , which represents the diameter of the measuring tool 70 .
- These line elements are also constrained to lie within planes that are perpendicular to one another.
- more than four points may be taken and used to map the articular surface, e.g., 8 points; however, a minimum of four points should be taken, so that two intersecting datum curves may be defined for purposes of mapping.
- Datum curves 86 and 87 representing the medial-lateral (“ML”) and anterior-posterior (“AP”) curves, are constructed by connecting the end points of the line elements 81 a and 81 b , and 82 a and 82 b and the point of origin 80 , which is common to both curves. These two datum curves 86 and 87 can be used to construct the articular or bottom surface 41 of the prosthetic implant 40 . By sweeping datum curve 87 along a path defined by datum curve 86 , a three dimensional surface is now defined.
- ML medial-lateral
- AP anterior-posterior
- this series of geometric relationships in a known parametric engineering model patient-specific geometry can be input as values and the model algorithm can be run to reproduce the anatomic contours mapped in the patients within only a few moments.
- this generic model is the starting point for all patient treatments. Sterile pins, screws, and measuring devices that are all non-patient-specific may be stocked in the hospital and ready to use whenever an appropriate defect is diagnosed.
- Patient-specific data may be transmitted from the surgeon to the fabricating facility via an interface to the Internet or other network. Data input into the interface may be read directly into the generic parametric model to produce a viewable and even mappable patient-specific parametric model within moments. Confirmation by the surgeon could initiate a work order for the production of the patient specific device.
- Existing technology allows the parametric model to generate toolpaths and programming, e.g., to a CAD/CAM system comprising appropriate hardware and/or software coupled to appropriate data-driven tools, to fabricate the implant.
- implant geometry may be defined whereby the top or bone contacting surface 42 of the implant 40 exhibits an axial symmetry.
- the central axis AA passes through the point of origin 80 of the implant 40 and when the implant is positioned at the target site, aligns with the original reference axis 20 A as defined by the guide pin 20 and fixation screw 10 .
- the central axis AA can then be used to define the preparation tools so that the bone contacting surfaces 42 of the implant 40 and the preparation tools can be matched in both configuration and dimension to create a mating fit between the surface of the prepared target site and the bone contacting surfaces 42 of the implant.
- the implant geometry and corresponding preparation tool geometry can be mated and optimized so that a minimum vertical thickness of the implant as well as a minimum depth of bone removal is required. This may be advantageous in ensuring good long term clinical results with the implant, as poor quality of fit between bone surfaces and bone-contacting surfaces of traditional orthopedic prosthetic devices has been noted to contribute to early clinical failures.
- a series of radial cuts 198 may create surfaces that increase resistance of the implant to rotational forces. These features may be located at the outer diameter 190 of the implant 40 to increase their effectiveness. Additional contact surfaces may also be created by one or more protrusions 195 located on the bottom 42 of the implant. Similarly, surface treatments known in the field of orthopedic devices, such as porous and/or osteoconductive coatings, may be utilized on surface 42 .
- outer diameter 190 may include a slight outward taper or protrusion 197 along the diametrical surface to enhance load bearing or load transfer properties of the implant to surrounding bone. This feature may also increase the fixation strength of the implant.
- a fillet 199 (as shown in FIG. 19 a ) that runs around the implant at the intersection of the diametrical surface 190 and the bearing surface 41 is also useful in providing a smooth transition between the host articular cartilage and the implant surface.
- the offset curves 88 and 89 can be extended to increase the overall thickness of the implant 40 or the offset curves may be eliminated entirely so that the contoured surface is backed by a revolved geometry that is symmetrical to reference axis 20 A.
- the thickness of the implant 40 requires adjustment.
- an unnecessarily thick implant requires a greater amount of bone to be removed at the target site. Therefore, the thickness of the implant may be determined by taking the largest obtained measurement and adding a minimal offset amount 208 .
- the implant is thinnest at the highest point on the ML curve.
- This can be similarly accomplished by adjusting the angle A ( FIG. 19 a ) of the bone-contacting surface 42 of the implant 40 and a corresponding angle of the preparation tool.
- This also allows for a correction of the implant geometry, to compensate for any non-perpendicular placement of the guide pin with respect to the articular surface.
- an exemplary algorithm consistent with the invention establishes the minimum thickness of an implant necessary to include all patient data points, receiving as input all of the points measured (typically, four) and identifying the largest value.
- One such exemplary algorithm is as follows (and as shown in FIGS. 25 and 26 ):
- a first data point D6 is initially assigned as the maximum value (maxval). If . . . then type statements are used to compare other data points (D11 and D14) to maxval. If other data points are greater than maxval, the algorithm reassigns maxval to the new larger data point.
- LLMT represents the height of the lower limit plane along the z-axis
- ULMT represents the height of the upper limit plane along the z-axis.
- D684 is a dimension that controls the ULMT plane, which is established in the model as the upper surface of the implant. ULMT is positioned as maxval plus an additional arbitrary and/or fixed material offset (0.045 in this case).
- FIGS. 5 c and 5 d illustrate an alternative embodiment of the implant 40 ′, having a ML curve between data points 340 and 341 and an AP curve between data points 342 and 343 , with male-shaped mating component 304 and key-shaped portion 344 for engagement with a reciprocal key-shaped surface in the proximal extension of a fixation screw, protrusions 345 (creating contact surfaces on the top 346 of the implant 40 ′), radial cuts 347 located at the outer diameter 348 of the implant 40 ′, and radius 349 (which may be formed, e.g. using an abrasive wheel) around the intersection of the outer diameter at point 341 and the surface comprising the patient geometry.
- bone cutting or scoring instrument 250 includes a handle (not shown), a cannulated shaft 111 that extends through the handle, and offset arm 140 housing adjustable blades 141 .
- individual cutting blades 141 are attached to offset arm 140 either fixedly or removably, e.g. via threaded portions 142 , into threaded recesses 342 of the offset arm 140 , although other attachment means may be used.
- guide pin 20 advanced through shaft 113 positioned on the reference axis 20 A, a fixed distance from the rotational or references axis 20 A to each of the cutting or scoring blades 141 is established.
- These lengths define the radii that are to be effected in the articular surface, as the scoring instrument 250 is rotated around the guide pin 20 , corresponding to the protrusions 195 on the bone contacting surface 42 of the implant 40 creating a matching fit between the bone surfaces of the prepared target site and the bone contacting surfaces of the implant.
- cutting blades are arranged on carrier 145 , configured so that it can be mounted within the slotted surface 114 of offset arm 112 , depicted in FIG. 17 a .
- cutting blades 141 can be fixedly positioned on offset arm 140 .
- the cutting and scoring device 250 can be fabricated to prepare the articular surface to correspond to the implant geometry to optimize fit.
- a bone cutting instrument 352 corresponds to the alternative embodiment of the implant 40 ′ illustrated in FIGS. 5 c and 5 d .
- Instrument 352 has a handle (not shown), a cannulated shaft 353 that extends through the handle and through the cannulation 355 , offset arm 354 with blades 350 and 351 corresponding to the protrusions 345 on the bone contacting surface 42 of the implant 40 creating a matching fit between the bone surfaces of the prepared target site and the bone contacting surfaces 346 of the implant 40 ′.
- an angular dimension 95 relating some locating surface or feature on the hex-shaped cover 30 or on the fixation screw 10 , to the four points 81 a , 81 b , 82 a and 82 b , may also be captured at the time of the initial procedure to assist in orientation of the implant 40 to the fixation screw 10 .
- Guide aperture 46 in implant 40 is located off the reference axis 20 A and may serve as the locating feature and/or as a suture passage way in the implantation procedure.
- a surface or feature created on the implant 40 may serve to reference or align to such locating surface on the hex-shaped cover 30 or the fixation screw 10 .
- Additional data can be taken at the time of the initial procedure, e.g., for fabricating a non-circular implant. Additional data curves can also be defined by measuring the offsets from the reference axis 20 A and determining diameters at these offsets. The final implant geometry, although measured using circular techniques, need not be circular.
- a second procedure is performed. If a cover 30 (or plug) is in place, it is removed, exposing proximal extension 14 (or recess) or some other precision taper or engagement surface located at the proximal end 17 of the fixation screw 10 to which the implant 40 is to be affixed.
- a pin having a distally mounted element or barb 5 is placed through through hole 16 running through the central lumen of the fixation screw 10 so that the distally mounted element 5 is secured into the screw.
- the distally mounted element 5 carries one or more suture strands 85 that now trail from the fixation screw 10 .
- a pin, braided cable, or flexible wire may also be used. However, sutures may make passing the implant 40 through the incision 200 and subsequent handling easier.
- the sutures 85 are then threaded through guide aperture 46 of the implant 40 and a knot or bead 49 may be created proximal to the implant, so that tensing one of the free running sutures 85 helps to advance the implant 40 toward the proximal extension 14 (or recess) of the fixation screw 10 .
- the suture strands 85 can be passed through the central lumen or shaft of a driving rod or other instrument to aid in seating the implant 40 , and positioned in the fixation screw 10 thereafter.
- the arthroscopic wound 200 is expanded slightly in either a vertical or horizontal direction, so that the implant 40 may be passed through.
- a polymeric sleeve (not shown) positioned over the implant may prove helpful in passing the implant through the incision.
- FIG. 11 b based on the size of the implant 40 , anatomy of the knee 50 , and retraction of the knee, it may be necessary to position the implant in the interchondular notch 77 as a staging area prior to final placement. By continuing to manipulate and tension the suture strands 85 , the implant 40 can be brought coaxial to the proximal extension 14 of the fixation screw 10 .
- driver 130 includes handle 110 , a cannulated shaft 111 that extends through the handle and a cannulated seat portion 131 attached to the end of the shaft.
- Tether element 135 which may comprise sutures or wire, is passed through driver 130 and is threaded through implant 40 through guide aperture 46 , connecting the implant to the driver toward seat portion 131 .
- the implant 40 and the driver 130 are then inserted arthroscopically through incision 200 to the target site.
- tensioning tether element 135 at the end 136 of handle 110 the implant 40 is drawn back into seat portion 131 of driver 130 .
- the implant 40 can then be controllably delivered to the prepared target site.
- At least the inner surface of seat portion 131 comprises a material that can be impacted to seat the implant 40 without damaging the implant surface.
- the implant 40 can be aligned via engagement of the proximal extension 14 on fixation screw 10 and precisions taper 44 on the bottom surface 42 of the implant and any locating feature, and driven into place with a plastic driving rod 91 and mallet 95 .
- a protrusion 92 of high strength material mounted at the distal tip 93 of the driving rod 91 may be necessary to ensure that the rod stays centered on the implant 40 during driving.
- bone cement 300 may be injected to enhance the contact surface between the implant 40 and the subchondral bone 100 .
- Vents, such as milled slots 13 in the fixation screw 10 , and in the walls of the implant central protrusion may be desirable to facilitate the flow of such materials.
- guide aperture 46 in the implant 40 may be altogether eliminated by using an alternative implant delivery system, as shown in FIGS. 19 d through 19 i, corresponding to an implant similar to that shown in FIGS. 5 c and 5 d .
- the alternative system comprises the implant 40 ′′ and a washer 361 for holding a suture 363 , the washer 361 being adapted to fit into a taper lock ring 360 .
- the ring 360 has a taper lock portion 362 having a series of notches 365 along its perimeter, creating flaps 372 that permit the taper lock portion 362 to flex somewhat.
- the taper lock portion 362 has a diameter gradually tapering from the middle to the proximal end 364 of the ring.
- the taper lock ring 360 may also have an alignment notch 386 or similar feature for properly aligning the taper lock ring 360 with respect to key-shaped portion 344 of the implant 40 ′′, which is to engage with a reciprocal key-shaped surface in the proximal extension of a fixation screw, so as to seat properly the implant rotationally with respect to the defect site when it is later seated thereon.
- a washer 361 is disposed between the ring 360 and the implant 40 ′′ and has two apertures 366 disposed in a recessed area 367 in the center of the washer.
- the suture 363 is threaded through the two apertures 366 to form a suture loop 368 , which remains in the recessed area when the ends of the suture 363 are pulled, so as to keep the suture loop 368 below the top surface 369 of the washer 361 .
- the implant 40 ′′ has a diameter at its center portion 370 that is approximately equal to the inner diameter of the ring 360 at its taper lock portion 362 .
- the taper lock portion 362 of the ring 360 may flex outward to receive slidably therein the implant 40 ′′ and washer 361 , which subsequently lock into the taper lock portion 362 of the ring, once the center portion 370 of the sides of the implant 40 ′′ is seated within the proximal end 364 of the ring by friction fit, as shown in FIG. 19 e . It is noted that the center portion 370 of the sides of the implant 40 ′′ to be of a width permitting the implant and washer to travel slidably within the ring 360 to some degree.
- a hex nut 373 may be integrally formed in the center of the washer 361 on its bottom side 374 , for mating with an appropriately configured tool for seating the implant 40 ′′.
- the implant 40 ′′, along with washer 361 , ring 360 , and sutures 363 is pushed through the incision 200 at the defect site.
- a seating tool 380 may be used to seat the implant.
- Seating tool 380 comprises a shaft 385 , a handle 381 (which may have a through hole 382 , if the same handle and/or shaft is used with interchangeable tips for performing various functions, although a through hole 382 is not integral to seating the implant), and tip 383 suitably configured to drive hex nut 373 (or other mating feature) and having an aperture 384 through which the ends of the suture 363 may be threaded.
- the sutures 363 may be used as a guide for seating the tip 383 of the tool 380 onto the hex nut 373 , which may be accomplished by alternately pulling on each end of the suture 363 to toggle the tip 383 of the tool 380 back and forth.
- the tool 380 may be rotated in either direction to seat the implant assembly properly (comprising implant 40 ′′, taper lock ring 360 , and washer 361 ) at the defect site.
- This may be effected by rotating tool 380 until alignment notch 386 and corresponding key-shaped portion 344 of the implant 40 ′′ are aligned with the corresponding reciprocal key-shaped surface in the proximal extension of the fixation screw, whereby the implant should slide into place, thereby properly seating the implant rotationally with respect to the defect site.
- the implant 40 ′′ can be driven into place with a plastic driving rod 91 and mallet 95 , and as shown in FIG. 13 with respect to the prior described embodiment, bone cement 300 may also be placed prior to the final seating of the implant 40 ′′ to enhance the contact surface between the implant 40 ′′ and the subchondral bone 100 .
- taper lock ring 360 , washer 361 , and sutures 363 described with respect to this embodiment allow the implant to be noncannulated but still easily handled.
- These elements are not required to be constructed as illustrated herein, and may be replaced by adhesive components, suction components, or other components serving the same function.
- a unitary (one-piece) implant 400 may also be constructed, thereby obviating the need for a fixation screw, taper lock ring, washer, and suture.
- implant 400 has key-shaped portion 401 for engagement with a reciprocal key-shaped surface 411 in an aperture 412 at the defect site 410 , a plurality of barbs 402 (or other mating features, e.g., one or more threads, ribs, fins, milled slots, tapered distal features, features to prevent rotational movement of the implant, or features to increase friction between the implant and the aperture at the defect site) for producing outward tension within the aperture 412 at the defect site 410 and for increasing the contact surface area of the implant 400 with respect to the aperture 412 at the defect site 410 .
- an aperture 412 having a key-shaped surface 411 or other feature for mating with the implant is created directly in the defect site 410 , by boring, abrasion, or other techniques for forming an appropriately shaped aperture in the chondral bone 410 for receiving an implant 400 having a corresponding key-shaped or other mating feature 401 .
- the fixation screw could be replaced with a tensioned member attachment, e.g., anchored to the distal femoral cortex.
- the fixation screw could be configured as a guide wire, only to define the axis AA corresponding to an axis about the point of origin in the implant to be used (as shown in FIGS. 14 c and 19 c ), but not to provide mechanical anchoring to or for the implant.
- FIG. 23 illustrates other alternative embodiments for an implant consistent with the invention, showing a perspective view of the components of an exemplary composite implant, in one embodiment of the present invention.
- implant 500 comprises top 501 and bottom 502 portions.
- Top portion 501 has a bottom surface 503 which may be glued, welded, bonded, or otherwise attached to top surface 504 of bottom portion 502
- bottom surface 505 of bottom portion 502 comprises the patient geometry and is the load-bearing surface of the implant, as set forth hereinabove.
- Top 504 and bottom 505 surfaces of the bottom portion 502 may comprise, in whole or in part, bioengineered material, while top portion 501 may comprise a material such as titanium.
- top portion 501 may be fabricated and/or manufactured (e.g. in large quantities) as a universal, generic, standard supply item for medical practitioners, which merely needs to be attached to a custom-machined bottom portion 502 comprising the patient-specific geometry.
- Surfaces 503 and 504 may be flat or may comprise other mating features, shapes or configurations.
- implant 600 comprises the patient-specific geometry 603 and a uniform thickness material bottom portion 602 comprising the bottom or bearing surface 606 .
- the bottom surface 603 of top portion 601 mates with the top surface 604 of bottom portion 602 , and surfaces 603 and 604 may be flat or may comprise other mating features, shapes or configurations.
- Lip 605 of bottom portion 602 has an inside diameter substantially the same as the outside diameter of top portion 601 , so that top portion 601 fits slidably into bottom portion 602 , whereby the two portions 601 and 602 may be glued, welded, bonded, or otherwise attached to one another.
- Bottom surface 606 being of uniform thickness, reflects the patient-specific geometry which surface 603 comprises and is the load-bearing surface of the implant.
- Ceramic e.g. aluminum oxide or zirconium oxide
- metal and metal alloys e.g. Co—Cr—W—Ni, Co—Cr—M, CoCr alloys, CoCr Molybdenum alloys, Cr—Ni—Mn alloys, powder metal alloys, 316L stainless steel, Ti 6Al-4V ELI
- polymers e.g., polyurethane, polyethylene (wear resistant and cross-linked), thermoplastic elastomers
- biomaterials e.g. polycaprolactone
- diffusion hardened materials e.g. Ti-13-13, Zirconium and Niobium.
- Coatings used may include, e.g., porous coating systems on bone-contacting surfaces, hydrophilic coatings on load-bearing surfaces, hydroxyapatite coatings on bone-contacting surfaces, and tri-calcium phosphate on bone-contacting surfaces. Additionally, components of the invention may be molded or cast, hand-fabricated, or machined.
- measurement methods may be utilized whereby radius measurements are taken with respect to an axis AA corresponding to an axis about the point of origin in the implant to be used (as shown in FIGS. 14 c and 19 c ).
- the technique is used in reverse, whereby aiming devices are used to place axis AA with respect to prefabricated generic-geometry implants.
- multiple reference axes may be used for measuring, mapping, or cutting a single defect or an articular surface having multiple defects, as well as for fabricating a single implant, or multiple implants for a single articular surface, consistent with the invention.
- methods for mapping the defect and/or articular surface other than those described hereinabove are possible, e.g., MRI or CT scanning, fluoroscopy, ultrasound, bone density, other stereotactic systems, nuclear medicine, or other sound or light wave-based imaging methods.
- FIGS. 27 a - 48 depict another exemplary embodiment of the present invention.
- a generic bone implant or set of standardized implants
- a generic cutting tool is used to cut the bone at this site to a point where a generic implant can be used.
- FIG. 27 a depicts an exemplary drill guide device 700 according to this exemplary embodiment.
- the guide 700 includes a contact surface 702 of known diameter d on the distal end 708 of the guide, where diameter d is generally the width of the widest portion of the site of the lesion.
- the distal end 708 of the guide is generally a hollowed-out toroidal structure attached to a handle 706 .
- a central lumen 704 runs the length of the guide from the attachment point of the distal end 708 to the handle 706 , and through the handle 706 .
- the guide device may be constructed in a number of other ways, including, e.g., a distal end 708 comprising a transparent material, e.g., polycarbonate or another clear plastic.
- a guide device 700 ′ may comprise a distal end 708 ′ (which could comprise either an opaque or a transparent material) having a plurality of cutaway areas 743 to improve visibility and the accuracy of drill location with respect to the site of a lesion.
- the guide device may also comprise a tripod-like construction, or other construction comprising fins, or projections. It should be noted that, instead of a central lumen being used to locate the working axis, a cylindrical bore located at some distal location of the guide may serve to create a working axis that is not necessarily coaxial to the handle or connecting shaft of the instrument.
- the present embodiment operates on the assumption that to a first approximation an anatomical model of some articular surfaces (e.g., knee, hip, etc.) can be assumed to be locally spherical.
- the AP plane and ML plane are depicted, wherein each corresponds to a model of the articular surface of a femoral region.
- These figures break up these cross-sections into a plurality of radii of arcs defining the articular surface, i.e., R 1 -R 4 in the AP plane, and R 5 -R 7 in the ML plane.
- the inventors herein have found that surfaces in some regions can be assumed to be substantially locally spherical.
- the present embodiment assumes that R 3 approximately equals R 6 (i.e., R 3 is within 50% of R 6 ). Under these assumptions, a normal axis can easily be developed. Once developed, one data point then needs to be defined to obtain the relevant geometry of an implant, as will be described below. If R 3 is not within 50% of R 6 , an alternative method for developing an axis normal to the surface of the lesion site, as described hereinbelow with reference to FIGS. 49-53 , may be used.
- FIGS. 29-34 depict the use of the drill guide, the generic implant, and procedures therefor, according to this exemplary embodiment.
- the drill guide 700 is brought up to a lesion site 712 of the articular surface 710 .
- the guide 700 is positioned so that the distal end 702 covers the lesion site 712 , such that the contact surface of the distal end 702 makes contact at a plurality of points around the lesion site 712 on the articular surface 710 .
- FIG. 30 with slight pressure the guide 700 becomes stable and fixed on the articular surface 710 .
- a guide pin 714 is driven through the central lumen of the guide to create a working axis that is generally normal to the articular surface 710 at the point of contact of the guide pin.
- a standard bore drill (not shown) can be placed over the guide pin 714 to create a pilot hole 716 for the screw (not shown).
- a screw 720 is driven into the pilot hole 716 .
- a cap 722 having a male component 719 adapted to mate with the female taper 718 of the screw 720 is placed on the screw 720 .
- the screw is driven to the appropriate depth, such that the top surface of the cap 722 is substantially aligned with the articular surface 710 , within the lesion site 712 , thereby ensuring congruency of the implant to the joint.
- FIG. 33 the cap 722 is removed, and a rod 730 having a mating taper 731 on its distal tip is inserted into the screw 720 .
- the guide 700 is positioned over the rod 730 so that the distal end 702 covers the lesion once again.
- a measurement of the exposed end length of the rod (l) may be taken. This will provide the information needed with respect to the implant geometry, by indicating the distance between the seating depth in the screw and the tangent point of the implant surface.
- the axis, z is defined (by the drill guide) as normal to the surface of the implant at a plurality of points, all dimensions defining the AP and ML curves may be assumed to be equal, such that only one dimension, l, is left to define the implant geometry.
- Variations from knee to knee and within a knee may be reflected in changes in l.
- the implant 736 of FIG. 36 may be compared to the implant 737 of FIG. 37 .
- the value of l 1 represents a relatively “flat” region on the articular cartilage, where the radius of the arc R AC1 is a relatively large number.
- the value of l 2 represents a more curved region on the articular cartilage, where the radius of the arc R AC2 is a smaller number than R AC1 .
- there is a range of values for l that suggests 5 to 6 values of l that will fit a majority of people.
- generic, off-the-shelf sized implants may be made. A single procedure technique involving establishing the normal axis, measuring l, and selecting the appropriate size implant is therefore feasible.
- an exemplary cutting or reaming tool 740 (e.g., as described hereinabove with respect to FIGS. 15 b and 16 ) is used to prepare the lesion site 712 to receive the implant (not shown).
- the cutting or reaming tool 740 may be configured so that, when coupled to the axis defined by the guide pin, it can be used for cutting operations.
- the tool 740 may have a cannulated shaft and a distal offset arm having a cutting or blade surface (not shown) having a radius corresponding to the radius of the implant to be used, such that the articular cartilage may be circumscribed by rotation of the tool 740 for cleanly cutting the surrounding articular cartilage in preparation for receiving the implant.
- the tool 740 may be configured so that, when coupled to the axis defined by the guide pin, it can be used for cutting operations.
- the proximal face of the screw 720 may serve as a depth stop for the proximal portion of the tool 740 , thereby defining a cutting/reaming depth corresponding to the thickness of the implant, l.
- an exemplary cutting tool 744 may comprise a cannulated shaft 749 , a circular blade portion 745 having a leading edge 746 comprising a blade surface turned on the distal-most portion.
- Such a tool 744 may further comprise a handle portion 747 and may be adapted to be turned by hand by the operator of the tool by means of rotating the handle 747 , or alternatively, may be motorized in certain embodiments.
- FIG. 40 illustrates an exemplary cleaning tool 770 for cleaning the female taper (not shown) of the screw 720 prior to delivery of the implant.
- the distal end 771 of an exemplary cleaning tool 770 comprises a semi-rigid material formed into a shape adapted to enter into the female taper of the screw 720 and be manipulated by the operator of the tool, to remove tissue or other debris therefrom, thereby ensuring a good mate of the female taper 720 of the screw and the male taper of the implant to be delivered (not shown).
- FIGS. 41-43 illustrate an exemplary suction tool 760 for holding the implant by means of a suction force and delivering it to the lesion site, as well as the steps of an exemplary procedure for using the suction tool 760 to deliver an implant.
- an exemplary suction tool 760 comprises an elastomeric suction tip 761 at its distal portion 767 , a proximal surface 768 , an inlet 762 for mating with a suction tube 763 connected either to a hospital wall suction supply 764 or other suction system, and a switch or valve 765 for controlling the suction force.
- FIG. 41 illustrates an exemplary suction tool 760 for holding the implant by means of a suction force and delivering it to the lesion site, as well as the steps of an exemplary procedure for using the suction tool 760 to deliver an implant.
- an exemplary suction tool 760 comprises an elastomeric suction tip 761 at its distal portion 767 , a proximal surface 768 , an
- the distal portion 767 of an exemplary suction tool 760 may comprise a rigid tip 766 (which may comprise, e.g., plastic material) disposed within the elastomeric suction tip 761 .
- Force may be applied to the rigid tip 766 (e.g., by striking or pressing on the proximal surface 768 of the tool 760 ) in order to seat the implant 742 within the lesion site, once the male taper 769 of the implant 742 and its corresponding mating component(s) 778 are properly aligned with the female taper of the screw (not shown) and its corresponding mating component(s). Since the suction tip 761 is elastomeric (e.g., rubber), upon application of such force, the material will compress, allowing impact to be transferred to the implant 742 for purposes of seating it.
- elastomeric e.g., rubber
- a suction tool 760 as described herein might also be used at some point during the process of removing an implant (e.g., in the event the implant is not fully seated).
- FIG. 44 illustrates an exemplary implant 742 driven into the lesion site 712 of the articular surface 710 once the site 712 has been sufficiently reamed or cut.
- FIG. 45 illustrates an exemplary implant removal or revision tool 750 comprising a shaft portion 751 and a distal portion 753
- FIG. 46 is a cross-sectional view illustrating the exemplary tool 750 with a removed implant 742 being held in place therein.
- the distal portion 753 of the tool 750 may comprise an approximately cylindrical structure with a circular blade portion 752 having a leading edge 758 comprising a blade surface turned on the distal-most portion and a lip portion 755 disposed proximally with respect to the leading edge 758 .
- a plurality of slits 754 parallel to the longitudinal central axis of the distal portion 753 are disposed along the length of the cylindrical structure, so as to permit sufficient outward expansion of the distal portion 753 to accommodate the top edge of the implant 742 therein.
- a device such as a slap-hammer or slide hammer (not shown) may be used to unseat the implant 742 .
- An exemplary such device may comprise a shaft having a weight slidably disposed thereon, wherein one end of the shaft is connected to the proximal end (not shown) of the tool 750 and the other end of the shaft comprises a stop for preventing the weight from moving off the shaft, and wherein the weight is propelled away from its connection point with the proximal end of the tool 750 , such that it stops abruptly at the stop and exerts a pulling force on the implant.
- FIGS. 47 and 48 illustrate an exemplary alternatively-keyed embodiment of the screw 720 ′ (c.f., key feature 315 of screw 10 ′, as shown in FIG. 9 c ) and the exemplary alternatively-keyed implant 742 ′ to which it is adapted to mate.
- the male taper 769 ′of the implant 742 ′ is coupled at its distal end to an offset mating feature 778 ′ for mating with a corresponding offset mating feature 779 of the screw 720 ′.
- the mating feature 778 ′ of the implant 742 ′ comprises a generally cylindrical structure (and may further comprise a rounded or chamfered distal end portion 777 ′ and/or other geometric features, i.e., recesses and/or protrusions) and is both offset from the central longitudinal axis of, and diametrically smaller than, the male taper 769 ′ of the implant 742 ′.
- a rounded or chamfered distal end portion 777 ′ and/or other geometric features, i.e., recesses and/or protrusions is both offset from the central longitudinal axis of, and diametrically smaller than, the male taper 769 ′ of the implant 742 ′.
- a generally cylindrical recessed mating feature 779 (or similar mating recess(es) and/or protrusion(s), e.g., a rounded or chamfered distal end portion 780 ) corresponding to the offset distal mating feature 778 ′ of the implant 742 ′ is disposed within the innermost portion of the female taper 718 ′ of the implant 742 ′, and offset from the central longitudinal axis of the female taper 718 ′.
- the female mating feature 779 of the screw is provided to mate with the offset male distal mating feature 778 ′ of the implant 742 ′, so as to seat the taper 769 ′ of the implant 742 ′ at a fixed location within the screw 720 ′, thereby preventing rotation of the implant 742 ′ with respect to the screw 720 ′.
- the taper structures provided may serve to prevent movement of the implant 742 ′ with respect to the screw 720 ′in all directions.
- a screw 720 ′ consistent with the present invention may comprise a titanium alloy, e.g., a 316L stainless steel alloy or a cobalt-chrome alloy.
- FIGS. 49-53 illustrate an alternative method for developing an axis normal to the surface of the lesion site using a biaxial measuring tool.
- This method has particular utility for lesion sites where the radii of arcs defining the articular surface, R ML and R AP , are different, i.e., the region is not locally spherical. (This would be the case, e.g., if R 3 is not within 50% of R 6 , as illustrated in FIGS. 29 a and 29 b and described hereinabove.)
- a biaxial measuring tool 800 is provided to develop an axis normal to the surface.
- the tool 800 comprises an outer shaft 805 coupled fixedly to an outer component 801 having a set of arms 803 , and an inner shaft 806 slidably disposed within the outer shaft 805 , wherein the inner shaft is coupled fixedly to an inner component 802 having a set of arms 804 .
- the arms 803 , 804 of the outer 801 and inner 802 components may take several forms, and one exemplary form for the arms 803 , 804 is illustrated in FIGS. 49-53 , wherein the distal portion of each arm 803 , 804 tapers outward and connects to one of four contact portions 808 .
- the contact portions 808 may be, e.g., as shown, one of four arcuate sections of a generally toroidal member (which may be solid or hollow) having a generally circular cross-section. (The lengths of the arcuate sections do not necessarily need to be equal to one another, e.g., as illustrated in the exemplary contact portions 808 of FIGS. 49-53 , the arcuate lengths of the contact portions 808 corresponding to the inner component 802 are shorter than those contact portions 808 corresponding to the outer component 801 .)
- the inner shaft 806 may be biased forward so as to tend to extend from the outer shaft 805 , or may alternatively be advanced manually without spring bias.
- the inner component 802 is slid proximally or distally with respect to the outer component 801 , until all of the contact portions 808 make contact with the articular surface (not shown).
- the articular surface curvatures may be separated into AP elements and ML elements, such that four separate contact points may be extrapolated from the four contact portions 808 , based on the relative positions of the inner 802 and outer 801 components, and an axis normal to the surface of the lesion site may be defined.
- the shaft of the tool 800 may be cannulated (not shown), so as to allow a guide pin or wire (or a boring tool) to pass therethrough and into the articular surface, as described hereinabove with respect to FIGS. 27 a to 31 .
- the articular surface must be locally spherical, i.e., R ML and R AP (as shown in FIG. 49 ) are equal, and it is therefore not necessary to use the biaxial tool 800 .
- contact surfaces may be constructed of some pliable, or malleable material(s) so that independently moving rigid mechanical members are not necessary. As long as the contact surfaces provide a normalizing force to some central shaft when the contact surfaces are applied to the articular surface, a normal axis could be defined.
- this biaxial guide could be replaced by a series of sized “trials” or gauges of predefined surfaces of varying dimensions, which are simply pressed onto the articular surface to visually determine an appropriate fit.
- These gauges may resemble an implant, as described herein, without any features (e.g., fixation element or screw) on the underside, and may contain a handling tab or other element for holding the gauge.
- the contact surfaces of these gauges may have a circular cross section, an ovular cross section, or another cross-section comprising a plurality of points to surround a defect in an articular surface, and the plurality of points may or may not lie in the same plane. Although they may be less precise or less accurate than other measuring methods described herein, it is contemplated that implant selection could be made directly from these gauges.
- FIGS. 54-61 illustrate an exemplary digital measuring system consistent with the present invention.
- the system 810 comprises a base unit 811 coupled to the handpiece 812 via a cable 813 .
- the base unit 811 may comprise a tear strip 814 in or on the chassis for detaching a printed paper tape comprising measurement data.
- Such a system may reduce or eliminate potential for surgical or other human error with respect to the implementation of the present invention.
- FIG. 55 is an exploded view of an exemplary handpiece 812 in a digital system consistent with the present invention.
- the linear measuring elements of the handpiece 812 are nested concentrically and coaxially to the rotary measuring elements, so that when the probe assembly 818 is translated and rotated with respect to the main body 822 of the handpiece, the ⁇ and z dimensions are simultaneously recorded.
- the handpiece 812 comprises a main body 822 containing a linear reading head 813 coupled to a linear reader 814 , a linear index strip 815 , a rotary reading head 821 coupled to a rotary reader 816 , and a rotary index strip 817 .
- the probe assembly 818 comprises a contact tip 819 coupled to an inner shaft 820 running along the length of the handpiece 813 disposed within the main body 822 .
- the shaft 820 comprises a mating feature 834 at its distal end that is keyed to fit in the mating feature of an implanted screw, such that the shaft 820 provides a rotational axis.
- the shaft 820 is rigidly connected to the main body 822 of the handpiece 812 via a nut 823 at its rear.
- the handpiece 813 is coupled to, and transfers motion both rotationally and axially from, the contact tip 819 via the shaft 820 .
- the linear 815 and rotary 817 strips which may comprise, e.g., mylar polyester film having thereon a very fine printed pattern, pass through the linear 813 and rotary 821 reading heads, respectively, such that the heads 813 , 821 read the pattern on the strips 815 , 817 and output data representing the rotational and axial travel of the contact tip 819 .
- Exemplary strips and heads may include those manufactured by U.S. DigitaTM Corporation of Vancouver, Wash., USA.
- FIG. 55 a is a cutaway view illustrating an exemplary printed linear index strip 815 passing through an exemplary linear head 813 for reading
- FIG. 55 b is a cutaway view illustrating two alternative exemplary printed rotary index strips 817 , 817 ′ of varying sizes passing through an exemplary rotary head 821 for reading.
- FIG. 55 c illustrates an exemplary linear index strip 815 comprising concentric “bullseye” circles 830 , reference lines 831 , a text area 832 , and a pattern area 833 .
- 55 d illustrates an exemplary rotary index strip 817 comprising an opaque area 823 , index areas 824 , a pattern area 825 , a text area 826 , crosshairs 827 , concentric “bullseye” circles 828 and a central aperture 829 .
- a rotational groove 840 and a linear groove 841 are provided on the handpiece 812 , such that the probe assembly 818 may slide onto the shaft 820 of the handpiece 812 and snap into the linear 841 and rotational 840 grooves.
- FIGS. 57 and 58 illustrate top and side views, respectively, of the assembled exemplary handpiece 812 .
- FIGS. 59 and 60 illustrate top and side cross-sectional views, respectively, of the assembled exemplary handpiece 812 .
- FIG. 61 illustrates a cutaway view of an exemplary base unit 811 in an exemplary digital measuring system consistent with the present invention.
- the base unit 811 comprises a power supply 850 (the system may be battery or AC-line powered), a paper roll 851 , a thermal printer 852 , a feed loop dowel 853 for threading the paper roll 851 into the thermal printer 852 , a set of controls or buttons 854 , and one or more displays 855 (e.g., LED/LCD).
- the base unit 811 further comprises appropriate hardware and/or software to compare measured values to known values, as well as to compare sweeps to one another to ensure procedural accuracy.
- the displays 855 and/or paper printouts from the thermal printer 852 may be adapted to display to the user, based on measured data, the ideal size of the generic implant to use. If a custom implant is required, a printout of the data set may be generated using the printer 852 .
- the base unit 811 may further comprise other means of recording data (not shown), e.g., floppy disk, hard disk, memory/flash card, etc., and may further comprise appropriate hardware to provide output signals (e.g., via RS-232, USB, etc.) to external hardware.
- other digital measurement methods may be used, including reflective light or sound methods, and percutaneous methods (e.g., using a hypodermic needle in conjunction with an MRI, CT, ultrasound, or other scanning method, wherein the needle or other handheld device comprises sensing elements for mapping the articular surface).
- a second (or third, etc.) set of data points may be taken, and the subsequent set(s) of data points compared with the original data points taken, to reduce the margin of error from taking only a single set of data points.
- a software algorithm in a system or method consistent with the invention may comprise appropriate routines to effect such comparisons, for error reduction purposes.
- FIG. 62A a top perspective view of an alternative exemplary implant 6200 that includes a protrusion 6204 that extends at least partially around the periphery of the device.
- the protrusion 6204 is provided to cover at least a portion of an un-excised portion of articular surface, however, this is not a structural requirement of the device of the present embodiment.
- the protrusion 6204 may surround the entire circumference of the implant 6200 and may extend radially outward from the center point P of the implant 6200 .
- the protrusion may be selectively placed around portions of the perimeter of the implant.
- the implant 6200 may include a radial ring 6220 formed on the bone-facing distal surface of the implant 6200 .
- the radial ring may be dimensioned to the excised portion such that the arcuate shaped outer side surface 6223 defines the size of the cut portion in the articular surface.
- the radial ring 6220 may have a width r 4 in a radial direction from the center point P of the implant 6200 and a height h 1 in the z-axis direction.
- the arcuate shaped outer side surface 6223 of the radial ring 6220 may be a radial distance r 1 from the center point P of the implant 6200 .
- the radial ring 6220 may also include a plurality of radial slots 6224 spaced evenly along the circumference of the ring in order to assist with anchoring of the implant to the bone.
- FIG. 62B a cross-sectional view of the implant 6200 taken along the line B-B of FIG. 62A is illustrated.
- the radial ring 6220 is positioned relative to the center point P as it would be with other such implants earlier described, e.g., the circular implant illustrated in FIGS. 25 and 26 .
- the protrusion 6204 is formed by an extension 6206 from the radial ring and an extension 6232 of the load bearing proximal surface. These extensions join at 6214 to define the protrusion 6204 .
- the top or proximal surface 6232 of the protrusion 6204 may simply be an extension of the proximal or load bearing surface 6205 of the implant 6200 . As such, the protrusion 6204 extends beyond the outside arcuate edge 6223 of the radial ring 6220 . Accordingly, the protrusion 6204 has a width r 3 at any one point along the perimeter of the implant 6200 equal to the difference between the radial distance r 2 from the center point P of the implant to the exterior edge 6214 of the protrusion 6204 and the radial distance r 1 from the center point P of the implant to the outside arcuate edge 6223 of the radial ring 6220 . The width r 3 of the protrusion may be a consistent width around the entire perimeter of the implant or may vary along the perimeter as conditions of the proximate articular cartilage vary.
- the protrusion 6204 is also defined by a bone-facing or distal surface 6206 that may extend to cover a portion of the un-excised articular surface 6218 .
- the distal surface 6206 of the protrusion 6204 may be shaped in any number of ways to match the mating edge of the articular surface 6218 proximate to the distal surface 6206 of the rim 6204 . As illustrated in FIG. 62B , the distal surface 6206 may have an arcuate shape for this purpose.
- FIG. 62C a side perspective view of the implant 6200 is illustrated.
- the protrusion 6204 may be advantageously configured to follow the mapped contour of the mating articular surface, e.g., articular cartilage.
- the distal surface 6206 of the rim 6204 may vary along the perimeter of the implant in order to match the edge of the articular cartilage which it covers based on mapping configurations as previously detailed herein.
- FIG. 63A a side perspective view of another alternative embodiment of an implant 6300 is illustrated.
- the implant 6300 includes a protrusion 6304 with protuberances 6312 a , 6312 b , 6312 c , and 6312 d formed at selected locations along the periphery of the protrusion 6304 , and may be used, for example, to secure the target articular surface proximate to the distal surface 6306 of the protrusion 6304 .
- the protuberances 6312 a , 6312 b , 6312 c , and 6312 d may be any variety of shape or geometry and are preferably spaced equal distances around the outside perimeter of the protrusion 6304 .
- the protuberances may also have barbs or teeth (not shown) to enhance grip to the articular surface.
- the interface between the implant 6300 and a fixation device, e.g., a screw may need to be revised in order to allow more axial range of forgiveness for interlock of the protuberances to the articular cartilage.
- FIG. 63B a cross-sectional view of the implant 6300 taken along the line B-B of FIG. 63A is illustrated.
- the protuberances 6312 a , 6312 d couple to the distal portion 6306 of the rim 6304 in order to more securely couple the protrusion 6304 to the un-excised portion of the articular surface 6318 proximate to the implant 6300 .
- FIG. 64A another alternative embodiment of an implant 6400 is illustrated.
- the proximal or load bearing surface 6405 has a perimeter edge 6406 that is configured to be separated a predetermined radial distance r 5 from a surrounding articular surface 6418 when the implant is properly seated in a patient.
- a cavity 6428 or trough defined by a bottom cavity surface 6408 , a side cavity surface 6406 , and the cut side of articular surface 6418 is formed.
- FIG. 64B a cross sectional view of the implant 6400 of FIG. 64A taken along the line B-B is illustrated which further shows the details of such a cavity 6428 .
- the articular cartilage 6418 may then settle or remodel into the cavity 6428 .
- One side 6406 of the cavity 6428 may be arcuate shaped and may be depressed a predetermined distance relative to the load bearing surface 6405 .
- the dimensions of the cavity may be large enough to permit sufficient space for the articular cartilage 6418 to remodel or settle into such cavity, but small enough so that articular cartilage 6418 may remodel into such space within a reasonable time frame after seating of the implant 6400 .
- FIG. 65A another alternative implant 6500 embodiment consistent with the invention is illustrated.
- This implant 6500 has a non-round or elongated shape.
- the concept behind this geometry of the implant is to provide extension of the implant in the AP plane without being constricted by the width of the condyle.
- the implant of this embodiment may be derived from a circular implant that has a radius that extends beyond the width of the condyle in the ML plane.
- the circular implant structure may then be truncated along the “sides” that form the edges of the condyle in the ML plane, thus forming the elongated implant depicted in FIG. 65A .
- the implant 6500 has a least two side surfaces 6517 , 6519 each having a concentric arcuate shape with a common center. As with implants described previously herein, the implant 6500 has an arc Arc AP and an arc Arc ML that represent the curvature of the proximal surface 6505 of the implant 6500 .
- the implant 6500 has a length from an anterior end of the implant to a posterior end of the implant along a segment of the arc Arc AP .
- the implant also had a width from the medial end of the implant to the lateral end of the implant along a segment of the arc Arc ML .
- the arc segment in the ML plane is less than the arc segment in the AP plane, for the non-round or elongate shaped implant 6500 .
- the implant 6500 may also have one concentric arcuate shaped side surface 6517 located opposite another concentric arcuate shaped side surface 6519 .
- Such side surfaces 6517 , 6519 are concentric with a common center.
- Such side surfaces 6517 , 6519 are also configured to mate with a cut or reamed edge of bone and/or articular cartilage when seating the implant.
- the implant 6500 also has a length 16500 in a plane defined by the maximum distance between two points on the arcuate shaped side surfaces 6517 , 6519 .
- the implant also may also have two other opposing side surfaces 6521 , 6523 .
- Such surfaces 6521 , 6523 are generally flat to where the surface cutter “runs off” of the condyle.
- the distance in a plane between the two side surfaces 6521 , 6523 define the width w 6500 of the implant 6500 . Having such an elongated or non-round implant allows the treatment of a greater variety of articular defects, and may also be effective in reducing fray between the perimeter of the cut articular cartilage and the implant 6500 .
- the implant 6500 may be defined by the ML curve swept along the AP curve as previously described herein.
- the implant may be a generic bone surface implant as previously described with reference to FIGS. 27 a - 48 assuming a locally spherical articular surface site.
- an implant site 6511 may be created by excising a portion of the articular surface 6508 to match the implant 6500 shape of FIG. 65A .
- the implant site 6511 may have two arcuate shaped side surfaces 6531 , 6533 located opposite each other to receive the two arcuate shaped side surfaces 6517 , 6519 of the implant 6500 .
- Two other side surfaces 6535 , 6537 of the implant site are configured to mate with the side surfaces 6521 , 6523 of the implant 6500 .
- the implant site 6511 may be generated a number of ways.
- a reaming or cutting tool 6524 having a circular blade portion 6526 with a blade diameter dblade greater than the width Wsurface of the articular surface 6608 to which the implant will be affixed may be utilized.
- Another exemplary reaming tool 744 is discussed more fully with reference to FIG. 39 .
- the circular blade 6526 of the reaming tool 6524 is depressed into the articular surface 6508 until it contacts the depth stops in the screw as previously described herein.
- a straight line distance dAP is created since the blade diameter dblade is greater than the width Wsurface of the articular surface 6608 .
- This straight line distance dAP in an AP plane is dependent on a number of factors including the depth of the cutout bottom surface 6510 compared to the top or proximal surface 6505 of the implant, and the shape of the surrounding articular surface 6508 to which the implant will be applied.
- the implant site 6511 of FIG. 65B should have a cross sectional view as illustrated in FIG. 65C .
- the cutout bottom surface 6510 will match the undersurface of the implant 6500 .
- FIG. 65D a perspective view of the elongated or non-round implant 6500 being placed into the implant site 6511 of the articular surface 6508 is illustrated.
- the implant 6500 may be placed and set into the implant site 6511 using any variety of tools and methods as previously discussed herein.
- the arcuate shaped side surfaces 6517 , 6519 mate with edges 6531 , 6533 of the implant site on the anterior and posterior side of the implant respectively.
- the other side surfaces 6521 , 6523 abut the edges 6535 , 6537 of the implant site on the medial and lateral side of the implant site.
- These side surfaces 6521 , 6523 may be shaped to match that excised portion of the articular surface on such medial and lateral sides.
- the diameter ⁇ 1 of one measuring probe may be used to define the diameter dblade of a round blade 6526 from a reaming tool 6524 .
- the diameter ⁇ 1 of such a measuring probe may typically be equal to the diameter dblade of the round blade 6526 from a reaming tool 6524 .
- the diameter ⁇ 2 from another measuring probe may defines the ML curve and hence the arcuate width of the implant along that curve.
- FIG. 66A a top perspective view of another alternative exemplary elongated implant 6600 having two protrusions 6605 , 6605 is illustrated.
- the protrusions 6605 , 6606 may prevent fraying of the articular cartilage that abuts the anterior and posterior edge of the elongated implant 6600 when seated in an excised portion of an articular surface.
- Protrusion 6605 is generally similar to protrusion 6606 so for clarity, description herein is made to protrusion 6606 only.
- Protrusion 6606 may extend radially from the arcuate shaped side surface 6623 to cover an un-excised portion 6634 of articular surface 6608 (see FIG. 66B ) proximate to the arcuate side surface 6623 of the implant 6600 .
- the protrusion 6606 has a width r 3 at any one point along the arc of the implant on the anterior side equal to the difference between the radial distance r 2 from the center point P of the implant to the exterior edge 6640 of the protrusion 6606 , and the radial distance r 1 from the center point P of the implant to the outside arcuate side surface 6623 .
- the width r 3 of the rim may be a consistent width around the perimeter of the arc or may vary as conditions of the mating articular cartilage vary.
- the protrusions 6605 , 6606 of the elongated implant 6600 may also have protuberance to more securely affix the rim to the articular cartilage as described and illustrated earlier with reference to FIGS. 63A and 63B .
- FIG. 66B a top perspective view of the elongated or non-round implant 6600 having protrusions 6605 , 6606 being placed into an implant site 6611 of the articular surface 6608 is illustrated.
- the implant 6600 may be placed and set into the implant site 6611 using any variety of tools and methods as previously discussed herein.
- the protrusion 6606 may cover and anchor a portion of the articular cartilage 6634 proximate to the cut edge of the implant site 6611 at the anterior side, while the protrusion 6605 may similarly cover and anchor a portion of the articular cartilage proximate to the cut edge of the implant site 6611 at the posterior side of the implant.
- FIG. 67 a top perspective view of an implant 6700 being placed into a section 6707 of an articular surface 6708 is illustrated.
- the articular cartilage of the articular surface 6708 is not cut. As such, fraying of the articular cartilage at a cut edge may be avoided.
- the implant 6700 is mapped and placed within the borders of the existing defect.
- the portion of the articular surface excised for the implant site has a surface area less than the surface area of the defect.
- one method may include locating the defect in the articular surface, establishing a working axis substantially normal to the articular surface and substantially centered within the defect, excising a portion of the bone surface adjacent to the axis thereby creating an implant site 6711 , and installing the implant in the implant site where a least a portion 6707 , 6709 of the existing defect is exposed around a perimeter of the defect.
- Such a method may require measuring down to the exposed subchondral bone, or measuring the articular cartilage surface in closes proximity to the implant site.
- a portion of the defect 6707 proximate to the posterior side may, of course, have a different shape or configuration as that portion of the defect 6709 proximate to the anterior side of the implant 6700 when seated.
- an implant 6800 consistent with the invention may be provided with a feature to promote and encourage remodeling of the articular cartilage onto the proximal surface 6806 of the implant 6800 .
- a feature may be an indentation in the proximal surface 6806 of the implant that may be of continuous or noncontiguous shape.
- the indentations are continuous grooves 6803 , 6805 , 6807 extending along the proximal surface 6806 of the implant from one side to another.
- Such grooves 6803 , 6805 , 6807 may also be provided with thru holes 6809 to communicate to the bone surface.
- FIG. 68B is a cross sectional view of the implant 6800 taken along the line B-B of FIG. 68A illustrating the square shaped cross sectional geometry of the exemplary grooves 6803 , 6805 , 6807 .
- another indentation of the proximal surface 6806 may be one or more spaces 6832 , 6834 created at the perimeter edge 6830 of the proximal surface 6806 by the particular geometry of the implant's proximal surface 6806 .
- Such edge spaces 6832 , 6834 may also promote and encourage remodeling of the articular cartilage onto the proximal surface 6806 of the implant 6800 .
- FIG. 68D a top perspective view of the implant 6800 seated in an articular surface 6816 is illustrated.
- indentations such as grooves 6803 , 6805 , 6807 and edge spaces 6832 , 6834 may promote remodeling of the articular cartilage such that a portion 6818 of the articular cartilage has extended over the proximal surface 6806 of the implant 6800 .
- This portion 6818 of articular cartilage may only be a superficial layer of cartilage, and may only extend over a portion of the proximal surface 6806 of the implant.
- this remodeling may facilitate load bearing across the transition between the implant 6800 and the surrounding articular cartilage.
Abstract
An implant for installation into a portion of an articular surface includes a protrusion configured to cover an un-excised portion of articular surface proximate to the implant. Another implant may form a cavity to allow the un-excised portion of articular surface to remodel over a perimeter edge of the implant. The implant may also include indentations such as grooves to promote articular cartilage remodeling over a portion of the load bearing surface of the implant. An elongated or non-round implant is also provided having two opposing concentric arcuate shaped sides, as well as a method to seat such an implant in an articular surface. A method for seating an implant without cutting articular cartilage is also provided.
Description
- This application is a continuation application under 37 CFR §1.53(b) of U.S. application Ser. No. 10/760,965 filed Jan. 20, 2004, now U.S. Pat. No. 7,618,462, which is a continuation of U.S. application Ser. No. 10/162,533 filed Jun. 4, 2002, now U.S. Pat. No. 6,679,917, which is a continuation-in-part application of U.S. application Ser. No. 10/024,077, filed Dec. 17, 2001, now U.S. Pat. No. 6,610,067 which is itself a CIP application of U.S. application Ser. No. 09/846,657, filed May 1, 2001, now U.S. Pat. No. 6,520,964 which claims the benefit of U.S. provisional application Ser. No. 60/201,049, filed May 1, 2000, all of which are incorporated herein by reference.
- This invention relates to devices and methods for the repair of defects that occur in articular cartilage on the surface of bones, particularly the knee.
- Articular cartilage, found at the ends of articulating bone in the body, is typically composed of hyaline cartilage, which has many unique properties that allow it to function effectively as a smooth and lubricious load-bearing surface. However, when injured, hyaline cartilage cells are not typically replaced by new hyaline cartilage cells. Healing is dependent upon the occurrence of bleeding from the underlying bone and formation of scar or reparative cartilage called fibrocartilage. While similar, fibrocartilage does not possess the same unique aspects of native hyaline cartilage and tends to be far less durable.
- Hyaline cartilage problems, particularly in knee and hip joints, are generally caused by disease such as occurs with rheumatoid arthritis or wear and tear (osteoarthritis), or secondary to an injury, either acute (sudden), or recurrent and chronic (ongoing). Such cartilage disease or deterioration can compromise the articular surface causing pain and further deterioration of joint function. As a result, various methods have been developed to treat and repair damaged or destroyed articular cartilage.
- For smaller defects, traditional options for this type of problem include non-operative therapies (e.g., oral medication or medication by injection into the joint), or performing a surgical procedure called abrasion arthroplasty or abrasion chondralplasty. The principle behind this procedure is to attempt to stimulate natural healing. At the defect site, the bone surface is abraded, removing approximately 1 mm. or less using a high-speed rotary bun or shaving device. This creates an exposed subchondral bone bed that will bleed and will initiate a fibrocartilage healing response. Although this procedure has been widely used over the past two decades and can provide good short term results, (1-3 years), the resulting fibrocartilage surface is seldom able to support long-term weight bearing, particularly in high-activity patients, and is prone to wear.
- Another procedure, referred to as the “microfracture” technique, incorporates similar concepts of creating exposed subchondral bone. During the procedure, the cartilage layer of the chondral defect is removed. Several pathways or “microfractures” are created to the subchondral bleeding bone bed by impacting a metal pick or surgical awl at a minimum number of locations within the lesion. By establishing bleeding in the lesion and by creating a pathway to the subchondral bone, a fibrocartilage healing response is initiated, forming a replacement surface. Results for this technique are generally similar to abrasion chondralplasty.
- Another known option to treat damaged articular cartilage is a cartilage transplant, referred to as a Mosaicplasty or osteoarticular transfer system (OATS) technique. This involves using a series of dowel cutting instruments to harvest a plug of articular cartilage and subchondral bone from a donor site, which can then be implanted into a core made into the defect site. By repeating this process, transferring a series of plugs, and by placing them in close proximity to one another, in mosaic-like fashion, a new grafted hyaline cartilage surface can be established. The result is a hyaline-like surface interposed with a fibrocartilage healing response between each graft.
- This procedure is technically difficult, as all grafts must be taken with the axis of the harvesting coring drill being kept perpendicular to the articular surface at the point of harvest. Also, all graft placement sites must be drilled with the axis of a similar coring tool being kept perpendicular to the articular surface at the point of implantation. Further, all grafts must be placed so that the articular surface portion of these cartilage and bone plugs is delivered to the implantation site and seated at the same level as the surrounding articular surface. If these plugs are not properly placed in relation to the surrounding articular surface, the procedure can have a very detrimental effect on the mating articular surface. If the plugs are placed too far below the level of the surrounding articular surface, no benefit from the procedure will be gained. Further, based on the requirement of perpendicularity on all harvesting and placement sites, the procedure requires many access and approach angles that typically require an open field surgical procedure. Finally, this procedure requires a lengthy post-operative non-weight bearing course.
- Transplantation of previously harvested hyaline cartilage cells from the same patient has been utilized in recent years. After the cartilage is removed or harvested, it is cultured in the lab to obtain an increase in the number of cells. These cells are later injected back into the focal defect site and retained by sewing a patch of perio steal tissue over the top of the defect to contain the cells while they heal and mature. The disadvantages of this procedure are its enormous expense, technical complexity, and the need for an open knee surgery. Further, this technique is still considered somewhat experimental and long-term results are unknown. Some early studies have concluded that this approach offers no significant improvement in outcomes over traditional abrasion and microfracture techniques.
- U.S. Pat. No. 5,782,835 to Hart et al. discloses an apparatus and method for repair of articular cartilage including a bone plug removal tool, and a bone plug emplacement tool. The method of repairing defective articular cartilage includes the steps of removing the defective cartilage and forming a hole of sufficient depth at the site. A bone plug comprising intact bone and cartilage adhering thereto is removed from a bone lacking defective cartilage is placed in the hole at the site of the damage.
- U.S. Pat. No. 5,413,608 to Keller discloses a knee joint endoprosthesis for replacing the articular surfaces of the tibia comprising a bearing part which is anchored on the bone having an upper bearing surface and a rotatable plateau secured on the bearing surface and forming a part of the articular surface to be replaced. A journal rises from the bearing surface and cooperates with a bore in the plateau to provide lateral support.
- U.S. Pat. No. 5,632,745 to Schwartz describes a method of surgically implanting into a site a bio-absorbable cartilage repair assembly. The assembly includes a bio-absorbable polygonal T-shaped delivery unit having radial ribs to be mounted in the removed area and a porous bio-absorbable insert supported by and in the delivery unit. The method comprises the steps of preparing the site to receive the assembly by removing a portion of the damaged cartilage and preparing the site to receive the assembly by drilling and countersinking the bone. The assembly is inserted and seated using an impactor in the drilled and countersunk hole in the bone until the assembly is flush with the surrounding articular surface.
- U.S. Pat. No. 5,683,466 to Vitale illustrates an articular joint surface replacement system having two opposing components. Each component has a tapered head piece for covering the end of a bone and for acting as an articular surface, an integrally formed screw stem of sufficient length to extend into the bone and inwardly angled bone grips on the underside of the head piece to allow fixation to the bone by compression fit. The partially spherical convex shaped exterior of the first component complements the partially spherical concave shaped exterior of the second component.
- U.S. Pat. No. 5,702,401 to Shaffer discloses an intra-articular measuring device including a hollow handle defining a first passageway and a hollow tube having a second passageway extending from the handle, the hollow tube carrying a projection at its distal end for seating on a fixed site and a probe disposed at the distal end of the hollow tube which may be directed to a second site, to enable measurement of the distance between the first and second sites.
- U.S. Pat. No. 5,771,310 to Vannah describes a method of mapping the three-dimensional topography of the surface of an object by generating digital data points at a plurality of sample points on said surface, each digital data point including a property value and a position value corresponding to a particular point representing the properties of the surface of the object. A 3-D transducer probe (e.g., a digitizer) is moved on or over the surface along a random path, and the sample points are digitized to generate a real-time topography or map on a computer screen of selected properties of the object, including without limitation, surface elevation, indentation stiffness, elevation of sub-surface layers and temperature.
- Prosthetics for total knee replacement (TKR), whereby the entire knee joint or a single compartment of the knee joint is replaced can be a common eventuality for the patient with a large focal defect. Although these patients are also managed with anti-inflammatory medications, eventual erosion of the remaining articular cartilage results in effusion, pain, and loss of mobility and/or activity for the patient. Problems encountered after implanting such prostheses are usually caused by the eventual loosening of the prosthetic due to osteolysis, wear, or deterioration of the cements used to attach the device to the host bones. Further, some prostheses used are actually much larger than the degenerated tissue that needs to be replaced, so that extensive portions of healthy bone are typically removed to accommodate the prostheses. Patients who undergo TKR often face a long and difficult rehabilitation period, and the life span of the TKR is accepted to be approximately 20 years. Accordingly, efforts are made to forgo the TKR procedure for as long as possible.
- Accordingly, there is a need for an improved joint surface replacement system that would be effective in restoring a smooth and continuous articular surface and that would also be as durable as the former hyaline cartilage surface, within the context of a minimally invasive procedure that allows for a nearly immediate return to activity, restoration of lifestyle, and pain relief.
- An implant consistent with the invention for installation into a portion of an articular surface includes: a bone-facing distal surface; a proximal surface; and a protrusion formed by an extension of the bone-facing distal surface and the proximal surface.
- Another implant consistent with the invention for installation into a portion of an articular surface includes: a bone-facing distal surface configured to mate with an implant site created by excising a portion of the articular surface; a proximal surface having a contour based on an original surface contour of the excised portion of the articular surface; and a cavity configured to allow an un-excised portion of the articular surface proximate to the implant to remodel over a perimeter edge of the proximal surface.
- Another implant consistent with the invention for installation into a portion of an articular surface having an anterior portion, a posterior portion, a medial portion and a lateral portion includes: a bone-facing distal surface configured to mate with an implant site created by excising a portion of the articular surface; and a proximal surface having a contour based on an original surface contour of the excised portion of the articular surface, and at least two side surfaces each having a concentric arcuate shape with a common center, wherein the implant has an elongate arcuate geometric shape.
- A method for replacing a portion of an articular surface of bone consistent with the invention includes: establishing a working axis substantially normal to an articular surface of bone; excising a portion of the articular surface adjacent to the axis, thereby creating an implant site, the implant site having a first and second opposing arcuate shaped sides; and installing an implant to the implant site.
- Another method of replacing a portion of an articular surface of bone consistent with the invention includes: locating an existing defect in the articular surface; establishing a working axis substantially normal to the articular surface and substantially centered with the existing defect; excising a portion of the articular surface adjacent to the axis, thereby creating an implant site; and installing an implant in the implant site, wherein at least a portion of the existing defect is exposed around a perimeter of the implant.
- Another implant for installation into a portion of an articular surface consistent with the invention includes: a bone-facing distal surface configured to mate with an implant site created by excising a portion of the articular surface; a proximal surface having a contour based on an original surface contour of the excised portion of the articular surface; at least one arcuate shaped side surface configured to abut an edge of the excised portion of the articular surface, the arcuate shaped side surface having a radial extension configured to cover an un-excised portion of the articular surface proximate to the implant.
- Another method for replacing a portion of an articular surface of bone consistent with the invention includes: establishing a working axis substantially normal to an articular surface of bone, the articular surface having a medial side and lateral side defining a width of the articular surface; excising a portion of the articular surface adjacent to the axis, thereby creating an implant site, wherein the excising is performed using a cutting tool that rotates about the axis, the cutting tool having a circular blade portion, the circular blade portion having a diameter greater than the width of the articular surface; and installing an implant to the implant site.
- Another implant consistent with the invention for installation into a portion of an articular surface includes: a bone-facing distal surface configured to mate with an implant site created by excising a portion of the articular surface; and a proximal surface having a contour based on an original surface contour of the excised portion of the articular surface, wherein the proximal surface has at least one indentation formed in the proximal surface configured to promote remodeling of articular cartilage over a portion of the proximal surface of the implant once seated.
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FIG. 1 is a fragmentary side view of a knee having therein an exemplary assembled fixation device and implant of the joint surface repair system surgically implanted by the method in one embodiment of the present invention; -
FIG. 2 a is an exploded side view of an exemplary fixation screw and hex-shaped proximal extension in one embodiment of the present invention; -
FIG. 2 b is an exploded perspective view of an exemplary fixation screw and hex-shaped proximal extension in one embodiment of the present invention; -
FIG. 3 a is a side view of an exemplary assembled fixation screw and hex shaped extension in one embodiment of the present invention; -
FIG. 3 b is an exploded perspective view of another exemplary fixation screw and implant in one embodiment of the present invention; -
FIG. 4 a is a perspective view of the upper surface of an exemplary implant in one embodiment of the present invention; -
FIG. 4 b is a side view of an exemplary implant in one embodiment of the present invention; -
FIG. 4 c is a perspective view of the lower surface of an exemplary implant in one embodiment of the present invention; -
FIG. 5 a is a side view of an exemplary assembled fixation device and implant in one embodiment of the present invention; -
FIG. 5 b is a perspective view of an assembled fixation device and implant in one embodiment of the present invention; -
FIG. 5 c is a perspective view of the upper surface of an exemplary implant, in one embodiment of the present invention; -
FIG. 5 d is a perspective view of the lower surface of an exemplary implant, in one embodiment of the present invention; -
FIG. 6 a is a sectional view of a knee having damaged articular cartilage, showing an exemplary guide pin drilled into the central portion of the defect and an arthroscope being disposed adjacent thereto, in a surgical procedure consistent with one embodiment of the present invention; -
FIG. 6 b is a side view of the distal tip of an exemplary drill device for boring a pilot hole to receive an exemplary fixation screw, in one embodiment of the present invention; -
FIG. 7 a is a sectional view of a knee having damaged articular cartilage, showing an exemplary fixation screw being driven into the defect by an exemplary socket type driver arranged on the guide pin, in a surgical procedure consistent with one embodiment of the present invention; -
FIG. 7 b is a side view of the exemplary fixation screw, socket type driver and guide pin ofFIG. 7 a, illustrating the hex shaped proximal extension in a cross-sectional view, in a surgical procedure consistent with one embodiment of the present invention; -
FIG. 8 a is a perspective view of a knee having damaged articular cartilage, showing an exemplary fixation screw and hex-shaped proximal extension implanted in the defect after removal of an exemplary socket type driver and guide pin, in a surgical procedure consistent with one embodiment of the present invention; -
FIG. 8 b is a sagital view of the exemplary fixation screw and hex-shaped proximal extension ofFIG. 8 a implanted in the defect after removal of an exemplary socket type driver and guide pin, in a surgical procedure consistent with one embodiment of the present invention; -
FIG. 8 c is a perspective view of an exemplary fixation screw, proximal extension and cover, in one embodiment of the present invention; -
FIG. 9 a is a sectional view of an exemplary fixation screw and hex-shaped proximal extension implanted in the defect with the exemplary guide pin replaced and an exemplary measuring tool arranged thereon, in a surgical procedure consistent with one embodiment of the present invention; -
FIG. 9 b is a side partial cross-sectional view of the exemplary fixation screw and hex-shaped proximal extension ofFIG. 9 a implanted in the defect with the exemplary guide pin replaced and an exemplary measuring tool arranged thereon, in a surgical procedure consistent with one embodiment of the present invention; -
FIG. 9 c is a perspective view of an exemplary fixation screw and proximal extension, with the cover removed, in one embodiment of the present invention; -
FIG. 10 a is a sectional view of an exemplary fixation screw and hex-shaped proximal extension implanted in the defect, after removal of the hex-shaped proximal extension, with an exemplary pin and suture strands placed therethrough, in a surgical procedure consistent with one embodiment of the present invention; -
FIG. 10 b is a side partial cross-sectional view of the exemplary fixation screw and hex-shaped proximal extension ofFIG. 10 a, implanted in the defect, with an exemplary pin and suture strands placed therethrough, in a surgical procedure consistent with one embodiment of the present invention; -
FIG. 11 a is a sectional view of an exemplary fixation screw implanted in the defect, with an exemplary pin and suture strands placed therethrough, showing the implanted fixation screw with the implant being tensioned on the suture strands, in a surgical procedure consistent with one embodiment of the present invention; -
FIG. 11 b is a partial cross-sectional view of the exemplary fixation screw ofFIG. 9 a implanted in the defect, showing the implant positioned in the interchondular notch, in a surgical procedure consistent with one embodiment of the present invention; -
FIG. 12 is a sectional view of an exemplary fixation screw implanted in the defect, wherein, after placement of the implant and removal of the suture strands, the implant is driven into place with an impactor and hammer, in a surgical procedure consistent with one embodiment of the present invention; -
FIG. 13 is a side cross-sectional view of an exemplary fixation screw implanted in the defect, after placement of the implant, wherein, after removal of the impactor and hammer, cement is injected between the implant and the bone, in a surgical procedure consistent with one embodiment of the present invention; -
FIG. 14 a is a schematic representation of the two datum curves used to define a patient-specific three-dimensional surface for construction of the articular or lower surface of an implant in one embodiment of the present invention; -
FIG. 14 b is a top view of an exemplary hex-shaped proximal extension in one embodiment of the present invention; -
FIG. 14 c is a perspective view of the bone-contacting or upper surface of an exemplary implant, in one embodiment of the present invention; -
FIG. 15 a is a perspective view of an exemplary compass instrument, in one embodiment of the present invention; -
FIG. 15 b is a perspective view of the distal offset arm of an exemplary compass instrument and cutting blade to be mounted thereon, in one embodiment of the present invention; -
FIG. 15 c is a perspective view of an exemplary driver, showing an exemplary implant on an exemplary tether element, in one embodiment of the present invention; -
FIG. 15 d is a perspective view of an exemplary driver, showing an exemplary implant tensioned on an exemplary tether element, in one embodiment of the present invention; -
FIG. 16 is a perspective view of an exemplary compass instrument and cutting blade mounted on an exemplary guide pin, in one embodiment of the present invention; -
FIG. 17 a is a perspective view of another exemplary cutting blade, in one embodiment of the present invention; -
FIG. 17 b is a perspective view of an exemplary measuring probe, in one embodiment of the present invention; -
FIG. 17 c is a perspective view of an exemplary multi-faced blade mounted in the distal offset arm of an exemplary compass instrument, in one embodiment of the present invention; -
FIG. 18 a is a perspective view of an exemplary site preparation and cutting device, in one embodiment of the present invention; -
FIG. 18 b is a cross sectional view of the exemplary site preparation and cutting device ofFIG. 18 a, in one embodiment of the present invention; -
FIG. 18 c is a perspective view of another exemplary site preparation and cutting device, in one embodiment of the present invention; -
FIG. 18 d is a side view of another exemplary site preparation and cutting device, in one embodiment of the present invention; -
FIG. 18 e is a perspective view of another exemplary site preparation and cutting device, in one embodiment of the present invention; -
FIG. 19 a is a sectional view of the upper surface of an exemplary implant, in one embodiment of the present invention; -
FIG. 19 b is a side view of a portion of the exemplary implant ofFIG. 19 a, in one embodiment of the present invention; -
FIG. 19 c is a perspective view of the upper surface of the exemplary implant ofFIG. 19 a, in one embodiment of the present invention; -
FIG. 19 d is an exploded perspective view of another exemplary implant with taper lock ring, washer and suture, in one embodiment of the present invention; -
FIG. 19 e is a top perspective view of the exemplary implant ofFIG. 19 d seated in the taper lock ring, in one embodiment of the present invention; -
FIG. 19 f is a bottom perspective view of the exemplary implant ofFIG. 19 d seated in the taper lock ring, with washer and suture, disposed within an incision near the defect site, in one embodiment of the present invention; -
FIG. 19 g is a perspective view of the exemplary implant ofFIG. 19 d seated in the taper lock ring, with washer and suture, wherein the suture is threaded through an aperture at the distal end of a seating tool, at a first point in time during the process of seating the implant into the defect site, in one embodiment of the present invention; -
FIG. 19 h is another perspective view of the exemplary implant ofFIG. 19 d seated in the taper lock ring, with washer and suture, wherein the suture is threaded through an aperture at the distal end of a seating tool, at a second point in time during the process of seating the implant into the defect site, in one embodiment of the present invention; -
FIG. 19 i is another perspective view of the exemplary implant ofFIG. 19 d seated in the taper lock ring, wherein the distal end of a seating tool is disposed onto the implant, at a third point in time during the process of seating the implant into the defect site, in one embodiment of the present invention; -
FIG. 20 a is a perspective view of an exemplary inner recording element of an exemplary measuring device, in one embodiment of the present invention; -
FIG. 20 b is a perspective view of an exemplary outer marking element of an exemplary measuring device, in one embodiment of the present invention; -
FIG. 20 c is a cross-sectional perspective view of an exemplary measuring device showing an exemplary inner recording element and an exemplary outer marking element, in one embodiment of the present invention; -
FIG. 20 d is an exploded perspective view of another exemplary measuring device, in one embodiment of the present invention; -
FIG. 20 e is a perspective view of the exemplary measuring device ofFIG. 20 d, illustrating an exemplary scroll alignment feature, in one embodiment of the present invention; -
FIGS. 20 f and 20 g are side views of the exemplary measuring device ofFIG. 20 d illustrating the translational motion of the handle with respect to the tip of the device, in one embodiment of the present invention; -
FIG. 20 h is a perspective view of the distal end of the exemplary measuring device of -
FIG. 20 d, in one embodiment of the present invention; -
FIG. 20 i is a perspective view of the distal end of the exemplary measuring device ofFIG. 20 d with outer element, disposed upon the inner element engaging a mating feature of the screw, in one embodiment of the present invention; -
FIG. 21 is a perspective view of an exemplary unitary implant, in one embodiment of the present invention; -
FIG. 22 is a perspective view of a defect site with a keyed aperture for receiving the exemplary unitary implant ofFIG. 21 , in one embodiment of the present invention; -
FIG. 23 is a perspective view of an exemplary composite implant, in one embodiment of the present invention; -
FIG. 24 is a perspective view of another exemplary composite implant, in one embodiment of the present invention; -
FIG. 25 is a perspective view of an exemplary implant illustrating the geometry of said implant for use in an algorithm for establishing minimum implant thickness, in one embodiment of the invention; -
FIG. 26 is a perspective view of an exemplary implant illustrating the geometry of said implant for use in an algorithm for establishing minimum implant thickness, in one embodiment of the invention; -
FIG. 27 a is a perspective view of an exemplary drill guide device in an exemplary generic bone implant embodiment of the present invention; -
FIG. 27 b is a perspective view of another exemplary drill guide device in an exemplary generic bone implant embodiment of the present invention; -
FIG. 28 a is a top sectional view of the anterior-posterior plane of an articulating surface in an exemplary generic bone implant embodiment of the present invention; -
FIG. 28 b is a side sectional view of the medial-lateral plane of an articulating surface in an exemplary generic bone implant embodiment of the present invention; -
FIG. 29 is a perspective view of the use of an exemplary drill guide in an exemplary generic bone implant embodiment of the present invention, as the drill guide is brought up to a lesion site of the articulating surface; -
FIG. 30 is a perspective view of the use of an exemplary drill guide in an exemplary generic bone implant embodiment of the present invention, as the drill guide is seated into position and a guide pin is driven through the drill guide; -
FIG. 31 is a perspective view of the articulating surface in an exemplary generic bone implant embodiment of the present invention, as a bone drill is passed over the guide pin to create a pilot hole for the screw; -
FIG. 32 is a cross-sectional view of the articulating surface in an exemplary generic bone implant embodiment of the present invention, as the screw is driven into the pilot hole with a cap positioned into the screw; -
FIG. 33 is a cross-sectional view of the articulating surface in an exemplary generic bone implant embodiment of the present invention, as the cap is removed and a rod is inserted into the screw, and the guide is positioned back over the rod and returned to its position in contact with the articular surface; -
FIG. 34 is a side perspective view of the articulating surface in an exemplary generic bone implant embodiment of the present invention, as the guide is used to take a depth measurement needed for implant geometry; -
FIG. 35 is a top perspective view of the lower surface of an exemplary implant in an exemplary generic bone implant embodiment of the present invention; -
FIG. 36 is a side perspective view of an exemplary implant in an exemplary generic bone implant embodiment of the present invention; -
FIG. 37 is a side perspective view of another exemplary implant in an exemplary generic bone implant embodiment of the present invention; -
FIG. 38 is a perspective view of the articulating surface in an exemplary generic bone implant embodiment of the present invention, as the implant site is reamed with a cutting/reaming tool in preparation for receiving an implant; -
FIG. 39 is a top perspective view of an alternative exemplary cutting/reaming tool in an exemplary generic bone implant embodiment of the present invention, -
FIG. 40 is a side perspective view of an exemplary cleaning tool for cleaning the female taper of the screw prior to delivery of the implant, in an exemplary generic bone implant embodiment of the present invention; -
FIG. 41 is a side perspective view of an exemplary suction tool for holding and delivering the implant, in an exemplary generic bone implant embodiment of the present invention; -
FIG. 42 is a side perspective view of an exemplary suction tool holding an implant in place, in an exemplary generic bone implant embodiment of the present invention; -
FIG. 43 is a side cross-sectional view of an exemplary suction tool holding an implant in place, with an implant in place, in an exemplary generic bone implant embodiment of the present invention; -
FIG. 44 is a top perspective view of the articulating surface in an exemplary generic bone implant embodiment of the present invention, with the implant driven into its final position; -
FIG. 45 is a side perspective view of an exemplary removal/revision tool in an exemplary generic bone implant embodiment of the present invention; -
FIG. 46 is a side perspective view of an exemplary removal/revision tool, with an implant in place, in an exemplary generic bone implant embodiment of the present invention; -
FIG. 47 illustrates an exemplary alternatively-keyed embodiment of the screw and the exemplary alternatively-keyed implant to which it is adapted to mate, in an exemplary embodiment of the present invention; -
FIG. 48 illustrates a side cross-sectional view of an exemplary alternatively-keyed embodiment of the screw, in an exemplary embodiment of the present invention; -
FIG. 49 illustrates a side perspective view of the articular surface of a lesion site and an exemplary biaxial measuring tool for developing an axis normal to the articular surface, in one embodiment of the present invention -
FIG. 50 illustrates another side perspective view of the articular surface of a lesion site and an exemplary biaxial measuring tool for developing an axis normal to the articular surface, in one embodiment of the present invention; -
FIG. 51 illustrates a side exploded view of an exemplary biaxial measuring tool, in one embodiment of the present invention; -
FIG. 52 illustrates a top perspective view of the distal end of an exemplary biaxial measuring tool in a first position, in one embodiment of the present invention; -
FIG. 53 illustrates a top perspective view of the distal end of an exemplary biaxial measuring tool in a second position, in one embodiment of the present invention; -
FIG. 54 illustrates an exemplary digital measuring system in one embodiment of the present invention; -
FIG. 55 illustrates an exploded perspective view of an exemplary handpiece in an exemplary digital measuring system in one embodiment of the present invention; -
FIG. 55 a illustrates a top perspective cutaway view of an exemplary printed linear index strip passing through an exemplary linear head for reading, in an exemplary handpiece in an exemplary digital measuring system in one embodiment of the present invention; -
FIG. 55 b illustrates a top perspective cutaway view of an exemplary printed rotary index strip passing through an exemplary rotary head for reading, in an exemplary handpiece in an exemplary digital measuring system in one embodiment of the present invention; -
FIG. 55 c illustrates an exemplary linear index strip in an exemplary handpiece in an exemplary digital measuring system in one embodiment of the present invention; -
FIG. 55 d illustrates an exemplary rotary index strip in an exemplary handpiece in an exemplary digital measuring system in one embodiment of the present invention; -
FIG. 56 a illustrates a side perspective view of an exemplary handpiece with the probe assembly removed, in an exemplary digital measuring system in one embodiment of the present invention; -
FIG. 56 b illustrates a side perspective view of an exemplary handpiece, including the probe assembly, in an exemplary digital measuring system in one embodiment of the present invention; -
FIG. 57 illustrates a top perspective view of an assembled exemplary handpiece, in an exemplary digital measuring system in one embodiment of the present invention; -
FIG. 58 illustrates a side perspective view of an assembled exemplary handpiece, in an exemplary digital measuring system in one embodiment of the present invention; -
FIG. 59 illustrates a top cross-sectional view of an assembled exemplary handpiece, in an exemplary digital measuring system in one embodiment of the present invention; -
FIG. 60 illustrates a side cross-sectional view of an assembled exemplary handpiece, in an exemplary digital measuring system in one embodiment of the present invention; -
FIG. 61 illustrates a side cutaway perspective view of an exemplary base unit, in an exemplary digital measuring system in one embodiment of the present invention; -
FIG. 62A is a top perspective view an alternative exemplary embodiment of a substantially round implant having a protrusion; -
FIG. 62B is a cross sectional view of the implant ofFIG. 62A taken along the line B-B ofFIG. 62A ; -
FIG. 62C is a side perspective view of the implant ofFIG. 62A ; -
FIG. 63A is a side perspective view of another implant embodiment consistent with the invention having protuberances; -
FIG. 63B is a cross sectional view of the implant ofFIG. 63A taken along the line B-B ofFIG. 63A ; -
FIG. 64A is an alternative embodiment of an implant having a cavity to allow an unexcised portion of articular surface proximate to the implant to grow over the perimeter edge of the implant; -
FIG. 64B is a cross sectional view of the implant ofFIG. 64A taken along the line B-B ofFIG. 64A ; -
FIG. 65A is another alterative embodiment of an elongated implant consistent with the invention; -
FIG. 65B is a perspective view of an implant site and a reaming tool for preparing the implant site to accept the implant ofFIG. 65A ; -
FIG. 65C is a cross sectional view of the bottom surface of the implant site ofFIG. 65B ; -
FIG. 65D is a perspective view of the implant ofFIG. 65A being seated or placed into the implant site ofFIG. 65B ; -
FIG. 66A is a top perspective view of alternative elongated implant embodiment having protrusions for covering proximate portions of un-excised articular surface when the implant is seated; -
FIG. 66B is a top perspective view of the implant ofFIG. 66A being seated or placed into a matching implant site; -
FIG. 67 is a perspective view of an implant being seated into an existing defect without cutting the borders of the defect; -
FIG. 68A is a top perspective view of an implant having grooves to promote remodeling of articular cartilage over a proximal surface of the implant; -
FIG. 68B is a cross sectional view of the implant ofFIG. 68A ; -
FIG. 68C is a perspective view of a portion of the perimeter edge of the implant ofFIG. 68A illustrating particular edge geometry to also promote remodeling of articular cartilage over a proximal surface of the implant; and -
FIG. 68D is a top perspective view of the implant ofFIG. 68A seated in an articular surface illustrating the remodeling of articular cartilage over a portion of the proximal surface of the implant. - As an overview,
FIG. 1 shows a surgically implanted articular joint surface repair system consistent with the present invention. As shown, the assembled fixation device includesfixation screw 10,implant 40, and anchoringpin 5, implanted in the defect in the medial femoralchondral surface 55 ofknee 50.Implant 40 is configured so that bearing orbottom surface 41 of the implant reproduces the anatomic contours of the surrounding articular surface of theknee 50. - As illustrated in
FIGS. 2 a, 2 b and 3 a,fixation screw 10 comprisesthreads 12 running the length of the screw from tapereddistal tip 11 to hex-shapeddrive 15. In the embodiment shown, the screw includes a tapereddistal end 11, and aggressivedistal threads 12, so that, asscrew 10 is driven into the subchondral bone 100 (as shown inFIG. 7 a) the screw dilates open and radially compress the subchondral bone, increasing its local density and thereby increasing the fixation strength of the screw. Thescrew 10 may taper down to thedistal end 11, and the diameter of the screw may become greater and more uniform at the center thereof, so that adjustment of the depth of thescrew 10 with respect to thesubchondral bone 100 does not significantly further increase or decrease the compression of the subchondral bone. - One or more milled
slots 13 run the length of the uniform diameter portion of thescrew 10.Slots 13 ensure that as healing or tissue in-growth begins, migrational or rotational movement of the screw is inhibited. Thescrew 10 is configured to be driven by a female orsocket type driver 2 as shown inFIG. 7 b, which engages a hex-shapeddrive 15 located toward theproximal end 17 of the screw. A cylindrical proximal extension 14 (which may, alternatively, be arecess 303 which mates with a plug or other protrusion on the implant surface, as shown inFIG. 8 c) extends from hex-shapeddrive 15, which eventually serves as a fixation element for surfaceprosthetic implant 40. Throughhole 16 runs through the central axis of the screw. Hex-shaped cover 30 (which may, alternatively, be a plug 301, for mating with afixation element 302 having a recess, as shown, e.g., inFIGS. 3 b, 8 c, and 9 c, and described in the following paragraph) is configured to engage the cylindricalproximal extension 14 of thescrew 10 to prevent exposure of the cylindrical extension from inadvertent contact or damage. The hex-shapedcover 30 is finished with a radiusedproximal end 31 that assists in the visual determination of the correct depth setting of the screw. Throughhole 32 in the hex-shapedcover 30 corresponds with throughhole 16 in thefixation screw 10. - Alternatively, as shown in
FIGS. 3 b, 8 c, and 9 c, the female-shaped cover may instead be a plug 301 having a male-shapedmating component 305, for mating with afixation element 302 of ascrew 10′ having arecess 303. Additionally, the shape of the cover and plug, or other recessed, protruding, or mating components may be other than hexagonal, and those in the art will recognize that one of any number of shapes or configurations for such components may be employed in a device or method consistent with the invention. - Also, while many of the components described herein are cannulated, having guide apertures, through holes, and/or central lumina along their length, for disposing such components about a guide rod for proper location of the components with respect to the articular surface, it should be recognized that a
suture 313 or other flexible element, or other guide feature may be used in place of a guide rod, or a guide rod or wire may be eliminated altogether from one or more steps consistent with the invention described herein. As shown inFIG. 8 c, thesuture 313 may be fixedly or removably attached to the plug 301. - As shown in
FIGS. 4 a, 4 b and 4 c,implant 40 compriseslower bearing surface 41,top surface 42 andprotrusion 45 located centrally on the bottom surface. As thetop surface 42 of theimplant 40 is not a bearing surface, and instead is fixed intosubchondral bone 100, a series of steppedmachine cuts 43 following the contours of the defect are created. By creating stepped machine cuts 43 a contoured contact surface matching the defect in thesubchondral bone 100 is created. This contact surface results in an increased surface area that should enhance resistance to loosening of theimplant 40 via rotational or translational loading. In the illustrated embodiment, the stepped cuts are shown as square cross-section cuts, but the cuts may be circular, triangular, or another configuration. - In order to secure the
implant 40 to thefixation screw 10,precision taper 44 is machined into or onto aprotrusion 45 on thetop surface 42 of the implant. Theprecision taper 44 is configured to engage the cylindricalproximal extension 14 of thescrew 10, once the hex-shapedcover 30 has been removed therefrom.Taper 44 may be mated withextension 14 so that a friction fit is provided between these surfaces. The assembled fixation device is shown inFIGS. 5 a and 5 b. Alternatively, other engagement mechanisms such as snap-fits, press-fits, threads, or coupling elements, for example, may also be used. In one embodiment, leadingpin 47 arranged on theprotrusion 45 assists penetration into subchondral bone. Also, in one embodiment, guideaperture 46 passes through the top 42 and bottom 41 surfaces of theimplant 40, just slightly off center of thereference axis 20A. Alternatively, guideaperture 46 may be located in the center of theimplant 40 and corresponds to throughhole 16 running through the central lumen in thefixation screw 10. Bone cement may be injected throughguide aperture 46 on the surface of theimplant 40 and throughhole 16 in thefixation screw 10, to enhance the contact surface between the device and the subchondral bone. In one embodiment, the implant is constructed of cobalt chromium, although other materials may be used, including implantable plastics. Additionally, biologically active coatings or surface treatments (e.g., to enhance bone ingrowth or improve wear properties) may be utilized or combined as laminates, particularly with respect to the bearing surfaces and bone contacting surfaces. Further exemplary materials that may be used in fabricating an implant consistent with the invention are described hereinbelow. - As shown in
FIG. 3 b, it is noted thatprecision taper 44 may be a male-shapedcomponent 304 instead of the above-describedfemale component 44. In this configuration, the male-shapedcomponent 304 of theimplant 40′ is configured for mating with afixation element 302 of thescrew 10′ having arecess 303 adapted to receive the male-shapedcomponent 304. - By way of example,
FIGS. 6 a-13 depict one exemplary joint surface methodology of the present invention.FIG. 6 a shows afocal defect 1 of thearticular surface 55 of the femoral chondyle bone of theknee 50. This defect is identified byarthroscope 25 inserted in the area of thedefect 1 during a diagnostic arthroscopy or surgical arthroscopy. The disclosed surgical intervention begins by drilling aguide pin 20 definingreference axis 20A into the central portion of thedefect 1 via anincision 200 typical of arthroscopic procedures. Placement of this pin may be done using visual, freehand techniques, or may be located centrally by usingouter element 71 of a measuring tool 70 (as shown inFIGS. 9 a and 9 b), or other aiming device or technique, to define a center. Thisreference axis 20A serves to establish a working axis located central to thedefect 1 for the procedures that follow, andarthroscope 25 may be used to view the joint for purposes of establishing areference axis 20A generally perpendicular to and bisecting the existingarticular surface 55 defined byradii FIG. 8 b. Referring toFIGS. 7 a, 7 b, 8 a and 8 b,fixation screw 10 and hex-shapedcover 30 are driven into thedefect 1 in thesubchondral bone 100 by socket-type driver 2 mounted over (i.e., about)guide pin 20 located onreference axis 20A. Under arthroscopic view, the depth offixation screw 10 may be adjusted bydriver 2 so that the bottom of the radiusedsurface 31 of the hex-shapedcover 30 is positioned tangent to theradii articular surface 55. Theguide pin 20 is removed and theknee 50 is articulated through its range of motion to ensure that the height of the radiusedsurface 31 of the hex-shapedcover 30 is proper, since theprosthetic surface 41 of theimplant 40 is created also to be tangent to thisradiused surface 31. The depth positioning of the radiusedsurface 31 of the hex-shapedcover 30 establishes a point of origin or a reference point for all future measuring and machining operations. Arthroscopic examination may be carried out from multiple arthroscopic views to confirm positioning. - A
drill mechanism 306, as illustrated inFIG. 6 b, may be used to bore a pilot hole for receiving a fixation screw 10 (as shown, e.g., inFIGS. 2 a, 2 b and 3 a). As shown, the drill may have ashank portion 307 and abit portion 308. Thebit portion 308 may include a spiral or parabolicfluted tip 309 having proximal 310, medial 311, and distal 312 portions. The root diameter at themedial portion 311 is substantially equal to the diameter of thefixation screw 10, and the diameter decreases as thedistal portion 312 tapers away from theshank 307. Theproximal portion 310 of thebit 308 may be used as a visual indicator during drilling, to determine the point at which the proper bore depth has been attained. The drill mechanism may have a central lumen (not shown) having a diameter slightly greater than the diameter of the guide pin 20 (as illustrated inFIG. 6 a) running along its length, so that, with theguide pin 20 in place, thedrill 306 may be disposed about theguide pin 20 during drilling to ensure proper location of the pilot hole with respect to thearticular surface 55. Alternatively, a self-drilling or self-tapping screw, may be used, as those skilled in the art will recognize. - For surface preparation and accurate measurement of the implant site and the subsequent sizing of the implant,
instrument 120 is provided. Thecompass instrument 120 may be configured to serve as a mounting tool for a number of functional blades or tips and when located about theaxis 20A, viaguide rod 20, may be used for measuring and cutting operations. In the embodiment shown inFIG. 15 a,compass instrument 120 includeshandle 110, a cannulatedshaft 111 that extends through the handle, and a cannulated distal offsetarm 112. The instrument may be rigid in construction and may be a durable reusable and resterilizable instrument. The distal offsetarm 112 is configured so that it can be introduced into a site through anincision 200 typical of an arthroscopic procedure. Once the distal offsetarm 112 has fully penetrated the incision and enters the site,shaft 111 can be angularly repositioned so that it becomes more coaxial to thereference axis 20A and advanced in-line with thereference axis 20A towards the implant target site. While performing this maneuver to position thecompass instrument 120, theguide pin 20 should be removed from its position in thedefect 1. Whencompass 120 is in its proper position at or near the implant target site, theguide pin 20 is delivered through theinstrument cannulation 113, re-establishing the working (reference)axis 20A used to define the implant geometry. - Referring to
FIG. 15 b, within offsetarm 112 is a slottedsurface 114 for engaging a series of cuttingblades 121,boring blades 124, or measuring probes 122. Theslots 115 are configured so that said series of cuttingblades 121, boring blades 124 (FIG. 17 c), measuringprobes 122, 123 (FIGS. 17 a, 17 b), or like elements may be partially constrained or fixed in position such that they may be adjusted linearly along the length of the slottedsurface 114 over a defined distance of travel. Intersecting the plane of travel defined by slottedsurface 114 andslots 115, is thecannulation 113. - As illustrated in
FIG. 16 , when fitted with acutting blade 121, and with theguide pin 20 advanced through theshaft 113 ofinstrument 120, so that the guide pin passes through a closelysized hole 116 in the cutting blade, the blade's position becomes fully constrained. When constrained in this fashion, a fixed length from the rotational orreference axis 20A to the cuttingsurface 117 of cuttingblade 121 is established. This defines the radius that is effected as theinstrument 120 is rotated around theguide pin 20, and corresponds to the overall diameter of theimplant 40 that is delivered to the fully prepared site. Thecutting blade 121 is used to circumscribe and cleanly cut the surrounding articular cartilage. - In an alternative embodiment, as shown in
FIGS. 17 a and 17 b,blade 123 and measuringprobe 122, respectively, may havemultiple holes 118 that defines that probe/blade's functional diameter. In addition, the blades may be specifically configured so that staged or sequential cuts of varying depths and diameters can be performed within the procedure. Also, such a blade can be configured by providing areadable scale 119 corresponding to thehole 118 pattern, so that the surgeon may determine and set the appropriate diameter as needed by positioning theguide pin 20 in the corresponding hole. As thereadable scale 119 may be located on theblade 123 with respect to the blade'scutting surface 117, a high degree of positional accuracy may be achieved as the scale may be defined specifically for each type of blade. This approach creates an inexpensive means of providing sharp blades of varying diameters and varying blade types without a large inventory of size- and type-specific blades. Referring toFIG. 17 b, roundedtip 109 of measuringprobe 122 can be used to determine the appropriate diameter and can be similarly sized and secured in thecompass instrument 120. Thetip 109 may be rounded to prevent marring of the articular surface.FIG. 17 c shows a boring bit orbone cutting blade 124 with multiple cutting surfaces 107 and 108 configured in this fashion. - Turning now to
FIGS. 9 a and 9 b, with theguide pin 20 replaced, a measuringtool 70 is inserted so that thereference axis 20A is utilized. A central element of the measuringtool 70 is apost 75 that is static, establishes the axial location of the point oforigin 80, and mates with a rotational location feature within thescrew 14. By rotating the outer arm oroutrigger 71 of the measuringtool 70 relative to thestatic post 75 while also maintaining contact with thearticular surface 55, an axial displacement or Z dimension can be established relative to the point oforigin 80 for any point along the sweep of the outrigger. Each such Z dimension may be recorded in real time with conventional dial gauge indicators 72 or with a digital recording device, such as disclosed in U.S. Pat. No. 5,771,310 to Vannah, or by using other known marking techniques. Although numerous points may be taken, ideally a minimum number of points are taken to define accurately the target articular surface. In other embodiments, multiple outriggers that embody different diameters or an adjustable outrigger may be used to map larger defects, and also to determine the final diameter of the prosthetic surface that fits within the defect. It is noted that the measuring tool may comprise a spring or other tensioning device (not shown), for urging the outrigger distally with respect to the handle of the tool. In this aspect, the outrigger is manually pressed against the articular cartilage, so as to maximally compress the articular cartilage upon recording data points, so that the data points taken are of a maximally “loaded” or “compressed” dimension. -
FIGS. 20 a, 20 b and 20 c show an alternative measuring andmapping device 210 for obtaining the articular surface dimension, comprisinghousing 217 and arecording element 218. As shown inFIG. 20 a,recording element 218 includesupper portion 219,flange 222 and calibratedlower portion 220. Key-shapedsurface 221 located atdistal end 225 ofrecording element 218 is configured to engage a reciprocal key-shaped surface in theproximal extension 14 offixation screw 10, or, for example, a key shaped cover arranged on the proximal end of the screw (not shown). Theupper portion 219 ofrecording element 218 may be constructed of a relatively soft or other deformable material that can be marked with patient data.Cannulated shaft 223 runs through the central lumen of therecording element 218. As shown in FIG. 20 b,housing 217 includes amarking mechanism 224 located on theupper portion 226 of the housing, at or within window oraperture 230. Anindexing indicator 228 is located on thelower portion 227 of thehousing 217, at window oropening 229. - Turning to
FIG. 20 c,recording element 218 is inserted inhousing 217 of measuring andmapping device 210, so that thedistal end 225 ofrecording element 218 appears throughopening 232. Tensioning means (not shown) in thedevice 210, enablesrecording element 218 to move longitudinally withinhousing 218. With theguide pin 20 replaced, the measuringdevice 210 is inserted on the guide pin onreference axis 20A so that key-shapedsurface 221 engages the corresponding keyed surface of the screw and is maintained in static position thereby. These key-shaped surfaces establish the rotational position of the articular surface points to be mapped relative to the screw. During the measuring and mapping procedure, the surgeon rotateshousing 217 and outer arm oroutrigger 231 located at thedistal end 235 of housing. By depressingmarking mechanism 224, a series of depressions ormarked points 240 is established in the relatively soft surface of theupper portion 219 of therecording element 218, which deforms at these marked points so that they can be utilized as patient data.Indexing indicator 228 and calibratedlower portion 220 ofrecording element 217 allow for controlled rotational movement betweenhousing 217 andrecording element 218. In this way, the rotational position of the mapped articular surface points 235 relative to thescrew 10 as appreciated by outer arm ofoutrigger 231, is translated to the implant geometry as a feature so that the accurate rotational location of theimplant 40 relative to thescrew 10 is maintained. - For example, as shown in
FIGS. 8 b and 9 b, to accurately reproduce the tworadii articular surface 55, four points, 81 a and 81 b, and 82 a and 82 b, and the point oforigin 80 are recorded. As any three points in a single plane define a curve, by recordingpoints origin 80,radius 60 defining the medial-lateral aspect 68 of the chondyle can be determined. By recordingpoints origin 80, theradius 61 defining the anterior-posterior aspect 69 of the chondyle can be determined. In the example provided, in order to maintain the relationship between these two defined radii, 60 and 61, the measuringtool 70 is constructed so that it can be accurately indexed from a fixed starting point along 90 degree intervals to capture or map said fourpoints - Locating surfaces or features created on the
radius cover 30, or along some length of thefixation screw 10, hex-shaped drive surface of thescrew 14 or on the cylindrical proximal extension (or recess) of thescrew 14, correlate to some surface or feature on the measuringtool 70 and allow the measurement of the rotational position of the four measuredpoints reference axis 20A with respect to said locating surfaces. This data becomes important in configuring theimplant 40 with respect to thefixation screw 10 so that the proper orientation of said measured points to fabricated geometry is maintained. Of course, such measuring tool can be configured to measure any number of points at any interval desired. - While the measurements are illustrated in
FIGS. 9 a and 9 b as being taken from the bottom of the radiusedsurface 31 of the hex-shapedcover 30 of the screw, the measurements may alternatively be taken from the top of thescrew 10′ itself, as shown inFIG. 9 b. As shown, in this embodiment, a key 315 or other alignment feature may be provided, to indicate the starting point for taking measurements. In this configuration, the measuring tool used, as well as the implant manufactured, both have a mating feature matching the key 315, for properly locating the starting point of the measurements taken and thereby subsequently properly aligning the implant with respect to the defect. - Other embodiments of measuring and recording tools are possible. One such embodiment of a measuring and
recording tool 210′ is shown inFIGS. 20 d-20 i. As shown, measuringtool 210′ comprises ahandle 316,outer shaft 333,inner shaft 330, scroll 317, atactile feedback portion 318,ring 320 having abutton 321 in communication with asharp marking point 326 thereunder, a rotatingportion 322 having arotational lock 323 which prevents rotation of therotating portion 322 when engaged, and anoutrigger portion 324. Thehandle 316 remains fixed during rotation and does not move while thetool 210′ is used for measuring. Instead, the rotatingportion 322 is rotated to a start position and the rotational lock is engaged, securing therotating portion 322 to thetactile feedback portion 318 and thereby preventing its rotation. Thescroll 317 is configured with anotch 325 or similar mating feature to align with a corresponding mating feature (not shown) of thehandle 316, such that the scroll can only align at one rotational point, at 0 degrees, with respect to thehandle 316 upon loading into thetool 210′, e.g., by “snapping” into place. Thesharp marking point 326 located inside thering 320 under thesharp marking point 326, marks a point of depression into thescroll 317 whilefirst button 321 is being depressed. Instead of marking by making depressions on a scroll or spool, marking could alternatively be made upon nearly any surface, e.g., using ink to record on a paper spool, or by digital means. - As shown in
FIGS. 20 f and 20 g,outer shaft 333, which is fixedly coupled to rotatingportion 322,outrigger 324 andring 320, is freely rotatably disposed aboutinner shaft 330 and slidably disposed aboutinner shaft 330 within a range bounded bypoints FIG. 20 f, theoutrigger 324 is retracted, andouter shaft 333 is located at a position of origin along a z-axis parallel to the inner 330 and outer 333 shafts, such that the proximal end of thering 320 is located atposition 335. InFIG. 20 g, theoutrigger 324 is extended, andouter shaft 333 is located at a position 0.250 in. (0.64 cm.) from the origin of the z-axis parallel to the inner 330 and outer 333 shafts, such that the proximal end of thering 320 is located atposition 335′. The motion of the sliding of theouter shaft 333 aboutinner shaft 330 during marking is translated via theouter shaft 333, rotatingportion 322 and ring 320 (including markingbutton 321 and marking point 326) to a location along thescroll 317. Thus, as the user rotatesoutrigger 324 by rotation of rotatingportion 322, the outrigger moves along the articular surface proximally or distally with respect to the inner shaft, and the displacement of theoutrigger 324 along a z-axis parallel to the inner 330 and outer 333 shafts may be marked on thescroll 317 by depression of thebutton 323 at various points along the rotation of theoutrigger 324. Thetactile feedback portion 318 has a series ofdepressions 319 or other tactile feedback means, e.g. spring ball plungers which engage in indentations (not shown) in theinner shaft 330, spaced at 90 degrees from one another, so that when therotational lock 323 is engaged asrotating portion 322 is being rotated, the user feels a “click” or other tactile feedback to indicate to the user the rotational location of therotating portion 322 at 90 degree intervals with respect to thehandle 316, i.e., at 90 degrees, 180 degrees, 270 degrees, and 0 (or 360) degrees, for purposes of marking at those points. It is further noted that the starting point for marking may or may not be selected independent of the 90-degree rotational points, and that therotating portion 322 may or may not be configured so that it is not tied to the 90-degree indexing until thescroll lock 323 is engaged. - As shown in
FIGS. 20 e, 20 h and 20 i, akeyed mating feature 331 may be disposed at the distal end of theinner shaft 330 with respect to the outrigger portion, for mating with akey feature 315 on thescrew 10′ (as shown inFIGS. 9 c and 20 i), so as to locate properly the starting point of the measurements taken with respect to the screw, and thescroll 317.FIG. 20 h illustrates a more detailed view of the distal end of the markingtool 210′, withouter shaft 333,inner shaft 330 with keyedmating feature 331, andoutrigger 324 withrounded end 338, which travels along the path ofcircle 339.FIG. 20 i illustrates the measuringtool 210′, with the keyedmating feature 331 inserted into the recessedportion 303 of thescrew 10′ at itsfixation element 302. - Referring now to
FIG. 14 a, data recorded during the mapping procedure described above can then be entered into a known parametric engineering design software or similar algorithm, as four values, 85 a, 85 b, 85 c, and 85 d, corresponding to the four measured points, 81 a, 81 b, 82 a and 82 b, with theorigin 80 defining a reference plane. These fourvalues circle 90, which represents the diameter of the measuringtool 70. These line elements are also constrained to lie within planes that are perpendicular to one another. Of course, more than four points may be taken and used to map the articular surface, e.g., 8 points; however, a minimum of four points should be taken, so that two intersecting datum curves may be defined for purposes of mapping. - Datum curves 86 and 87, representing the medial-lateral (“ML”) and anterior-posterior (“AP”) curves, are constructed by connecting the end points of the
line elements origin 80, which is common to both curves. These twodatum curves bottom surface 41 of theprosthetic implant 40. Bysweeping datum curve 87 along a path defined bydatum curve 86, a three dimensional surface is now defined. - By constructing this series of geometric relationships in a known parametric engineering model, patient-specific geometry can be input as values and the model algorithm can be run to reproduce the anatomic contours mapped in the patients within only a few moments. As a process, this generic model is the starting point for all patient treatments. Sterile pins, screws, and measuring devices that are all non-patient-specific may be stocked in the hospital and ready to use whenever an appropriate defect is diagnosed. Patient-specific data may be transmitted from the surgeon to the fabricating facility via an interface to the Internet or other network. Data input into the interface may be read directly into the generic parametric model to produce a viewable and even mappable patient-specific parametric model within moments. Confirmation by the surgeon could initiate a work order for the production of the patient specific device. Existing technology allows the parametric model to generate toolpaths and programming, e.g., to a CAD/CAM system comprising appropriate hardware and/or software coupled to appropriate data-driven tools, to fabricate the implant.
- Defining two additional datum curves 88 and 89, at offset distances from datum curves 86 and 87, is performed to define the top or
non-bearing surface 42 of theimplant 40. Thistop surface 42 should be closely matched to the bearing surface geometry to be implanted without having to remove an excessive quantity of bone from the chondral surface. - Referring to
FIGS. 14 c and 19 c, implant geometry may be defined whereby the top orbone contacting surface 42 of theimplant 40 exhibits an axial symmetry. The central axis AA passes through the point oforigin 80 of theimplant 40 and when the implant is positioned at the target site, aligns with theoriginal reference axis 20A as defined by theguide pin 20 andfixation screw 10. The central axis AA can then be used to define the preparation tools so that thebone contacting surfaces 42 of theimplant 40 and the preparation tools can be matched in both configuration and dimension to create a mating fit between the surface of the prepared target site and thebone contacting surfaces 42 of the implant. For example, if the preparation tools can be fabricated using some of the same dimensions obtained during the articular surface mapping procedure, the implant geometry and corresponding preparation tool geometry can be mated and optimized so that a minimum vertical thickness of the implant as well as a minimum depth of bone removal is required. This may be advantageous in ensuring good long term clinical results with the implant, as poor quality of fit between bone surfaces and bone-contacting surfaces of traditional orthopedic prosthetic devices has been noted to contribute to early clinical failures. - For example, as shown in
FIGS. 14 c and 19 c the top orbone contacting surface 42 of theimplant 40, a series ofradial cuts 198 may create surfaces that increase resistance of the implant to rotational forces. These features may be located at theouter diameter 190 of theimplant 40 to increase their effectiveness. Additional contact surfaces may also be created by one ormore protrusions 195 located on the bottom 42 of the implant. Similarly, surface treatments known in the field of orthopedic devices, such as porous and/or osteoconductive coatings, may be utilized onsurface 42. - As shown in
FIG. 19 b,outer diameter 190 may include a slight outward taper orprotrusion 197 along the diametrical surface to enhance load bearing or load transfer properties of the implant to surrounding bone. This feature may also increase the fixation strength of the implant. A fillet 199 (as shown inFIG. 19 a) that runs around the implant at the intersection of thediametrical surface 190 and the bearingsurface 41 is also useful in providing a smooth transition between the host articular cartilage and the implant surface. - However, if a greater depth of implant is needed as a result of the defect appearance the offset curves 88 and 89 (as shown in
FIG. 14 a) can be extended to increase the overall thickness of theimplant 40 or the offset curves may be eliminated entirely so that the contoured surface is backed by a revolved geometry that is symmetrical toreference axis 20A. Turning toFIG. 19 c, where the ML curve and AP curve (defined by the obtained measurements) are not axially symmetrical, the thickness of theimplant 40 requires adjustment. At the same time, an unnecessarily thick implant requires a greater amount of bone to be removed at the target site. Therefore, the thickness of the implant may be determined by taking the largest obtained measurement and adding a minimal offsetamount 208. (The implant is thinnest at the highest point on the ML curve.) This can be similarly accomplished by adjusting the angle A (FIG. 19 a) of the bone-contactingsurface 42 of theimplant 40 and a corresponding angle of the preparation tool. This also allows for a correction of the implant geometry, to compensate for any non-perpendicular placement of the guide pin with respect to the articular surface. - With reference now to
FIGS. 25 and 26 , an exemplary algorithm consistent with the invention establishes the minimum thickness of an implant necessary to include all patient data points, receiving as input all of the points measured (typically, four) and identifying the largest value. One such exemplary algorithm is as follows (and as shown inFIGS. 25 and 26 ): -
maxval= D6 if maxval < D11 maxval = D11 endif if maxval < D14 maxval = D14 endif D684 = maxval + .045
In the foregoing exemplary algorithm, a first data point D6 is initially assigned as the maximum value (maxval). If . . . then type statements are used to compare other data points (D11 and D14) to maxval. If other data points are greater than maxval, the algorithm reassigns maxval to the new larger data point. LLMT represents the height of the lower limit plane along the z-axis, and ULMT represents the height of the upper limit plane along the z-axis. D684 is a dimension that controls the ULMT plane, which is established in the model as the upper surface of the implant. ULMT is positioned as maxval plus an additional arbitrary and/or fixed material offset (0.045 in this case). -
FIGS. 5 c and 5 d illustrate an alternative embodiment of theimplant 40′, having a ML curve betweendata points data points mating component 304 and key-shapedportion 344 for engagement with a reciprocal key-shaped surface in the proximal extension of a fixation screw, protrusions 345 (creating contact surfaces on the top 346 of theimplant 40′),radial cuts 347 located at theouter diameter 348 of theimplant 40′, and radius 349 (which may be formed, e.g. using an abrasive wheel) around the intersection of the outer diameter atpoint 341 and the surface comprising the patient geometry. - Referring to
FIGS. 18 a and 18 b, bone cutting or scoringinstrument 250 includes a handle (not shown), a cannulatedshaft 111 that extends through the handle, and offsetarm 140 housingadjustable blades 141. In the embodiment shown,individual cutting blades 141 are attached to offsetarm 140 either fixedly or removably, e.g. via threadedportions 142, into threadedrecesses 342 of the offsetarm 140, although other attachment means may be used. Withguide pin 20 advanced throughshaft 113 positioned on thereference axis 20A, a fixed distance from the rotational orreferences axis 20A to each of the cutting or scoringblades 141 is established. These lengths define the radii that are to be effected in the articular surface, as thescoring instrument 250 is rotated around theguide pin 20, corresponding to theprotrusions 195 on thebone contacting surface 42 of theimplant 40 creating a matching fit between the bone surfaces of the prepared target site and the bone contacting surfaces of the implant. - In an alternative embodiment, as shown in
FIG. 18 c, cutting blades are arranged oncarrier 145, configured so that it can be mounted within the slottedsurface 114 of offsetarm 112, depicted inFIG. 17 a. In another embodiment, as shown inFIG. 18 d, cuttingblades 141 can be fixedly positioned on offsetarm 140. Using the same dimensions obtained during articular surface mapping procedure, the cutting and scoringdevice 250 can be fabricated to prepare the articular surface to correspond to the implant geometry to optimize fit. In another alternative embodiment, as shown inFIG. 18 e, abone cutting instrument 352 corresponds to the alternative embodiment of theimplant 40′ illustrated inFIGS. 5 c and 5 d.Instrument 352 has a handle (not shown), a cannulatedshaft 353 that extends through the handle and through thecannulation 355, offsetarm 354 withblades protrusions 345 on thebone contacting surface 42 of theimplant 40 creating a matching fit between the bone surfaces of the prepared target site and thebone contacting surfaces 346 of theimplant 40′. - As shown in
FIG. 14 b, anangular dimension 95, relating some locating surface or feature on the hex-shapedcover 30 or on thefixation screw 10, to the fourpoints implant 40 to thefixation screw 10.Guide aperture 46 inimplant 40 is located off thereference axis 20A and may serve as the locating feature and/or as a suture passage way in the implantation procedure. Alternatively, a surface or feature created on theimplant 40, may serve to reference or align to such locating surface on the hex-shapedcover 30 or thefixation screw 10. - Additional data can be taken at the time of the initial procedure, e.g., for fabricating a non-circular implant. Additional data curves can also be defined by measuring the offsets from the
reference axis 20A and determining diameters at these offsets. The final implant geometry, although measured using circular techniques, need not be circular. - Referring to
FIGS. 10 a and 10 b, following fabrication of theimplant 40, a second procedure is performed. If a cover 30 (or plug) is in place, it is removed, exposing proximal extension 14 (or recess) or some other precision taper or engagement surface located at theproximal end 17 of thefixation screw 10 to which theimplant 40 is to be affixed. A pin having a distally mounted element orbarb 5 is placed through throughhole 16 running through the central lumen of thefixation screw 10 so that the distally mountedelement 5 is secured into the screw. The distally mountedelement 5 carries one ormore suture strands 85 that now trail from thefixation screw 10. Alternatively, a pin, braided cable, or flexible wire may also be used. However, sutures may make passing theimplant 40 through theincision 200 and subsequent handling easier. - Turning to
FIGS. 11 a and 11 b, thesutures 85 are then threaded throughguide aperture 46 of theimplant 40 and a knot orbead 49 may be created proximal to the implant, so that tensing one of the free running sutures 85 helps to advance theimplant 40 toward the proximal extension 14 (or recess) of thefixation screw 10. Alternatively, thesuture strands 85 can be passed through the central lumen or shaft of a driving rod or other instrument to aid in seating theimplant 40, and positioned in thefixation screw 10 thereafter. - If necessary, the
arthroscopic wound 200 is expanded slightly in either a vertical or horizontal direction, so that theimplant 40 may be passed through. A polymeric sleeve (not shown) positioned over the implant may prove helpful in passing the implant through the incision. As shown inFIG. 11 b, based on the size of theimplant 40, anatomy of theknee 50, and retraction of the knee, it may be necessary to position the implant in theinterchondular notch 77 as a staging area prior to final placement. By continuing to manipulate and tension thesuture strands 85, theimplant 40 can be brought coaxial to theproximal extension 14 of thefixation screw 10. - As shown in
FIGS. 15 c and 15 d, alternatively,driver 130 includeshandle 110, a cannulatedshaft 111 that extends through the handle and a cannulatedseat portion 131 attached to the end of the shaft.Tether element 135, which may comprise sutures or wire, is passed throughdriver 130 and is threaded throughimplant 40 throughguide aperture 46, connecting the implant to the driver towardseat portion 131. Theimplant 40 and thedriver 130 are then inserted arthroscopically throughincision 200 to the target site. By tensioningtether element 135 at theend 136 ofhandle 110, theimplant 40 is drawn back intoseat portion 131 ofdriver 130. By maintaining tension ontether element 135, theimplant 40 can then be controllably delivered to the prepared target site. At least the inner surface ofseat portion 131 comprises a material that can be impacted to seat theimplant 40 without damaging the implant surface. - Referring to
FIG. 12 , once coaxial, theimplant 40 can be aligned via engagement of theproximal extension 14 onfixation screw 10 and precisions taper 44 on thebottom surface 42 of the implant and any locating feature, and driven into place with aplastic driving rod 91 andmallet 95. Aprotrusion 92 of high strength material mounted at thedistal tip 93 of the drivingrod 91 may be necessary to ensure that the rod stays centered on theimplant 40 during driving. - Finally, as shown in
FIG. 13 , throughguide aperture 46 on theupper surface 41 of theimplant 40, bone cement 300 may be injected to enhance the contact surface between theimplant 40 and thesubchondral bone 100. Vents, such as milledslots 13 in thefixation screw 10, and in the walls of the implant central protrusion may be desirable to facilitate the flow of such materials. - Alternatively, guide
aperture 46 in theimplant 40 may be altogether eliminated by using an alternative implant delivery system, as shown inFIGS. 19 d through 19i, corresponding to an implant similar to that shown inFIGS. 5 c and 5 d. The alternative system comprises theimplant 40″ and awasher 361 for holding asuture 363, thewasher 361 being adapted to fit into ataper lock ring 360. Thering 360 has ataper lock portion 362 having a series ofnotches 365 along its perimeter, creatingflaps 372 that permit thetaper lock portion 362 to flex somewhat. Thetaper lock portion 362 has a diameter gradually tapering from the middle to theproximal end 364 of the ring. Thetaper lock ring 360 may also have analignment notch 386 or similar feature for properly aligning thetaper lock ring 360 with respect to key-shapedportion 344 of theimplant 40″, which is to engage with a reciprocal key-shaped surface in the proximal extension of a fixation screw, so as to seat properly the implant rotationally with respect to the defect site when it is later seated thereon. Awasher 361 is disposed between thering 360 and theimplant 40″ and has twoapertures 366 disposed in a recessedarea 367 in the center of the washer. Thesuture 363 is threaded through the twoapertures 366 to form asuture loop 368, which remains in the recessed area when the ends of thesuture 363 are pulled, so as to keep thesuture loop 368 below thetop surface 369 of thewasher 361. Theimplant 40″ has a diameter at itscenter portion 370 that is approximately equal to the inner diameter of thering 360 at itstaper lock portion 362. Thus, when tension is applied to the ends of thesuture 363, thetaper lock portion 362 of thering 360 may flex outward to receive slidably therein theimplant 40″ andwasher 361, which subsequently lock into thetaper lock portion 362 of the ring, once thecenter portion 370 of the sides of theimplant 40″ is seated within theproximal end 364 of the ring by friction fit, as shown inFIG. 19 e. It is noted that thecenter portion 370 of the sides of theimplant 40″ to be of a width permitting the implant and washer to travel slidably within thering 360 to some degree. - As shown in
FIG. 19 f, ahex nut 373 may be integrally formed in the center of thewasher 361 on itsbottom side 374, for mating with an appropriately configured tool for seating theimplant 40″. AsFIG. 19 f illustrates, theimplant 40″, along withwasher 361,ring 360, and sutures 363, is pushed through theincision 200 at the defect site. Next, as shown inFIGS. 19 g-19 i, illustrative of successive steps in the process of seating the implant, aseating tool 380 may be used to seat the implant.Seating tool 380 comprises ashaft 385, a handle 381 (which may have a throughhole 382, if the same handle and/or shaft is used with interchangeable tips for performing various functions, although a throughhole 382 is not integral to seating the implant), and tip 383 suitably configured to drive hex nut 373 (or other mating feature) and having anaperture 384 through which the ends of thesuture 363 may be threaded. Once thetip 383 of thetool 380 is introduced into theincision 200, thesutures 363 may be used as a guide for seating thetip 383 of thetool 380 onto thehex nut 373, which may be accomplished by alternately pulling on each end of thesuture 363 to toggle thetip 383 of thetool 380 back and forth. Once thetip 383 of thetool 380 is seated onto thehex nut 373, thetool 380 may be rotated in either direction to seat the implant assembly properly (comprisingimplant 40″,taper lock ring 360, and washer 361) at the defect site. This may be effected by rotatingtool 380 untilalignment notch 386 and corresponding key-shapedportion 344 of theimplant 40″ are aligned with the corresponding reciprocal key-shaped surface in the proximal extension of the fixation screw, whereby the implant should slide into place, thereby properly seating the implant rotationally with respect to the defect site. As shown inFIG. 12 with respect to the prior described embodiment, once properly seated, theimplant 40″ can be driven into place with aplastic driving rod 91 andmallet 95, and as shown inFIG. 13 with respect to the prior described embodiment, bone cement 300 may also be placed prior to the final seating of theimplant 40″ to enhance the contact surface between theimplant 40″ and thesubchondral bone 100. It should be understood that thetaper lock ring 360,washer 361, and sutures 363 described with respect to this embodiment allow the implant to be noncannulated but still easily handled. These elements are not required to be constructed as illustrated herein, and may be replaced by adhesive components, suction components, or other components serving the same function. - As
FIGS. 21 and 22 illustrate, a unitary (one-piece)implant 400 may also be constructed, thereby obviating the need for a fixation screw, taper lock ring, washer, and suture. In this embodiment,implant 400 has key-shapedportion 401 for engagement with a reciprocal key-shapedsurface 411 in anaperture 412 at thedefect site 410, a plurality of barbs 402 (or other mating features, e.g., one or more threads, ribs, fins, milled slots, tapered distal features, features to prevent rotational movement of the implant, or features to increase friction between the implant and the aperture at the defect site) for producing outward tension within theaperture 412 at thedefect site 410 and for increasing the contact surface area of theimplant 400 with respect to theaperture 412 at thedefect site 410. In this embodiment, anaperture 412 having a key-shapedsurface 411 or other feature for mating with the implant is created directly in thedefect site 410, by boring, abrasion, or other techniques for forming an appropriately shaped aperture in thechondral bone 410 for receiving animplant 400 having a corresponding key-shaped orother mating feature 401. It should also be recognized that, in this or other embodiments, the fixation screw could be replaced with a tensioned member attachment, e.g., anchored to the distal femoral cortex. Alternatively, the fixation screw could be configured as a guide wire, only to define the axis AA corresponding to an axis about the point of origin in the implant to be used (as shown inFIGS. 14 c and 19 c), but not to provide mechanical anchoring to or for the implant. -
FIG. 23 illustrates other alternative embodiments for an implant consistent with the invention, showing a perspective view of the components of an exemplary composite implant, in one embodiment of the present invention. As shown,implant 500 comprises top 501 and bottom 502 portions.Top portion 501 has abottom surface 503 which may be glued, welded, bonded, or otherwise attached totop surface 504 ofbottom portion 502, whilebottom surface 505 ofbottom portion 502 comprises the patient geometry and is the load-bearing surface of the implant, as set forth hereinabove. Top 504 and bottom 505 surfaces of thebottom portion 502 may comprise, in whole or in part, bioengineered material, whiletop portion 501 may comprise a material such as titanium. In such a configuration,top portion 501 may be fabricated and/or manufactured (e.g. in large quantities) as a universal, generic, standard supply item for medical practitioners, which merely needs to be attached to a custom-machinedbottom portion 502 comprising the patient-specific geometry.Surfaces - Further composite implant embodiments are illustrated in
FIG. 24 , whereinimplant 600 comprises the patient-specific geometry 603 and a uniform thicknessmaterial bottom portion 602 comprising the bottom or bearingsurface 606. Thebottom surface 603 oftop portion 601 mates with thetop surface 604 ofbottom portion 602, and surfaces 603 and 604 may be flat or may comprise other mating features, shapes or configurations.Lip 605 ofbottom portion 602 has an inside diameter substantially the same as the outside diameter oftop portion 601, so thattop portion 601 fits slidably intobottom portion 602, whereby the twoportions Bottom surface 606, being of uniform thickness, reflects the patient-specific geometry which surface 603 comprises and is the load-bearing surface of the implant. - Other materials from which an implant consistent with the invention may be constructed, in whole or in part, include ceramic, e.g. aluminum oxide or zirconium oxide; metal and metal alloys, e.g. Co—Cr—W—Ni, Co—Cr—M, CoCr alloys, CoCr Molybdenum alloys, Cr—Ni—Mn alloys, powder metal alloys, 316L stainless steel, Ti 6Al-4V ELI; polymers, e.g., polyurethane, polyethylene (wear resistant and cross-linked), thermoplastic elastomers; biomaterials, e.g. polycaprolactone; and diffusion hardened materials, e.g. Ti-13-13, Zirconium and Niobium. Coatings used may include, e.g., porous coating systems on bone-contacting surfaces, hydrophilic coatings on load-bearing surfaces, hydroxyapatite coatings on bone-contacting surfaces, and tri-calcium phosphate on bone-contacting surfaces. Additionally, components of the invention may be molded or cast, hand-fabricated, or machined.
- Alternatively, measurement methods may be utilized whereby radius measurements are taken with respect to an axis AA corresponding to an axis about the point of origin in the implant to be used (as shown in
FIGS. 14 c and 19 c). The technique is used in reverse, whereby aiming devices are used to place axis AA with respect to prefabricated generic-geometry implants. - It is noted that, although the invention is herein described as utilizing a single reference axis, multiple reference axes may be used for measuring, mapping, or cutting a single defect or an articular surface having multiple defects, as well as for fabricating a single implant, or multiple implants for a single articular surface, consistent with the invention. In other embodiments, methods for mapping the defect and/or articular surface other than those described hereinabove are possible, e.g., MRI or CT scanning, fluoroscopy, ultrasound, bone density, other stereotactic systems, nuclear medicine, or other sound or light wave-based imaging methods.
- It is further noted that, although the invention is described herein as utilizing the specific geometry of a patient's articular surface to fabricate an implant for that patient, it is contemplated that data from a plurality of patients may be analyzed statistically and utilized in fabricating and/or manufacturing (e.g. in large quantities) one or more universal, generic, or standard supply item type implants for medical practitioners to use in a procedure consistent with the invention. For such implants, as well as for patient-specific implants as described herein, pre- or post-implantation trimming may be required to correct for minor variations that may occur as between the implant and the subchondral bone (or other articular surface).
- It should be understood that, although the various tools described hereinabove, e.g., for measuring, cutting, and seating, are described as separate devices, a single handle, shaft and/or instrument may be configured to serve as a universal mounting tool for a series of devices for performing various functions consistent with the invention.
-
FIGS. 27 a-48 depict another exemplary embodiment of the present invention. In this embodiment a generic bone implant (or set of standardized implants) is created (or selected) based on developing an axis normal to the surface and collecting only one data point. In the above-described embodiments, a non-normal axis was utilized, and four data points were required to develop ML and AP curves. Further, a generic cutting tool is used to cut the bone at this site to a point where a generic implant can be used. Several improved tools relating to the procedure for using such an implant (as well as for using implants as described hereinabove) are further described in this section and illustrated in the corresponding figures. -
FIG. 27 a depicts an exemplarydrill guide device 700 according to this exemplary embodiment. Theguide 700 includes acontact surface 702 of known diameter d on thedistal end 708 of the guide, where diameter d is generally the width of the widest portion of the site of the lesion. Thedistal end 708 of the guide is generally a hollowed-out toroidal structure attached to ahandle 706. Acentral lumen 704 runs the length of the guide from the attachment point of thedistal end 708 to thehandle 706, and through thehandle 706. The guide device may be constructed in a number of other ways, including, e.g., adistal end 708 comprising a transparent material, e.g., polycarbonate or another clear plastic. For example, as shown inFIG. 27 b, aguide device 700′ may comprise adistal end 708′ (which could comprise either an opaque or a transparent material) having a plurality ofcutaway areas 743 to improve visibility and the accuracy of drill location with respect to the site of a lesion. The guide device may also comprise a tripod-like construction, or other construction comprising fins, or projections. It should be noted that, instead of a central lumen being used to locate the working axis, a cylindrical bore located at some distal location of the guide may serve to create a working axis that is not necessarily coaxial to the handle or connecting shaft of the instrument. - Referring now to
FIGS. 28 a and 28 b, the present embodiment operates on the assumption that to a first approximation an anatomical model of some articular surfaces (e.g., knee, hip, etc.) can be assumed to be locally spherical. In other words, as shown inFIGS. 28 a and 28 b, the AP plane and ML plane, respectively, are depicted, wherein each corresponds to a model of the articular surface of a femoral region. These figures break up these cross-sections into a plurality of radii of arcs defining the articular surface, i.e., R1-R4 in the AP plane, and R5-R7 in the ML plane. In this embodiment, the inventors herein have found that surfaces in some regions can be assumed to be substantially locally spherical. Thus, for example, the present embodiment assumes that R3 approximately equals R6 (i.e., R3 is within 50% of R6). Under these assumptions, a normal axis can easily be developed. Once developed, one data point then needs to be defined to obtain the relevant geometry of an implant, as will be described below. If R3 is not within 50% of R6, an alternative method for developing an axis normal to the surface of the lesion site, as described hereinbelow with reference toFIGS. 49-53 , may be used. -
FIGS. 29-34 depict the use of the drill guide, the generic implant, and procedures therefor, according to this exemplary embodiment. InFIG. 29 , thedrill guide 700 is brought up to alesion site 712 of thearticular surface 710. Theguide 700 is positioned so that thedistal end 702 covers thelesion site 712, such that the contact surface of thedistal end 702 makes contact at a plurality of points around thelesion site 712 on thearticular surface 710. As shown inFIG. 30 , with slight pressure theguide 700 becomes stable and fixed on thearticular surface 710. Once seated in position, aguide pin 714 is driven through the central lumen of the guide to create a working axis that is generally normal to thearticular surface 710 at the point of contact of the guide pin. AsFIG. 31 illustrates, a standard bore drill (not shown) can be placed over theguide pin 714 to create apilot hole 716 for the screw (not shown). - With reference now to
FIG. 32 , as with the previous embodiments described above, ascrew 720 is driven into thepilot hole 716. Acap 722 having amale component 719 adapted to mate with thefemale taper 718 of thescrew 720 is placed on thescrew 720. The screw is driven to the appropriate depth, such that the top surface of thecap 722 is substantially aligned with thearticular surface 710, within thelesion site 712, thereby ensuring congruency of the implant to the joint. Turning now toFIG. 33 , thecap 722 is removed, and arod 730 having amating taper 731 on its distal tip is inserted into thescrew 720. Theguide 700 is positioned over therod 730 so that thedistal end 702 covers the lesion once again. As illustrated inFIG. 34 , since the length of therod 730 and the length of theguide 700 are known, a measurement of the exposed end length of the rod (l) may be taken. This will provide the information needed with respect to the implant geometry, by indicating the distance between the seating depth in the screw and the tangent point of the implant surface. As shown inFIG. 35 , since the axis, z, is defined (by the drill guide) as normal to the surface of the implant at a plurality of points, all dimensions defining the AP and ML curves may be assumed to be equal, such that only one dimension, l, is left to define the implant geometry. Variations from knee to knee and within a knee may be reflected in changes in l. For example, theimplant 736 ofFIG. 36 may be compared to theimplant 737 ofFIG. 37 . Forimplant 736 ofFIG. 36 , the value of l1 represents a relatively “flat” region on the articular cartilage, where the radius of the arc RAC1 is a relatively large number. However, forimplant 737 ofFIG. 37 , the value of l2 represents a more curved region on the articular cartilage, where the radius of the arc RAC2 is a smaller number than RAC1. As indicated by clinical data, there is a range of values for l that suggests 5 to 6 values of l that will fit a majority of people. Thus, generic, off-the-shelf sized implants may be made. A single procedure technique involving establishing the normal axis, measuring l, and selecting the appropriate size implant is therefore feasible. - As illustrated in
FIG. 38 , an exemplary cutting or reaming tool 740 (e.g., as described hereinabove with respect toFIGS. 15 b and 16) is used to prepare thelesion site 712 to receive the implant (not shown). The cutting or reamingtool 740 may be configured so that, when coupled to the axis defined by the guide pin, it can be used for cutting operations. Thetool 740 may have a cannulated shaft and a distal offset arm having a cutting or blade surface (not shown) having a radius corresponding to the radius of the implant to be used, such that the articular cartilage may be circumscribed by rotation of thetool 740 for cleanly cutting the surrounding articular cartilage in preparation for receiving the implant. Thetool 740 may be configured so that, when coupled to the axis defined by the guide pin, it can be used for cutting operations. The proximal face of thescrew 720 may serve as a depth stop for the proximal portion of thetool 740, thereby defining a cutting/reaming depth corresponding to the thickness of the implant, l. - Those skilled in the art will recognize that the cutting tool may be motorized in certain embodiments, and/or alternatively, as illustrated in
FIG. 39 , anexemplary cutting tool 744 may comprise a cannulatedshaft 749, acircular blade portion 745 having aleading edge 746 comprising a blade surface turned on the distal-most portion. Such atool 744 may further comprise ahandle portion 747 and may be adapted to be turned by hand by the operator of the tool by means of rotating thehandle 747, or alternatively, may be motorized in certain embodiments. -
FIG. 40 illustrates anexemplary cleaning tool 770 for cleaning the female taper (not shown) of thescrew 720 prior to delivery of the implant. Thedistal end 771 of anexemplary cleaning tool 770 comprises a semi-rigid material formed into a shape adapted to enter into the female taper of thescrew 720 and be manipulated by the operator of the tool, to remove tissue or other debris therefrom, thereby ensuring a good mate of thefemale taper 720 of the screw and the male taper of the implant to be delivered (not shown). -
FIGS. 41-43 illustrate anexemplary suction tool 760 for holding the implant by means of a suction force and delivering it to the lesion site, as well as the steps of an exemplary procedure for using thesuction tool 760 to deliver an implant. As illustrated inFIG. 41 , anexemplary suction tool 760 comprises anelastomeric suction tip 761 at itsdistal portion 767, aproximal surface 768, aninlet 762 for mating with asuction tube 763 connected either to a hospital wall suction supply 764 or other suction system, and a switch orvalve 765 for controlling the suction force. AsFIG. 42 illustrates, when the suction force at theelastomeric suction tip 761 is activated by the switch orvalve 765, theimplant 742 is held in place, and thus, thesuction tool 760 may be used to hold the implant prior to, and during, the delivery thereof. As shown in the cross-sectional view ofFIG. 43 , thedistal portion 767 of anexemplary suction tool 760 may comprise a rigid tip 766 (which may comprise, e.g., plastic material) disposed within theelastomeric suction tip 761. Force may be applied to the rigid tip 766 (e.g., by striking or pressing on theproximal surface 768 of the tool 760) in order to seat theimplant 742 within the lesion site, once themale taper 769 of theimplant 742 and its corresponding mating component(s) 778 are properly aligned with the female taper of the screw (not shown) and its corresponding mating component(s). Since thesuction tip 761 is elastomeric (e.g., rubber), upon application of such force, the material will compress, allowing impact to be transferred to theimplant 742 for purposes of seating it. It is noted that, in addition to its utility in delivering an implant, asuction tool 760 as described herein (or a suction tool similar thereto) might also be used at some point during the process of removing an implant (e.g., in the event the implant is not fully seated). -
FIG. 44 illustrates anexemplary implant 742 driven into thelesion site 712 of thearticular surface 710 once thesite 712 has been sufficiently reamed or cut. -
FIG. 45 illustrates an exemplary implant removal orrevision tool 750 comprising ashaft portion 751 and adistal portion 753, andFIG. 46 is a cross-sectional view illustrating theexemplary tool 750 with a removedimplant 742 being held in place therein. As shown, thedistal portion 753 of thetool 750 may comprise an approximately cylindrical structure with acircular blade portion 752 having aleading edge 758 comprising a blade surface turned on the distal-most portion and alip portion 755 disposed proximally with respect to theleading edge 758. A plurality ofslits 754 parallel to the longitudinal central axis of thedistal portion 753 are disposed along the length of the cylindrical structure, so as to permit sufficient outward expansion of thedistal portion 753 to accommodate the top edge of theimplant 742 therein. Thus, when thedistal portion 753 of thetool 750 is forced onto animplant 742 to be removed, and driven down over theimplant 742, thedistal portion 753 will snap/lock into place once thelip portion 755 of thedistal portion 753 of thetool 750 passes the top edge of theimplant 742 being removed, thereby holding theimplant 742 in place within thedistal portion 753 of thetool 750, as shown inFIG. 46 . At this point, a device such as a slap-hammer or slide hammer (not shown) may be used to unseat theimplant 742. An exemplary such device may comprise a shaft having a weight slidably disposed thereon, wherein one end of the shaft is connected to the proximal end (not shown) of thetool 750 and the other end of the shaft comprises a stop for preventing the weight from moving off the shaft, and wherein the weight is propelled away from its connection point with the proximal end of thetool 750, such that it stops abruptly at the stop and exerts a pulling force on the implant. -
FIGS. 47 and 48 illustrate an exemplary alternatively-keyed embodiment of thescrew 720′ (c.f.,key feature 315 ofscrew 10′, as shown inFIG. 9 c) and the exemplary alternatively-keyedimplant 742′ to which it is adapted to mate. As shown, themale taper 769′of theimplant 742′ is coupled at its distal end to an offsetmating feature 778′ for mating with a corresponding offsetmating feature 779 of thescrew 720′. Themating feature 778′ of theimplant 742′ comprises a generally cylindrical structure (and may further comprise a rounded or chamfereddistal end portion 777′ and/or other geometric features, i.e., recesses and/or protrusions) and is both offset from the central longitudinal axis of, and diametrically smaller than, themale taper 769′ of theimplant 742′. AsFIG. 48 illustrates, a generally cylindrical recessed mating feature 779 (or similar mating recess(es) and/or protrusion(s), e.g., a rounded or chamfered distal end portion 780) corresponding to the offsetdistal mating feature 778′ of theimplant 742′ is disposed within the innermost portion of thefemale taper 718′ of theimplant 742′, and offset from the central longitudinal axis of thefemale taper 718′. Thefemale mating feature 779 of the screw is provided to mate with the offset maledistal mating feature 778′ of theimplant 742′, so as to seat thetaper 769′ of theimplant 742′ at a fixed location within thescrew 720′, thereby preventing rotation of theimplant 742′ with respect to thescrew 720′. Along with the mating features 778′, 779, the taper structures provided may serve to prevent movement of theimplant 742′ with respect to thescrew 720′in all directions. Ascrew 720′ consistent with the present invention may comprise a titanium alloy, e.g., a 316L stainless steel alloy or a cobalt-chrome alloy. -
FIGS. 49-53 illustrate an alternative method for developing an axis normal to the surface of the lesion site using a biaxial measuring tool. This method has particular utility for lesion sites where the radii of arcs defining the articular surface, RML and RAP, are different, i.e., the region is not locally spherical. (This would be the case, e.g., if R3 is not within 50% of R6, as illustrated inFIGS. 29 a and 29 b and described hereinabove.) To develop an axis normal to the surface, abiaxial measuring tool 800 is provided. Thetool 800 comprises anouter shaft 805 coupled fixedly to anouter component 801 having a set ofarms 803, and aninner shaft 806 slidably disposed within theouter shaft 805, wherein the inner shaft is coupled fixedly to aninner component 802 having a set ofarms 804. Thearms arms FIGS. 49-53 , wherein the distal portion of eacharm contact portions 808. Thecontact portions 808 may be, e.g., as shown, one of four arcuate sections of a generally toroidal member (which may be solid or hollow) having a generally circular cross-section. (The lengths of the arcuate sections do not necessarily need to be equal to one another, e.g., as illustrated in theexemplary contact portions 808 ofFIGS. 49-53 , the arcuate lengths of thecontact portions 808 corresponding to theinner component 802 are shorter than thosecontact portions 808 corresponding to theouter component 801.) Theinner shaft 806 may be biased forward so as to tend to extend from theouter shaft 805, or may alternatively be advanced manually without spring bias. Theinner component 802 is slid proximally or distally with respect to theouter component 801, until all of thecontact portions 808 make contact with the articular surface (not shown). In this manner, the articular surface curvatures may be separated into AP elements and ML elements, such that four separate contact points may be extrapolated from the fourcontact portions 808, based on the relative positions of the inner 802 and outer 801 components, and an axis normal to the surface of the lesion site may be defined. The shaft of thetool 800 may be cannulated (not shown), so as to allow a guide pin or wire (or a boring tool) to pass therethrough and into the articular surface, as described hereinabove with respect toFIGS. 27 a to 31. As shown inFIG. 53 , if the inner 802 and outer 801 components are aligned such that the fourcontact portions 808 meet to form a complete toroidal member or ring, the articular surface must be locally spherical, i.e., RML and RAP (as shown inFIG. 49 ) are equal, and it is therefore not necessary to use thebiaxial tool 800. - It should be noted that, alternatively, contact surfaces may be constructed of some pliable, or malleable material(s) so that independently moving rigid mechanical members are not necessary. As long as the contact surfaces provide a normalizing force to some central shaft when the contact surfaces are applied to the articular surface, a normal axis could be defined.
- In another embodiment, this biaxial guide could be replaced by a series of sized “trials” or gauges of predefined surfaces of varying dimensions, which are simply pressed onto the articular surface to visually determine an appropriate fit. These gauges may resemble an implant, as described herein, without any features (e.g., fixation element or screw) on the underside, and may contain a handling tab or other element for holding the gauge. The contact surfaces of these gauges may have a circular cross section, an ovular cross section, or another cross-section comprising a plurality of points to surround a defect in an articular surface, and the plurality of points may or may not lie in the same plane. Although they may be less precise or less accurate than other measuring methods described herein, it is contemplated that implant selection could be made directly from these gauges.
-
FIGS. 54-61 illustrate an exemplary digital measuring system consistent with the present invention. As shown, thesystem 810 comprises abase unit 811 coupled to thehandpiece 812 via acable 813. As described further hereinbelow, thebase unit 811 may comprise atear strip 814 in or on the chassis for detaching a printed paper tape comprising measurement data. Such a system may reduce or eliminate potential for surgical or other human error with respect to the implementation of the present invention. -
FIG. 55 is an exploded view of anexemplary handpiece 812 in a digital system consistent with the present invention. The linear measuring elements of thehandpiece 812 are nested concentrically and coaxially to the rotary measuring elements, so that when theprobe assembly 818 is translated and rotated with respect to themain body 822 of the handpiece, the θ and z dimensions are simultaneously recorded. Thehandpiece 812 comprises amain body 822 containing alinear reading head 813 coupled to alinear reader 814, alinear index strip 815, arotary reading head 821 coupled to arotary reader 816, and arotary index strip 817. Theprobe assembly 818 comprises acontact tip 819 coupled to aninner shaft 820 running along the length of thehandpiece 813 disposed within themain body 822. Theshaft 820 comprises amating feature 834 at its distal end that is keyed to fit in the mating feature of an implanted screw, such that theshaft 820 provides a rotational axis. Theshaft 820 is rigidly connected to themain body 822 of thehandpiece 812 via anut 823 at its rear. Thehandpiece 813 is coupled to, and transfers motion both rotationally and axially from, thecontact tip 819 via theshaft 820. In this manner, the linear 815 and rotary 817 strips, which may comprise, e.g., mylar polyester film having thereon a very fine printed pattern, pass through the linear 813 and rotary 821 reading heads, respectively, such that theheads strips contact tip 819. - Exemplary strips and heads may include those manufactured by U.S. Digita™ Corporation of Vancouver, Wash., USA.
FIG. 55 a is a cutaway view illustrating an exemplary printedlinear index strip 815 passing through an exemplarylinear head 813 for reading, andFIG. 55 b is a cutaway view illustrating two alternative exemplary printed rotary index strips 817, 817′ of varying sizes passing through an exemplaryrotary head 821 for reading.FIG. 55 c illustrates an exemplarylinear index strip 815 comprising concentric “bullseye” circles 830,reference lines 831, atext area 832, and apattern area 833.FIG. 55 d illustrates an exemplaryrotary index strip 817 comprising anopaque area 823,index areas 824, apattern area 825, atext area 826,crosshairs 827, concentric “bullseye” circles 828 and acentral aperture 829. - Turning now to
FIGS. 56 a and 56 b, arotational groove 840 and alinear groove 841 are provided on thehandpiece 812, such that theprobe assembly 818 may slide onto theshaft 820 of thehandpiece 812 and snap into the linear 841 and rotational 840 grooves. -
FIGS. 57 and 58 illustrate top and side views, respectively, of the assembledexemplary handpiece 812. -
FIGS. 59 and 60 illustrate top and side cross-sectional views, respectively, of the assembledexemplary handpiece 812. -
FIG. 61 illustrates a cutaway view of anexemplary base unit 811 in an exemplary digital measuring system consistent with the present invention. Thebase unit 811 comprises a power supply 850 (the system may be battery or AC-line powered), apaper roll 851, athermal printer 852, afeed loop dowel 853 for threading thepaper roll 851 into thethermal printer 852, a set of controls orbuttons 854, and one or more displays 855 (e.g., LED/LCD). Thebase unit 811 further comprises appropriate hardware and/or software to compare measured values to known values, as well as to compare sweeps to one another to ensure procedural accuracy. Further, thedisplays 855 and/or paper printouts from thethermal printer 852 may be adapted to display to the user, based on measured data, the ideal size of the generic implant to use. If a custom implant is required, a printout of the data set may be generated using theprinter 852. Thebase unit 811 may further comprise other means of recording data (not shown), e.g., floppy disk, hard disk, memory/flash card, etc., and may further comprise appropriate hardware to provide output signals (e.g., via RS-232, USB, etc.) to external hardware. Instead of the strips, heads, and other recording elements described in the exemplary digital system hereinabove, other digital measurement methods may be used, including reflective light or sound methods, and percutaneous methods (e.g., using a hypodermic needle in conjunction with an MRI, CT, ultrasound, or other scanning method, wherein the needle or other handheld device comprises sensing elements for mapping the articular surface). - It should be noted that in the digital measuring system and method described hereinabove (as well as any of the mapping/measuring techniques herein), a second (or third, etc.) set of data points may be taken, and the subsequent set(s) of data points compared with the original data points taken, to reduce the margin of error from taking only a single set of data points. Thus, a software algorithm in a system or method consistent with the invention may comprise appropriate routines to effect such comparisons, for error reduction purposes.
- Further Alternative Implant Structures
- Turning to
FIG. 62A , a top perspective view of an alternativeexemplary implant 6200 that includes aprotrusion 6204 that extends at least partially around the periphery of the device. In the exemplary embodiment, theprotrusion 6204 is provided to cover at least a portion of an un-excised portion of articular surface, however, this is not a structural requirement of the device of the present embodiment. With a substantiallyround implant 6200 as illustrated inFIG. 62A , theprotrusion 6204 may surround the entire circumference of theimplant 6200 and may extend radially outward from the center point P of theimplant 6200. Alternatively, with other round and non-round implants as detailed further herein, the protrusion may be selectively placed around portions of the perimeter of the implant. - The
implant 6200 may include aradial ring 6220 formed on the bone-facing distal surface of theimplant 6200. The radial ring may be dimensioned to the excised portion such that the arcuate shapedouter side surface 6223 defines the size of the cut portion in the articular surface. Theradial ring 6220 may have a width r4 in a radial direction from the center point P of theimplant 6200 and a height h1 in the z-axis direction. The arcuate shapedouter side surface 6223 of theradial ring 6220 may be a radial distance r1 from the center point P of theimplant 6200. Theradial ring 6220 may also include a plurality ofradial slots 6224 spaced evenly along the circumference of the ring in order to assist with anchoring of the implant to the bone. - Turning the
FIG. 62B , a cross-sectional view of theimplant 6200 taken along the line B-B ofFIG. 62A is illustrated. Theradial ring 6220 is positioned relative to the center point P as it would be with other such implants earlier described, e.g., the circular implant illustrated inFIGS. 25 and 26 . Theprotrusion 6204 is formed by anextension 6206 from the radial ring and anextension 6232 of the load bearing proximal surface. These extensions join at 6214 to define theprotrusion 6204. - The top or
proximal surface 6232 of theprotrusion 6204 may simply be an extension of the proximal orload bearing surface 6205 of theimplant 6200. As such, theprotrusion 6204 extends beyond the outsidearcuate edge 6223 of theradial ring 6220. Accordingly, theprotrusion 6204 has a width r3 at any one point along the perimeter of theimplant 6200 equal to the difference between the radial distance r2 from the center point P of the implant to theexterior edge 6214 of theprotrusion 6204 and the radial distance r1 from the center point P of the implant to the outsidearcuate edge 6223 of theradial ring 6220. The width r3 of the protrusion may be a consistent width around the entire perimeter of the implant or may vary along the perimeter as conditions of the proximate articular cartilage vary. - The
protrusion 6204 is also defined by a bone-facing ordistal surface 6206 that may extend to cover a portion of the un-excisedarticular surface 6218. Thedistal surface 6206 of theprotrusion 6204 may be shaped in any number of ways to match the mating edge of thearticular surface 6218 proximate to thedistal surface 6206 of therim 6204. As illustrated inFIG. 62B , thedistal surface 6206 may have an arcuate shape for this purpose. - Turning to
FIG. 62C , a side perspective view of theimplant 6200 is illustrated. As illustrated, theprotrusion 6204 may be advantageously configured to follow the mapped contour of the mating articular surface, e.g., articular cartilage. In other words, thedistal surface 6206 of therim 6204 may vary along the perimeter of the implant in order to match the edge of the articular cartilage which it covers based on mapping configurations as previously detailed herein. - Turning to
FIG. 63A , a side perspective view of another alternative embodiment of animplant 6300 is illustrated. In this embodiment, theimplant 6300 includes aprotrusion 6304 withprotuberances protrusion 6304, and may be used, for example, to secure the target articular surface proximate to thedistal surface 6306 of theprotrusion 6304. Theprotuberances protrusion 6304. The protuberances may also have barbs or teeth (not shown) to enhance grip to the articular surface. In the embodiment ofFIG. 63A , the interface between theimplant 6300 and a fixation device, e.g., a screw, may need to be revised in order to allow more axial range of forgiveness for interlock of the protuberances to the articular cartilage. - Turning to
FIG. 63B , a cross-sectional view of theimplant 6300 taken along the line B-B ofFIG. 63A is illustrated. As illustrated, theprotuberances distal portion 6306 of therim 6304 in order to more securely couple theprotrusion 6304 to the un-excised portion of thearticular surface 6318 proximate to theimplant 6300. - Turning to
FIG. 64A , another alternative embodiment of animplant 6400 is illustrated. In the embodiment ofFIG. 64A , the proximal orload bearing surface 6405 has aperimeter edge 6406 that is configured to be separated a predetermined radial distance r5 from a surroundingarticular surface 6418 when the implant is properly seated in a patient. As such, acavity 6428 or trough defined by abottom cavity surface 6408, aside cavity surface 6406, and the cut side ofarticular surface 6418 is formed. - Turning to
FIG. 64B , a cross sectional view of theimplant 6400 ofFIG. 64A taken along the line B-B is illustrated which further shows the details of such acavity 6428. Thearticular cartilage 6418 may then settle or remodel into thecavity 6428. Oneside 6406 of thecavity 6428 may be arcuate shaped and may be depressed a predetermined distance relative to theload bearing surface 6405. The dimensions of the cavity may be large enough to permit sufficient space for thearticular cartilage 6418 to remodel or settle into such cavity, but small enough so thatarticular cartilage 6418 may remodel into such space within a reasonable time frame after seating of theimplant 6400. - Turning to
FIG. 65A , anotheralternative implant 6500 embodiment consistent with the invention is illustrated. Thisimplant 6500 has a non-round or elongated shape. The concept behind this geometry of the implant is to provide extension of the implant in the AP plane without being constricted by the width of the condyle. In other words, the implant of this embodiment may be derived from a circular implant that has a radius that extends beyond the width of the condyle in the ML plane. The circular implant structure may then be truncated along the “sides” that form the edges of the condyle in the ML plane, thus forming the elongated implant depicted inFIG. 65A . Theimplant 6500 has a least twoside surfaces implant 6500 has an arc ArcAP and an arc ArcML that represent the curvature of theproximal surface 6505 of theimplant 6500. - The
implant 6500 has a length from an anterior end of the implant to a posterior end of the implant along a segment of the arc ArcAP. The implant also had a width from the medial end of the implant to the lateral end of the implant along a segment of the arc ArcML. Obviously, the arc segment in the ML plane is less than the arc segment in the AP plane, for the non-round or elongate shapedimplant 6500. - The
implant 6500 may also have one concentric arcuate shapedside surface 6517 located opposite another concentric arcuate shapedside surface 6519.Such side surfaces Such side surfaces implant 6500 also has a length 16500 in a plane defined by the maximum distance between two points on the arcuate shapedside surfaces - The implant also may also have two other opposing
side surfaces Such surfaces side surfaces implant 6500. Having such an elongated or non-round implant allows the treatment of a greater variety of articular defects, and may also be effective in reducing fray between the perimeter of the cut articular cartilage and theimplant 6500. - When articular surface mapping is done using one axis normal to the surface of the implant, two measuring probes may be utilized. One measuring probe may be utilized to map the points for the AP curve and another smaller diameter measuring probe may be utilized to map the points for the ML curve so as it is revolved its captures the data for points M and L. The
implant 6500 may be defined by the ML curve swept along the AP curve as previously described herein. Alternatively, the implant may be a generic bone surface implant as previously described with reference toFIGS. 27 a-48 assuming a locally spherical articular surface site. - Turning to
FIG. 65B , animplant site 6511 may be created by excising a portion of thearticular surface 6508 to match theimplant 6500 shape ofFIG. 65A . As such theimplant site 6511 may have two arcuate shapedside surfaces side surfaces implant 6500. Twoother side surfaces implant 6500. - The
implant site 6511 may be generated a number of ways. In one instance, a reaming orcutting tool 6524 having acircular blade portion 6526 with a blade diameter dblade greater than the width Wsurface of thearticular surface 6608 to which the implant will be affixed may be utilized. Anotherexemplary reaming tool 744 is discussed more fully with reference toFIG. 39 . Thecircular blade 6526 of thereaming tool 6524 is depressed into thearticular surface 6508 until it contacts the depth stops in the screw as previously described herein. A straight line distance dAP is created since the blade diameter dblade is greater than the width Wsurface of thearticular surface 6608. - This straight line distance dAP in an AP plane is dependent on a number of factors including the depth of the
cutout bottom surface 6510 compared to the top orproximal surface 6505 of the implant, and the shape of the surroundingarticular surface 6508 to which the implant will be applied. Once properly reamed, theimplant site 6511 ofFIG. 65B should have a cross sectional view as illustrated inFIG. 65C . As with prior cutouts, thecutout bottom surface 6510 will match the undersurface of theimplant 6500. - Turning to
FIG. 65D , a perspective view of the elongated ornon-round implant 6500 being placed into theimplant site 6511 of thearticular surface 6508 is illustrated. Theimplant 6500 may be placed and set into theimplant site 6511 using any variety of tools and methods as previously discussed herein. The arcuate shapedside surfaces edges other side surfaces edges - In one exemplary method of setting the
non-round implant 6500, the diameter φ1 of one measuring probe may be used to define the diameter dblade of around blade 6526 from areaming tool 6524. As such, the diameter φ1 of such a measuring probe may typically be equal to the diameter dblade of theround blade 6526 from areaming tool 6524. The diameter φ2 from another measuring probe may defines the ML curve and hence the arcuate width of the implant along that curve. - Turning to
FIG. 66A , a top perspective view of another alternative exemplaryelongated implant 6600 having twoprotrusions protrusions elongated implant 6600 when seated in an excised portion of an articular surface. -
Protrusion 6605 is generally similar toprotrusion 6606 so for clarity, description herein is made toprotrusion 6606 only.Protrusion 6606 may extend radially from the arcuate shapedside surface 6623 to cover anun-excised portion 6634 of articular surface 6608 (seeFIG. 66B ) proximate to thearcuate side surface 6623 of theimplant 6600. - The
protrusion 6606 has a width r3 at any one point along the arc of the implant on the anterior side equal to the difference between the radial distance r2 from the center point P of the implant to theexterior edge 6640 of theprotrusion 6606, and the radial distance r1 from the center point P of the implant to the outsidearcuate side surface 6623. The width r3 of the rim may be a consistent width around the perimeter of the arc or may vary as conditions of the mating articular cartilage vary. Although not illustrated, theprotrusions elongated implant 6600 may also have protuberance to more securely affix the rim to the articular cartilage as described and illustrated earlier with reference toFIGS. 63A and 63B . - Turning to
FIG. 66B , a top perspective view of the elongated ornon-round implant 6600 havingprotrusions implant site 6611 of thearticular surface 6608 is illustrated. Theimplant 6600 may be placed and set into theimplant site 6611 using any variety of tools and methods as previously discussed herein. Theprotrusion 6606 may cover and anchor a portion of thearticular cartilage 6634 proximate to the cut edge of theimplant site 6611 at the anterior side, while theprotrusion 6605 may similarly cover and anchor a portion of the articular cartilage proximate to the cut edge of theimplant site 6611 at the posterior side of the implant. - Turning to
FIG. 67 , a top perspective view of animplant 6700 being placed into asection 6707 of anarticular surface 6708 is illustrated. Alternatively, in another method consistent with the present invention, the articular cartilage of thearticular surface 6708 is not cut. As such, fraying of the articular cartilage at a cut edge may be avoided. - In other words, the
implant 6700 is mapped and placed within the borders of the existing defect. As such, the portion of the articular surface excised for the implant site has a surface area less than the surface area of the defect. Such an alternative method may be accomplished by any of the variety of methods discussed herein. For instance, one method may include locating the defect in the articular surface, establishing a working axis substantially normal to the articular surface and substantially centered within the defect, excising a portion of the bone surface adjacent to the axis thereby creating animplant site 6711, and installing the implant in the implant site where a least aportion defect 6707 proximate to the posterior side may, of course, have a different shape or configuration as that portion of thedefect 6709 proximate to the anterior side of theimplant 6700 when seated. - Turning to
FIGS. 68A-68D , animplant 6800 consistent with the invention may be provided with a feature to promote and encourage remodeling of the articular cartilage onto theproximal surface 6806 of theimplant 6800. Such a feature may be an indentation in theproximal surface 6806 of the implant that may be of continuous or noncontiguous shape. In one exemplary embodiment as illustrated inFIGS. 68A and 68B , the indentations arecontinuous grooves proximal surface 6806 of the implant from one side to another.Such grooves holes 6809 to communicate to the bone surface.FIG. 68B is a cross sectional view of theimplant 6800 taken along the line B-B ofFIG. 68A illustrating the square shaped cross sectional geometry of theexemplary grooves - Turning to
FIG. 68C , another indentation of theproximal surface 6806 may be one ormore spaces perimeter edge 6830 of theproximal surface 6806 by the particular geometry of the implant'sproximal surface 6806.Such edge spaces proximal surface 6806 of theimplant 6800. - Turning to
FIG. 68D , a top perspective view of theimplant 6800 seated in anarticular surface 6816 is illustrated. As illustrated, indentations such asgrooves edge spaces portion 6818 of the articular cartilage has extended over theproximal surface 6806 of theimplant 6800. Thisportion 6818 of articular cartilage may only be a superficial layer of cartilage, and may only extend over a portion of theproximal surface 6806 of the implant. However, this remodeling may facilitate load bearing across the transition between theimplant 6800 and the surrounding articular cartilage. - Those skilled in the art will recognize that the present invention is subject to other modifications and/or alterations, all of which are deemed within the scope of the present invention, as defined in the hereinafter appended claims.
Claims (20)
1. An implant comprising:
a bone-facing distal surface; and
a proximal surface;
wherein said bone-facing distal surface and said proximal surface define an outer perimeter comprising at least two arcuate sections each having a concentric arcuate shape with a common center and a first and a second generally opposing side section extending generally along a length of said implant between said at least two arcuate shaped sections, wherein said outer perimeter has a truncated circular shape.
2. The implant of claim 1 , wherein said truncated circular shape comprises a circular shape truncated on two opposed sides.
3. The implant of claim 1 , further comprising a protrusion extending around at least a portion of said implant, said protrusion configured to cover an un-excised portion of an articular surface proximate said implant.
4. The implant of claim 1 , wherein said implant further comprises:
a width extending between said two opposing side sections and through said common center; and
a length extending between said two arcuate sections and through said common center;
wherein said width is less than said length.
5. The implant of claim 4 , wherein said width extends along a medial-lateral (ML) curvature of said implant and said length extends along an anterior-posterior (AP) curvature of said implant.
6. A system comprising:
a reamer configured to remove a portion of a patient's articular surface in an area proximate to a defect site to form an excision site, said reamer comprising a blade portion configured to create a circular cutting projection when rotated about a longitudinal axis of said reamer, said circular cutting projection having a diameter greater than a width of said patient's articular surface in said portion to be removed; and
an implant comprising:
a bone-facing distal surface; and
a proximal surface;
wherein said bone-facing distal surface and said proximal surface define an outer perimeter comprising at least two arcuate sections each having a concentric arcuate shape with a common center and a first and a second generally opposing side section extending generally along a length of said implant between said at least two arcuate shaped sections, wherein said outer perimeter has a truncated circular shape.
7. The system of claim 6 , wherein said bone-facing distal surface is configured to match with said excision site.
8. The system of claim 7 , wherein said outer perimeter of said implant corresponds to a perimeter of said excision site.
9. The system of claim 6 , further comprising a guide pin having a length configured to extend generally perpendicular to said articular surface proximate said defect site, said guide pin defining a working axis along said length of said guide pin.
10. The system of claim 9 , wherein said reamer is configured to translate along working axis of said guide pin.
11. The system of claim 6 , wherein said implant further comprises a screw configured to engage bone beneath said removed articular surface along said working axis.
12. The system of claim 6 , wherein said reamer comprises a generally circular blade portion.
13. The system of claim 12 , wherein said reamer comprises a shaft extending along said longitudinal axis of said reamer, wherein said generally circular blade portion extends generally radially outwardly from said shaft.
14. The system of claim 12 , wherein said generally circular blade portion is rotated about said shaft.
15. The system of claim 6 , wherein said reamer comprises:
a shaft extending along said longitudinal axis of said reamer; and
a cutting blade extending generally radially outwardly from said shaft arm.
16. The system of claim 15 , wherein said cutting blade comprises an offset
17. The system of claim 16 , wherein said bone-facing distal surface of said implant includes a non-planar contour and wherein said offset arm of said cutting blade comprises a non-planar cutting surface configured to create said excision site including a base portion having a non-planar contour generally matching said non-planar contour of bone-facing distal surface of said implant.
18. An implant for installation into an excision site formed within a patient's articular surface, said implant comprising:
a bone-facing distal surface having a non-planar contour configured to match with a non-planar base portion of said excision site;
a screw extending generally outwardly from bone-facing distal surface, said screw configured to secure said implant within said excision site;
a proximal surface having a contour based on an original surface contour of said excised portion of said articular surface; and
an outer perimeter comprising at least two arcuate sections each having a concentric arcuate shape with a common center and a first and a second generally opposing side section extending generally along a length of said implant between said at least two arcuate shaped sections, wherein said outer perimeter has a truncated circular shape.
19. The implant of claim 18 , wherein said truncated circular shape comprises a circular shape truncated on two opposed sides.
20. The implant of claim 18 , wherein said implant further comprises:
a width extending between said two opposing side sections and through said common center, said width extending along a medial-lateral (ML) curvature of said implant; and
a length extending between said two arcuate sections and through said common center, said length extending along a anterior-posterior (AP) curvature of said implant;
wherein said width is less than said length.
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2009
- 2009-11-17 US US12/620,309 patent/US20100070045A1/en not_active Abandoned
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2010
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- 2013-09-24 US US14/035,061 patent/US20140288561A1/en not_active Abandoned
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Also Published As
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EP1596768A2 (en) | 2005-11-23 |
AU2004216106B2 (en) | 2010-06-17 |
WO2004075777A3 (en) | 2005-03-10 |
US20030225456A1 (en) | 2003-12-04 |
US7678151B2 (en) | 2010-03-16 |
AU2004216106A1 (en) | 2004-09-10 |
US8540717B2 (en) | 2013-09-24 |
EP1596768A4 (en) | 2010-09-08 |
US20100204701A1 (en) | 2010-08-12 |
WO2004075777A2 (en) | 2004-09-10 |
US20140288561A1 (en) | 2014-09-25 |
JP2006518615A (en) | 2006-08-17 |
CA2516789A1 (en) | 2004-09-10 |
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