ANCHOR DRIVING TOOL AND TENDON ANCHORING SYSTEM

专利摘要:
biceps tenodesis implants and application tools. the present invention relates to methods and devices for anchoring a ligament or tendon to a bone. in one embodiment, there is shown a surgical implant having a sheath, and an expander that is received within the sheath. a number of application tools are also presented, including a sheath inserter and a conductor. in use, the sheath inserter can be used to position a tendon within a prepared bone hole, and can be used to drive the sheath, with a guidewire attached thereto, into the bone hole. the conductor can be used to drive the expander into the sheath. a charger may optionally be used to charge the lead and expander on the guidewire attached to the implanted sheath.
公开号:BR102015026825B1
申请号:R102015026825-4
申请日:2015-10-22
公开日:2022-01-11
发明作者:Gerome Miller；David R. Diduch；Mark H. Getelman；Jacob A. Marks；Matthew J. Ravenscroft；Mehmet Z. Sengun；Howard C. Tang；Gregory R. Whittaker
申请人:Depuy Synthes Products, Inc；
IPC主号:

专利说明:

CROSS REFERENCE TO RELATED DEPOSIT REQUESTS
[0001] The present application claims priority to US Provisional Application No. 62/067,701, filed on October 23, 2014 and entitled "Biceps Tenodesis Implants and Delivery Devices", which is incorporated herein by reference in its totality. FIELD OF THE INVENTION
[0002] Surgical methods and devices for anchoring tissue to bone are presented and, more particularly, surgical implants, application tools and methods for fixing a biceps tendon to the humerus are presented. BACKGROUND
[0003] Disorders of the long head of the biceps tendon are a common source of shoulder pain and may occur in association with other diagnoses such as rotator cuff tears, anterior and posterior superior labrum tears, collision syndrome and capsular injuries, or may be present as an isolated source of shoulder pain. Treatment options for long head of biceps (CLB) disorders continue to evolve and may include LLB tenodesis. In a tenodesis procedure, a suture is passed through the base of the LHB to locate the LBL in the subacromial space, and to provide proximal control during dissection. Once the suture is in place, the CLB is cut close to the glenoid ligament. A size gauge can be used to measure the size of the tendon and thus determine the properly sized bone screw. Once the screw is selected, a bone hole is drilled, and a tendon fork is then used to push the tendon down and into the bone hole. A bone screw is then applied to the bone hole to anchor the tendon within the bone hole.
[0004] While current procedures may offer an effective means of anchoring a tendon to a bone, they may suffer from several disadvantages. For example, current procedures require the use of numerous tools, which can lead to a lengthy procedure and increased costs. The use of a screw can also increase the risk of damage to the tendon, as rotating the screw into the bone can tear or cut through the tendon. In addition, it may be difficult to maintain the desired tension in the tendon while the screw is being implanted, as the tendon may become misaligned or may slip during screw insertion. Any tension applied to the tendon during anchor insertion may also cause the anchor to retract out of the bone hole.
[0005] Consequently, there is a need for improved methods and devices for anchoring tissue to bone and, in particular, for performing a biceps tenodesis. SUMMARY
[0006] Various implants, tools and methods for fixing a tendon to a bone are presented. In one embodiment, an anchor assembly for anchoring a tendon to a bone is provided, and includes a sheath having a substantially solid distal end with at least two side walls extending proximally therefrom, and separated by at least a first and a second slit. The side walls may have threads formed on an inner surface thereof, and the side walls may define an inner lumen therebetween. The solid distal end of the sheath may have a snap-in feature. The anchor assembly may additionally include a guidewire having a distal tip configured to releasably engage the snap-on feature. In one embodiment, the engagement feature may be a threaded hole formed in the sheath, and the distal tip on the guidewire may be threaded to threadedly engage the threaded hole. The guidewire may extend proximally from the sheath when fitted to the sheath. The anchor assembly may additionally include an expander which may have a generally elongated cylindrical configuration such that the expander is configured to be received within the inner lumen of the sheath. In one embodiment, the expander may have threads formed on an outer surface thereof, which threadably engage with threads formed on the inner surface of the at least two side walls. The expander may additionally include a lumen extending therethrough to receive the guidewire.
[0007] In some embodiments, the sheath of the anchor assembly may include at least one anti-flattening tab formed on at least one of the side walls adjacent to one of the slots. The at least one flap may be configured to limit movement of the side walls towards each other. In some embodiments, the sidewalls may have an increased thickness in a midportion thereof as compared to the proximal and distal portions thereof. In other embodiments, the sidewalls may include ribs extending radially around them. For example, the ribs on a first side wall of the anchor can be angled distally, and the ribs on an opposite second side wall of the anchor can be angled proximally.
[0008] The sheath may also include at least one anti-sink flap extending radially outward from a more proximal end thereof. The anti-sinking tab can be configured to limit a depth of insertion of the sheath into a bone hole. The sheath may also include at least one retaining tab extending radially outward from the sheath at a predetermined distance from the anti-sinking tab. The distance can be configured so that the anti-sinking tab can be positioned on a proximal surface of the cortical bone, and the retention tab can be positioned on a distal surface of the cortical bone. In an exemplary embodiment, the distance may be greater than about 0.5 mm.
[0009] In some embodiments, the anchor assembly may include a sheath that may have a concave end facing the distal portion for seating a tendon. In some embodiments, the anchor assembly may include a sheath which may have a proximally facing convex end.
[00010] In other aspects, the first and second slits may each have a proximal portion, a distal portion, and a transition region extending between the proximal and distal portions. The proximal and distal portions may each be of a constant width, and the transition region may have a width that tapers inwardly in a distal direction. In an exemplary embodiment, a length of the transition region may be substantially equal to a width of the proximal portion.
[00011] In another embodiment, a method for anchoring a tendon to a bone is provided. The method may include positioning a distal end of a sheath over a tendon that extends through a bony orifice. The sheath may have a guidewire attached thereto and extending proximally therefrom. The sheath, with the guidewire attached to it, can be advanced into the bone hole to cause the tendon to advance into the bone hole and extend between the sheath and the bone hole. A cannulated expander can be advanced along the guidewire and into the sheath to cause the sheath to expand outward to anchor the tendon within the bone hole.
[00012] The method may include advancing the sheath into the bone hole using an insertion tool that has the guidewire extending through it. The method may additionally include the steps of, after advancing the sheath, manipulating the insertion tool to release the guidewire from a guidewire clamp on the insertion tool, and removing the insertion tool from the guidewire. In another embodiment, when the expander is fully inserted into the sheath, the expander and sheath may be in full circumferential contact over a major part of a length thereof. In another embodiment, the expander may be non-rotatably advanced into the sheath, or alternatively, a distal portion of the expander may be non-rotatedly advanced into the sheath, and a proximal portion of the expander may be threaded swivel into the sheath.
[00013] In other aspects, the method may include advancing the expander along the guidewire using a driving tool. The driving tool may include an outer shank having opposing pins at a distal end thereof, which are positioned within opposing slots formed in the sheath. The driving tool may additionally include an inner shank extending through the outer shank and engaged with the expander. The inner rod can be rotated to advance the expander into the sheath, while the pins on the outer rod keep the sheath substantially stationary. The driving tool can be removed from the guidewire and sheath, leaving the sheath and expander implanted in the bone.
[00014] In another embodiment, an anchor assembly is provided for anchoring a tendon to a bone, and includes a sheath and a threaded expander. The sheath may have a body with at least two side walls extending proximally therefrom. The side walls may be separated by at least a first and a second slit, and the side walls may define an internal lumen therebetween. The side walls may additionally include threads formed on an inner surface thereof. The threaded expander may be configured to be received between the at least two side walls, and to threadably join the threads formed on the inner surface of the side walls. The sheath and threaded expander can be configured so that when the expander is fully threaded into the sheath, a middle portion of the side wall expands outward by a distance that is greater than a distance for which the proximal and distal portions of the walls sides expand outwards. The middle portion thus defines a maximum external dimension of the sheath for anchoring the sheath within a bony orifice.
[00015] In some embodiments, the middle portion of the at least two side walls may have a thickness that is greater than a thickness of the proximal and distal portions of the at least two side walls. In some embodiments, the expander of the anchor assembly may have a smaller diameter, and the threads on the expander define a larger diameter. A smaller expander diameter can cause the side walls of the sheath to expand outwards. In other embodiments, a larger diameter or both a smaller and a larger diameter can cause the sidewalls of the sheath to expand outwardly. In some embodiments, the expander of the anchor assembly may include a proximal cylindrical portion of substantially constant diameter, and a tapered distal portion of distally decreasing diameter.
[00016] In other aspects, a method for anchoring a tendon to a bone is presented. The method may include positioning a distal end of a sheath over a tendon that extends through a bony orifice. The sheath can be advanced into the bone hole to cause the tendon to be advanced into the bone hole. An expander can be inserted into an inner lumen of the sheath such that the expander causes the proximal, middle, and distal portions of the sheath to expand outward. The middle portion of the sheath can expand outward by a distance that is greater than the distance for which the proximal and distal portions of the sheath expand outward. The middle portion can thus define a maximum external dimension of the sheath that prevents the sheath from retracting out of the bony orifice.
[00017] In other aspects, the sheath may have threads formed on an inner surface thereof. The expander may additionally include threads formed on an internal surface thereof. The expander can be inserted into the sheath by rotating the expander with respect to the sheath to thread the expander into the sheath. The expander can have a smaller diameter, and the threads on the expander can define a larger diameter. The smaller diameter of the expander may cause the sheath to expand outwards. In other embodiments, the major or both minor and major diameters of the expander may cause the sheath to expand outward.
[00018] In another embodiment, an anchor assembly for anchoring a tendon to a bone is presented. The anchor assembly may include a sheath having a substantially solid distal end, and at least two side walls extending proximally from the distal end. The side walls may be separated by at least a first and a second slit, and the side walls may define an internal lumen therebetween. The sheath may additionally include at least one anti-sink flap extending from a more proximal end of the sheath adjacent the slits. The anti-sink tab can be configured to prevent over-insertion of the sheath into a bone hole. The sheath may additionally include at least one retention tab extending from the sheath at a location distal to the anti-sinking tab. The retaining tab can be positioned at a distance from the anti-sinking tab. The distance can be set so that when the anti-sinking tab is on a proximal surface of a cortical bone, the retention tab will extend beneath a distal surface of the cortical bone. The anchor assembly may additionally include a threaded expander that can be received between the at least two side walls in the sheath to cause the sheath to expand and engage with cortical bone.
[00019] In some embodiments, the at least one anti-sag flap may include a pair of anti-sag flaps, and the at least one retainer flap may include a pair of retention flaps. In some embodiments, the at least one anti-sag tab may extend radially outward by a distance that is greater than a distance by which the at least one retention tab extends radially outward. In some embodiments, the at least one anti-sinking tab may be coplanar with the at least one retention tab. In some embodiments, the distance between the anti-sink tab and the retention tab can be greater than about 0.5 mm, and more preferably, can be in the range of about 1.0 mm to 2.0 mm.
[00020] In other aspects, a method for anchoring a tendon to a bone is presented. The method may include positioning a distal end of a sheath over a tendon that extends through a bony hole in a bone. The sheath can be advanced into the bone hole so that the tendon is advanced into the bone hole. At least one anti-sink tab extending from opposite sides of a more proximal end of the sheath may be in a boundary position against a surface of the bone to limit a depth of insertion of the sheath into the bone hole. At least one retention tab extending from the sheath at a location distal to the anti-sinking tab may extend beneath a surface of the bone. An expander can be inserted into the sheath to cause the sheath to expand outward. The retention tab can expand to a diameter that is greater than a diameter of the bone hole to thereby prevent removal of the sheath from the bone hole, thereby anchoring the tendon within the bone hole.
[00021] In one embodiment, the anti-sinking tab may extend radially outward by a distance that is greater than a distance by which the retention tab extends radially outward. The retention tab can be inserted into the bone hole while the anti-sinking tab can be prevented from being inserted into the bone hole. The bone may be, for example, cortical bone. The bone can be at least 0.5 mm thick, and the anti-sinking tab can be positioned at least 0.5 mm away from the retaining tab, to receive the bone between them.
[00022] In another embodiment, an anchor insertion tool is provided having an elongated first body, with first and second pins extending distally from a distal end thereof and configured to extend along opposing slots formed in a sheath of an anchor set. The anchor assembly may also include a second elongate body slidably disposed relative to the first elongate body. The anchor assembly may also include a cable assembly coupled to a proximal end of each of the first and second elongate bodies. The cable assembly may be configured so that the first elongate body has first and second ranges of motion. The first elongate body in the first range of motion is movable between a first position in which the first and second pins extend distally beyond the second elongate body and a second position in which the first and second pins are retained. inside the second elongated body. The first elongate body in the second range of motion is movable from the second position to a third position, in which the first elongate body is configured to cause a guide wire extending through the first elongate body and engaged with the cable assembly to be disengaged and released from the cable assembly.
[00023] In certain embodiments, the first elongate body can be an inner rod and the second elongate body can be an outer rod disposed around the inner rod. In some embodiments, the second elongate body may include a closed distal end having a central hole formed therein to receive a guidewire. The second elongate body may additionally include first and second slots formed therein and extending radially outward from the central hole to receive the pins. In another embodiment, a distal portion of the second elongate body may include first and second recesses formed in opposite outer side walls thereof. In another embodiment, the first and second elongate bodies may be configured to be releasably locked together to prevent movement of the first and second elongate bodies relative to each other.
[00024] In certain embodiments, the cable assembly may include a first tilting element that applies a first tilting force, which must be overcome to move the first elongate body from the first position to the second position, and the cable assembly includes a second tilting element that applies a second tilting force that must be overcome to move the first elongate body from the second position to the third position. The second tilt force can be greater than the first tilt force. The cable assembly may also include a guidewire gripping element, which may be configured to engage a proximal end of a guidewire coupled to a sheath of an anchor assembly, and extend through the first. elongated body. In other embodiments, the cable assembly may include an actuator coupled to the first elongate body, and configured to move the first elongate body through the first and second ranges of motion. In other embodiments, the cable assembly may include a first cable fitted to the second elongate body and having an engagement member formed therein for engagement with a guide wire. The handle assembly may additionally include a second handle fitted to the first elongate body to move the first elongate body relative to the second elongate body.
[00025] In another embodiment, a tendon anchoring system is presented. The system may include an anchor assembly having a sheath with at least two side walls at least partially separated by at least first and second slits. The side walls can define an internal lumen between them. The anchor assembly may additionally include an expander which can be received within the inner lumen of the sheath. The system may also include an insertion tool which may have an outer shaft with an inner lumen extending therethrough, and an inner shaft having first and second pins formed at a distal end thereof. The pins may be sized to extend along the first and second slots in the sheath, and to extend distally beyond a distal end of the sheath. The insertion tool may also include a handle assembly coupled to a proximal end of the inner and outer rods. The cable assembly may have an actuator configured to move the inner rod axially relative to the outer rod to thereby move the pins between an extended position, in which the pins extend distally beyond a distal end of the outer rod, and a retracted position, in which the pins are retracted into the distal end of the outer stem.
[00026] In certain embodiments, the external nail may have a closed distal end having a central hole formed therein to receive a guide wire. The outer shank may also include first and second slots formed therein and extending radially outward from the central hole to receive the first and second pins. In some embodiments, a guidewire may be fitted to the sheath, and a guidewire gripper element on the cable assembly may be configured to engage a proximal end of the guidewire. In other embodiments, the first and second pins may include a connector extending therebetween along a proximal portion of the pins, and the connector may have a central lumen extending therethrough. In yet another embodiment, the sheath may include at least one anti-sink flap extending radially outward from a more proximal end thereof, and a surface facing the distal side of the outer shank may include at least one recess formed in the sheath. same to seat at least one anti-sinking flap.
[00027] In other aspects, the actuator may move between a distal position on the handle assembly, where the pins extend distally beyond the distal end of the outer stem, and a proximal position on the handle assembly, where the pins extend distally beyond the distal end of the outer stem, and a proximal position on the handle assembly. pins are retracted into the distal end of the outer stem. In certain embodiments, the actuator can be forced to the distal position.
[00028] A method for anchoring a tendon to a bone is also presented. The method may include attaching a sheath to an insertion tool so that a pair of pins at a distal end of an inner shank of the insertion tool extends along opposing slots formed in the sheath. The method may include manipulating an actuator on a lead assembly of the insertion tool to retract the pair of pins into an outer shank of the insertion tool and, with the pins retracted, manipulating the lead assembly to advance the sheath through. of the fabric. After the sheath has been advanced through the tissue, the actuator can be manipulated to cause the pins to extend along opposing slots formed in the sheath, and to extend distally beyond a distal end of the sheath. The method may further include positioning the tendon between the pair of pins, and manipulating the cable assembly to advance the pins, with the tendon therebetween, and the sheath into a bony hole. The insertion tool can be removed so that the anchor and tendon remain in the bone hole. In some embodiments the method may additionally include inserting an expander into the sheath to cause the sheath to expand outwardly so as to anchor the tendon within the bone hole.
[00029] In certain embodiments, the method may include measuring a size of a tendon to be anchored to bone, by positioning the tendon between the pair of pins at the distal end of the inner shaft of the insertion tool. In some embodiments, measuring the size of a tendon may include measuring a tendon using a first insertion tool having a pair of pins spaced a first distance apart, and measuring the tendon using a second insertion tool having a pair of pins spaced a first distance apart. second distance.
[00030] In other aspects, attachment of the sheath to the inserter may include advancing a guidewire fitted to the sheath proximally into a distal end of the inner shank of the insertion tool to cause the guidewire to engage to a guidewire clamp on the insertion tool handle assembly. In some embodiments, removal of the inserter may additionally include manipulating the actuator to cause the guidewire jaw to release the guidewire.
[00031] In another aspect, an anchor driving tool is provided. The anchor driving tool may include an outer shank having first and second pins extending distally from a distal end thereof. The first and second pins may be configured to extend into opposing slots formed in a sheath of an anchor assembly. The anchor driving tool may also include an inner shank extending through the outer shank and having a distal end configured to fit an expander of an anchor assembly. A cable assembly can be attached to a proximal end of the inner and outer rods. The cable assembly may include an actuator configured to rotate the inner stem relative to the outer stem to drive an expander coupled to a distal end of the inner stem into a sheath coupled to the first and second pins of the outer stem. The outer shaft may be configured to maintain the sheath in a substantially fixed position during rotation of the inner shaft. In some embodiments, the actuator may include a handle at a proximal end of the inner shaft, and the handle assembly may include a stationary handle at a proximal end of the outer shaft.
[00032] In certain embodiments, the outer rod may include opposing viewing windows formed in a distal portion thereof, and/or opposing indentations formed in the distal end thereof, to seat a tendon. In some embodiments, the outer shank is free to pivotally move relative to the inner shank, and the axial translation of the outer shank relative to the inner shank can be limited to a predetermined distance. In some embodiments, at least one of the inner and outer rods may include at least one marking to indicate when an expander is fully seated within a sheath.
[00033] In another aspect, a tendon anchoring system is presented, which includes an anchor set and an insertion set. The anchor assembly may include a sheath having a sheath having a generally elongated cylindrical configuration with at least two side walls at least partially separated by at least first and second slits. The side walls can define an internal lumen between them. The anchor assembly may also include an expander configured to be received within the inner lumen of the sheath. The inserter assembly may include an outer shaft having first and second pins formed at a distal end thereof. The pins may be sized to be received within the first and second slots in the sheath. The inserter assembly may additionally include an inner stem extending through the outer stem and having a distal end configured for engagement with the expander. A cable assembly can be attached to a proximal end of the inner and outer rods. The cable assembly may have an actuator configured to rotate the inner rod to drive the expander into the sheath, while the pins on the outer rod maintain the sheath in a substantially fixed position.
[00034] In certain embodiments, the tendon anchor system may include a carrier having a route extending therethrough, between the proximal and distal ends thereof, to seat the expander and a distal portion of the outer rod. The magazine may include a tapered distal end.
[00035] In some embodiments, the pins have a length that is less than a length of the first and second slots, so that the pins only partially extend into them. In some embodiments, the actuator may include a handle at a proximal end of the inner shaft, and the handle assembly may include a stationary handle at a proximal end of the outer shaft. In some embodiments, markings may be formed on at least one of the inner and outer shafts to indicate when the expander is fully seated within the sheath.
[00036] In some embodiments, the outer rod may include opposing viewing windows formed in a distal portion thereof, and/or opposing indentations formed in the distal end thereof, to seat a tendon. In some embodiments, the outer shank is freely rotatable relative to the inner shank, and the axial translation of the outer shank relative to the inner shank is limited to a predetermined distance.
[00037] In another aspect, a method for anchoring a tendon to bone is presented. The method may include advancing a sheath and tendon into a bone hole in the bone so that the tendon extends between the sheath and bone hole. A pair of pins at a distal end of an outer shaft of a driving tool can be inserted into opposing slots formed in the sheath implanted in the bone hole. The method may also include manipulating an actuator on a drive tool handle assembly to rotate an inner stem extending through the outer stem to thereby advance an expander coupled to a distal end of the inner stem into the inner stem. sheath. The pair of pins on the outer shaft can hold the sheath substantially stationary while the inner shaft rotates the expander into the sheath. In some embodiments, the pins can prevent the side walls of the sheath from flattening radially inwardly.
[00038] In some embodiments, the inner stem may rotate freely with respect to the outer stem, and the axial movement of the inner stem to advance the expander into the sheath is limited to a predetermined distance. In other embodiments, the inner stem may be cannulated to receive a guidewire attached to the sheath such that the guidewire axially aligns the inner stem and outer stem with respect to the sheath.
[00039] In some embodiments, tabs on the sheath limit a depth of insertion of the sheath into the bone hole. In some embodiments, the outer stem may include opposing indentations formed at a distal end thereof. The tendon can extend into the opposing cutouts when pins are inserted into the slots so that the outer rod is positioned against a surface of the bone. BRIEF DESCRIPTION OF THE DRAWINGS
[00040] The invention will be more widely understood from the detailed description presented in conjunction with the accompanying drawings, in which:
[00041] Figure 1 is a perspective view of a biceps tenodesis system having a sheath inserter, a sheath, a driving tool and an expander screw;
[00042] Figure 2 is a side perspective view of the sheath of Figure 1;
[00043] Figure 3 is another side perspective view of the sheath of Figure 1;
[00044] Figure 4 is a top view of the sheath of Figure 1;
[00045] Figure 5A is a perspective view of the sheath of Figure 1, shown with a guide wire for joining thereto;
[00046] Figure 5B is a side perspective view of the sheath and guidewire of Figure 5A, shown together;
[00047] Figure 6 is a cross-sectional view of the sheath of Figure 1;
[00048] Figure 7 is another cross-sectional view of the sheath of Figure 1;
[00049] Figure 8A is a side perspective view of the expander screw of Figure 1;
[00050] Figure 8B is a side perspective view of another embodiment of an expander that is configured to be partially non-rotatably advanced into a bone hole and then rotatably advanced into the bone hole;
[00051] Figure 8C is a side perspective view of another embodiment of an expander that is configured to be non-rotatably advanced into a bone hole;
[00052] Figure 9 is a perspective view in cross section of the expander screw of Figure 1;
[00053] Figure 10 is a perspective view of the insertion tool of Figure 1;
[00054] Figure 11A is an exploded perspective view of the insertion tool of Figure 1;
[00055] Figure 11B is a perspective view of one embodiment of a locking mechanism for use with the insertion tool of Figure 1;
[00056] Figure 11C is a side view of the locking mechanism of Figure 11B;
[00057] Figure 12A is a partially transparent perspective view of a distal yoke of the insertion tool of Figure 1;
[00058] Figure 12B is an end view of the distal fork of the insertion tool of Figure 1;
[00059] Figure 12C illustrates another embodiment of an insertion tool having a fork with collapsible pins, showing the tool about to be inserted through a bone hole in the bone;
[00060] Figure 12D illustrates the insertion tool of Figure 12C inserted through the bone hole to cause the fork pins to curve outward.
[00061] Figure 13 is a perspective view of the distal fork and a portion of the outer shank of the insertion tool of Figure 1;
[00062] Figure 14A is a perspective view of the guidewire of Figure 5A extending from the outer shank of the insertion tool of Figure 1;
[00063] Figure 14B is a perspective view of a distal end of an outer shank of an insertion tool according to another embodiment;
[00064] Figure 14C is a side view of the outer rod of Figure 14B, having a sheath coupled thereto;
[00065] Figure 15 is a perspective view showing the sheath of Figure 1 mounted on the distal yoke of the insertion tool of Figure 1;
[00066] Figure 16A is a side view of a small size insertion tool;
[00067] Figure 16B is a side view of an oversize insertion tool;
[00068] Figure 17A is a side view of the insertion tool of Figure 1, showing the insertion tool in an initial position;
[00069] Figure 17B is a side view of the insertion tool of Figure 17A, showing a trigger pulled proximally to retract a distal fork from an external shank of the tool;
[00070] Figure 17C is a side view of the insertion tool of Figure 17B, showing the trigger pulled even more proximally to release a guidewire from joining engagement with the insertion tool;
[00071] Figure 18 is a side perspective view of the driving tool of Figure 1;
[00072] Figure 19 is a transparent exploded view of the tool trigger of Figure 18;
[00073] Figure 20 is a transparent perspective view of a handle and handle of the insertion tool of Figure 18;
[00074] Figure 21 is a perspective view of a distal end of an outer shank of the driving tool of Figure 18;
[00075] Figure 22 is a side view of the distal end of the outer rod of Figure 21;
[00076] Figure 23 is another side view of the distal end of the outer rod of Figure 21;
[00077] Figure 24A is a side view of the driving tool of Figure 1, showing the driving tool in an initial position;
[00078] Figure 24B is a side view of the driving tool of Figure 24A, showing the outer rod moved distally with respect to the inner rod;
[00079] Figure 24C is a side view of the driving tool of Figure 24B, showing the outer rod moved even more distally with respect to the inner rod;
[00080] Figure 25 is a perspective view of an embodiment of a magazine, shown having the expander screw and driving tool of Figure 1 coupled thereto;
[00081] Figure 26A is a side view of the loader of Figure 25;
[00082] Figure 26B is a front view of the loader of Figure 26A, showing the expander screw of Figure 1 about to be received inside;
[00083] Figure 26C is a front view of the loader and expander screw of Figure 26B, shown in the snapped configuration and being guided over a guide wire;
[00084] Figure 26D illustrates the charger, the expander screw and the guide wire of Figure 26C, showing the removed charger that leaves the expander screw positioned over the guide wire;
[00085] Figure 27A is a side view of one embodiment of a tendon measuring device;
[00086] Figure 27B is a side view of a distal end of another embodiment of a tendon measuring device;
[00087] Figure 28 is a side view of another embodiment of a tendon measuring device;
[00088] Figure 29 is a side view of another embodiment of a tendon measuring device;
[00089] Figure 30 is another side view of the tendon measuring device of Figure 29;
[00090] Figure 31 is a side view of a distal end of the tendon measuring device of Figure 29;
[00091] Figure 32 is a side view of a guidewire and bone hole drilling device combination, according to another embodiment;
[00092] Figure 33A is a side view of an embodiment of a combined tendon measuring device and bone hole piercing device, showing a fork retracted into the distal end;
[00093] Figure 33B is a side view of the device of Figure 33A, showing the fork partially extending from the distal end;
[00094] Figure 33C is a side view of the device of Figure 33A, showing the fork fully extending from the distal end;
[00095] Figure 34A is a side view of another embodiment of a tendon measuring device;
[00096] Figure 34B is a side view of a distal portion of the tendon measuring device of Figure 34A, shown adjacent a tendon to be measured;
[00097] Figure 34C is a side view of the distal portion of the tendon measuring device and the tendon of Figure 34B, showing the measuring device measuring the tendon;
[00098] Figure 35 is a top view of another embodiment of a bone hole preparation device;
[00099] Figure 36 is a side view of the bone hole preparation device of Figure 35;
[000100] Figure 37 is an end view of a tip of the device of Figure 35;
[000101] Figure 38 is a side view of an embodiment of an angled tip of a bone hole preparation device;
[000102] Figure 39 is a side view of an embodiment of a rounded edge tip of a bone hole preparation device;
[000103] Figure 40A is a perspective view of a distal portion of the insertion tool of Figure 1, shown measuring a tendon to be anchored to bone;
[000104] Figure 40B is a perspective view of the distal portion of the insertion tool of Figure 40A, with the sheath of Figure 1 being loaded into the insertion tool;
[000105] Figure 40C is a perspective view of the insertion tool and sheath of Figure 40B, showing the assembly being used to thread a tendon into a bone hole in the bone;
[000106] Figure 40D is a perspective view of the sheath and sheath insertion tool of Figure 40C, showing the sheath fully inserted into the bone hole;
[000107] Figure 40E is a perspective view of the sheath of Figure 40D, showing the insertion tool removed, leaving the guidewire attached to the implanted sheath;
[000108] Figure 41A is a perspective view of the expander screw of Figure 1 loaded on the guide wire of Figure 40E;
[000109] Figure 41B is a perspective view of the expander screw of Figure 41A, showing the driving tool of Figure 1 being advanced over the guidewire;
[000110] Figure 41C is a perspective view of the driving tool and expansion screw of Figure 41B, with the driving tool engaged with the expansion screw;
[000111] Figure 41D is a perspective view of the driving tool and expander screw of Figure 41C, showing an outer shaft of the driving tool advanced distally to position the pins of the outer shaft within the sheath slots;
[000112] Figure 41E is a perspective view of the driving tool and expansion screw of Figure 41D, showing the expansion screw completely driven into the sheath;
[000113] Figure 41F is a perspective view of the driving tool and expander screw of Figure 41E, showing the driving tool removed, leaving the guidewire extending from the expander screw disposed within the sheath;
[000114] Figure 41G is a perspective view of the sheath and expander screw of Figure 41F, showing the guidewire being removed from the implant;
[000115] Figure 42A is a top view of another embodiment of a sheath having anti-sag flaps;
[000116] Figure 42B is a side perspective view of the sheath of Figure 42A;
[000117] Figure 42C is a side perspective view of the sheath of Figure 42A, disposed in a bone hole and shown anchoring a tendon to bone;
[000118] Figure 42D is a top view of the sheath and tendon of Figure 42C;
[000119] Figure 43A is a top view of another embodiment of a sheath having a proximal flange;
[000120] Figure 43B is a side perspective view of the sheath of Figure 43A;
[000121] Figure 43C is a side perspective view of the sheath of Figure 43A, disposed in a bone hole and shown anchoring a tendon to bone; and
[000122] Figure 43D is a top view of the sheath and tendon of Figure 43C. DETAILED DESCRIPTION
[000123] Certain exemplifying modalities will now be described to provide a general understanding of the principles of structure, function, fabrication and use of the devices and methods disclosed herein. One or more examples of such embodiments are illustrated in the accompanying drawings. Those skilled in the art will understand that the devices and methods specifically described in the present invention and illustrated in the accompanying drawings are exemplary non-limiting embodiments, and that the scope of the present invention is defined solely by the claims. Features illustrated or described in connection with one exemplary embodiment may be combined with features of other embodiments. Such modifications and variations are intended to be included within the scope of the present invention.
[000124] Throughout this specification, the terms "several modalities", "some modalities", "one modality" or "the modality", or similar, mean that a specific feature, structure or characteristic described together with the embodiment is included in at least one embodiment. Therefore, the appearance of the phrases "in several embodiments", "in some embodiments," "in one (1) embodiment," or "in one embodiment", or similar, in places from beginning to end of the specification are not necessarily all referring to the same modality. In addition, particular features, structures or features may be combined in any suitable manner in one or more modalities. Therefore, the particular features, structures or characteristics illustrated or described in conjunction with a modality may be combined, in whole or in part, with the structures of the features or characteristics of a or more other modalities, without limitation.
[000125] It will be understood that the terms "proximal" and "distal" may be used throughout the specification with reference to a physician manipulating an end of an instrument used to treat a patient. The term "proximal" refers to the portion of the instrument closest to the physician and the term "distal" refers to the portion located furthest from the physician. It should be further appreciated that, for accuracy and clarity, spatial terms such as "vertical", "horizontal", "up" and "down" may be used in the present invention with respect to the illustrated embodiments. However, surgical instruments can be used in many orientations and positions, and these terms are not intended to be limiting and absolute.
[000126] In general, methods and devices for anchoring a ligament or tendon to a bone are presented. In an exemplary embodiment, the methods and devices are used to perform a biceps tenodesis, but one skilled in the art will understand that the devices and methods can be used in various procedures, and to anchor any tissue to a bone. In one embodiment, there is provided a surgical implant having a sheath, and an expander that is received within the sheath. Various application tools are also presented, including a sheath inserter and a conductor. In use, the sheath inserter can be used to position a tendon within a prepared bone hole, and can be used to drive the sheath, with a guidewire attached thereto, into the bone hole. The conductor can be used to drive the expander into the sheath. A charger can optionally be used to charge the lead and expander on the guidewire attached to the implanted sheath.
[000127] One skilled in the art will understand that the surgical implants, delivery tools, and methods presented herein can be used with a variety of surgical devices, including measuring devices, drills, mallets, etc.
[000128] The modalities described herein generically refer to systems and methods for performing biceps tenodesis surgery. In some embodiments, the system may include any one or more of the following components: an anchor assembly or an implant having a sheath and an expander; a sheath insertion tool; a driving tool; and a charger. System components can reduce the number of steps required to perform a biceps tenodesis, and can do so with minimal risk of injury to the tendon.
[000129] Figure 1 illustrates an embodiment of a biceps tenodesis system that includes a sheath insertion tool 300, a sheath 100 coupled to a distal end of the sheath insertion tool 300, a driving tool 400, and a expander in the form of a screw 200 coupled to a distal end of the driving tool 400. Although not shown in Figure 1, the system may also include a magazine configured to detachably fit the driving tool 200 and screw 400 , as well as various other devices such as bone preparation tools and measuring device.
[000130] The apparatus and methods described here may have several advantages over existing techniques for performing biceps tenodesis. In particular, the entire fixation preparation procedure can be simple and straightforward, and requires a surgeon to perform just a few quick steps to secure the implant framework, including the sheath and expander, into the bone. A risk of tendon damage during expander rotation or any other technique that requires rotation of a component in direct contact with the tendon can be avoided. As a result, a risk of causing trauma to the tendon can be reduced and the time required to prepare and fix the tendon can be significantly reduced, which can facilitate surgery and mitigate patient inconvenience. In addition, the techniques described can help save operating room costs. implant
[000131] Figure 2 illustrates in more detail the implantable sheath of Figure 1. In general, the sheath is configured to accommodate a tendon around it, and to receive an expander inside it, which is effective in making it the sheath expands into the bone to anchor the tendon within a bone hole. The sheath may be formed from any biocompatible material, and may optionally be bioabsorbable.
[000132] While the shape and configuration of the sheath may vary, in one exemplary embodiment the sheath 100 has a generally elongated cylindrical shape, with a circular or oval cross-sectional geometry. The sheath 100 has a proximal end 100p and a distal end 100d, as shown in Figure 2. As shown in the side view of the sheath 100 in Figure 3, the sheath 100 may be a split sheath, with a first side wall 112a and a second side wall 112b which are connected at distal end 100d and which are separated by first and second elongate slots 114a and 114b extending therebetween. Elongated slots 114a and 114b may extend from proximal end 100p, and may terminate near distal end 100d. Slots 114a and 114b are preferably shaped to seat a fork member in the sheath insertion tool, as will be discussed in more detail below. In the illustrated embodiment, the width of slots 114a and 114b decreases in a proximal to distal direction. As further shown in Figure 2, the distal end 100d of the sheath 100 may be solid and closed, but an inner surface 116 may include a hole 120 formed therein, which is configured to receive a guidewire 140 therein. Hole 120 is preferably a blind hole that is threaded for engagement with a threaded end of guidewire 140, however the hole may optionally extend all the way through the distal end.
[000133] As shown in Figure 3, the elongated slots 114a and 114b formed in the side walls 112a and 112b of the sheath 100 may allow for expansion of the sheath. Slots 114a and 114b between side walls 112a and 112b of sheath 100 preferably have a width that is greater than a width of the forks (discussed below), so that side walls 112a and 112b can flatten inwardly. , toward the fork, to allow the tendon and sheath 100 to be pushed into the bone hole. For example, slots 114a and 114b at rest may have a width that is greater than the width of the yoke to allow side walls 112a and 112b of sheath 100 to move radially inward toward the yoke by a first distance to a flattened position. The side walls can also be configured to flex and move radially outward, away from the rest position by a second distance to an expanded position. In an exemplary embodiment, the sheath 100 is configured to have a rest state in which the first and second distances are equal. This type of configuration can be advantageous as the side walls 112a and 112b move from a middle rest position, rather than having the rest position in the expanded position and requiring the sheath to flex through both the first and of the second distances. In use, prior to implantation the side walls 112a and 112b may have a curvature which may be semicircular. When the sheath 100 is inserted into the bone hole, the side walls 112a and 112b can flatten in an oval orientation. When the sheath is expanded by the expander, the side walls can expand in a circular orientation, which can help achieve uniform compression around the entire sheath 100.
[000134] In some embodiments, the sheath may be formed having a varying wall thickness. As shown in Figure 6, an outer diameter D of the sheath may be substantially constant along the proximal portion, and may taper distally inwardly along the distal portion, to facilitate insertion. The inner lumen of the sheath 100 may have either a smaller inner diameter D1 or a larger inner diameter D2. The major inner diameter D2 (and optionally the smaller inner diameter D1) of the sheath 100 may taper distally inward from the proximal end 100p towards the distal end 100d, such that a thickness of the side walls 112a and 112b in a mid-portion 100 m of the sheath 100 is greater than a thickness at the proximal end 100p and distal end 100d of the sheath. As a result, when the screw 200 is inserted into the sheath 100, an average portion 100 m of the sheath 100, i.e., a portion of the sheath that is placed under the cortex, may expand to a diameter that is greater than a diameter of the sheath. 100 at the proximal end 100p, i.e., a portion of the sheath positioned within the cortex. The expansion of the midportion 100 m thus "anchores" the sheath 100 to prevent retraction of the sheath 100 back through the opening of the bone hole.
[000135] As shown in Figure 2, the sheath 100 may also include a distal-facing surface that is concave or saddle-shaped to seat the tendon thereon. This surface can be used to aid in tendon retention during insertion or immersion of the tendon and sheath 100 into the bone hole. This feature can be used in conjunction with, or independently of, other tendon retention features.
[000136] As further shown, the sheath may include a convex proximal surface over each sidewall 112a and 112b. The convex shape offers a rounded edge that can help prevent damage to any fabric in contact with the hem.
[000137] The sheath 100 may also include various surface features formed thereon to facilitate engagement with the bone. In one embodiment, the sheath 100 may have surface features such as ribs 106a, 106b, 106c, 106d, and 106e, and each rib may be uniplanar so as to allow the sheath to be inserted into bone without the need for sheath rotation. . A distal portion 102 of the sheath may be devoid of surface features. Although ribs are shown, those skilled in the art will understand that the sheath may include various surface features for engagement with the bone, such as threads, teeth, or other protrusions.
[000138] As noted above and further shown in Figure 7, the interior of the sheath 100 may have a hole 120 formed in the solid distal tip of the sheath 100. The hole 120 may be configured to receive the guidewire 140. The sheath 100 may be be pre-packaged on the 140 guidewire, to optimize ease of use during the surgical procedure. In an exemplary embodiment, as shown in Figure 11A, the guidewire 140 has a predetermined length that is sufficient to allow the guidewire to fit into the sheath and extend fully through and into the cable portion of the cable. each of the insertion device and the driving device. The guidewire may also have a threaded distal tip 142 that is configured to mate with threads (not shown) formed in hole 120 in sheath 100. In one embodiment, hole 120 is a blind hole, so that the wire -guide 140 does not protrude through the distal end 100d and is retained within the sheath 100. In an alternative embodiment, the hole may extend all the way through the distal tip, thereby allowing the guidewire 140 to protrude through the end of the sheath. 100.
[000139] As further shown in Figure 7, the sheath 100 may include features formed on the inner surface of the side walls 112a and 112b. For example, side walls 112a and 112b may include threads 124 formed on the inwardly facing surfaces thereof for threaded engagement with screw 200. In some embodiments, the threads may extend along a portion of the interior of the side walls. 112a and 112b, or completely along the inside of side walls 112a and 112b. Additional internal features may include, but are not limited to, ridges, engaging elements, or detents that could be used to assist the sheath 100 in pulling or engaging the bolt 200 in its final position. In an exemplary embodiment, the threads 124 are shaped to match the threads on the screw 200 when the sheath 100 is in the expanded state, not the rest state, as will be discussed in more detail below.
[000140] In some embodiments, the sheath 100 may include anti-sinking tabs formed at the proximal end 100p. For example, Figures 2 to 7 illustrate four anti-sink flaps, 110a, 110b, 110c and 110d, each having a generally rectangular configuration and extending radially outward from a proximal end 100p of the sheath 100 to prevent excessive insertion of the sheath 100 into the bone hole. In particular, the first and second anti-sink wings 110a and 110b extend from opposite sides of the first side wall 112a, and the fourth and fifth anti-sag wings 110c and 110d extend from opposite sides of the second. side wall 112b. The anti-sinking flaps 110a, 110b, 110c and 110d are therefore disposed adjacent the slots 114a and 114b. The anti-sink tabs 110 preferably extend radially outward from the sheath 100, beyond a maximum dimension or outside diameter of the sheath, so as to act as a lock that limits the depth of insertion of the sheath into a hole. bone.
[000141] Figures 42A to 42D illustrate another embodiment of a sheath 150 having anti-sink tabs 156a, 156b, 156c and 156d formed at an upper proximal end 150p. For example, Figure 42A is a top view of a sheath having two pairs of anti-sink flaps 156a, 156b, 156c and 156d, which extend radially outward from opposite sides of sheath 150. In particular, as shown in Fig. Figure 42B , first and second flaps 156a and 156c extend from opposite sides of a first side wall 158a, and fourth and fifth flaps 156b and 156d extend from opposite sides of a second side wall 158b. Flaps 156a, 156b, 156c and 156d are disposed adjacent to slots 154a and 154b which separate side walls 158a and 158b. The bifurcated pins of the insertion tool, discussed in more detail below, can mate with slots 154a and 154b to insert sheath 150 into the bone hole. In use, as shown in Figure 42C, the top surface 152 of the sheath 150 or the proximal end 150p is configured to remain above the top surface of the bone 500. As shown in Figure 42D, the anti-sink tabs 156a, 156b, 156c and 156d will be in a position bordering the top surface of the bone, extending beyond the bone hole to limit the depth of insertion of the sheath 150 into the bone hole. Tabs 156a to 156d are preferably oriented so that they are positioned on opposite sides of the tendon, i.e. in a direction perpendicular to the tendon. For example, the first and second flaps 156a and 156b may be in position near the left side of tendon 600l, and the third and fourth flaps 156c and 156d may be in position near the right side of tendon 600r. Anti-sag tabs 156a, 156b, 156c, and 156d can compress the tendon against the bone to facilitate anchoring of the tendon to the bone.
[000142] Figures 43A to 43D illustrate another embodiment of a sheath 160 having an anti-sink feature. In this embodiment, the proximal end 160p of the sheath 160 includes proximal flanges 162a and 162b extending radially outward from the proximal surface 168 of each side wall. In particular, the first and second proximal flanges 162a and 162b may extend from opposite sides beyond the diameter 160D of the sheath 160. As shown in Figure 43B, the sheath 160 may include opposing elongated slots 164a and 164b extending from from the proximal end 160p towards the distal end 160d. Elongated slots 164a and 164b may terminate in position proximate to solid distal tip 166, and may be configured to be coupled to an insertion tool, as will be discussed in more detail below. As shown in Figures 42A and 42B, the first flange 162a may extend between the first and second elongate slots 164a and 164b, extending circumferentially around the perimeter of the proximal surface 168 of the first side wall 170a. The second proximal flange 162b may extend between the first and second elongate slots 164a and 164b, extending circumferentially around the perimeter of the proximal surface 168 of the second side wall 170b. Flanges 162a and 162b may each have a generally semicircular or oblong shape. As shown in Figure 43C, when the sheath is implanted into a bone hole, the tendon 600 will be engaged between the proximal flanges 162a and 162b and the surface of the bone. Proximal flanges 162a and 162b may thus be positioned on the top surface of tendon 600 covering bone. Proximal flanges 162a and 162b may be formed from a flexible material, and may be configured to provide relief to the tendon upon flexion. As shown in Figure 43D, the outer edges 172b and 147b of the proximal flanges 162a and 162b can flex up and away from the bone surface, while the inner edges 172a and 174a of the proximal flanges 162a and 162b, located in position near the elongated slots 164a and 164b, can flex downwards towards the bone hole, pressing the tendon 600 into place. In this embodiment, the flanges 162a and 162b are oriented in line with the tendon, so that the first flange 162a extends through the tendon along one side of the bone hole, i.e., the distal side, and the second flange 162b extends through the tendon along one side of the bone hole, i.e., the distal side. extends through the tendon along the opposite side of the bony orifice, that is, the proximal side.
[000143] Again with reference to the embodiment of Figure 2, the sheath 100 may additionally include cortical retention tabs 108a and 108b positioned along the central section of the sheath 100, for example at a location just distal to the proximal end 100p. The cortical retention flaps 108a and 108b are preferably positioned about 2 mm from the most proximal end so that the cortical retention flaps 108a and 108b are positioned slightly beyond the cortical bone and into the cancellous bone tissue when the sheath 100 is implanted into a bone hole. Cortical retention tabs 108a and 108b can be sized to match a bone hole diameter. This allows the cortical retention tabs 108a and 108b to be passed into the bone hole. In other words, the cortical retention tabs 108a and 108b may have an outside diameter that is equal to or less than a dimension or a maximum outside diameter of the sheath 100. Once implanted and after insertion of the screw into the sheath 100, the sheath will expand to cause the cortical retaining flaps 108a and 108b, or at least an outer corner thereof, to extend under the surface of the cortex to prevent them from being pulled out, thereby locking the sheath 100 into the bone. In the illustrated embodiment, the sheath 100 includes four cortical retaining tabs 108a, 108b, 108c, and 108d, with two on opposite sides of each sidewall 112a and 112b. However, sheath 100 may include any number of cortical retaining tabs 108a and 108b.
[000144] As shown in Figure 4, the sheath 100 may also include anti-flattening tabs 128a, 128b, 128c and 128d integrally formed or positioned on the inner walls 126a and 126b to prevent flattening of the walls 126a and 126b beyond a position predetermined. In the illustrated embodiment, an edge of each of the first and second side walls 112a and 112b, extending adjacent the first and second elongate slots 114a and 114b, define four anti-flattening tabs. The flaps can move towards each other but act as a lock to prevent the side walls 112a and 112b from flattening out completely. Tabs 128a, 128b, 128c and 128d can thus allow the side walls to flatten towards each other when the sheath 100 and tendon are inserted into the bone, but before the procedure is completed and the screw 200 is inserted.
[000145] As indicated above, the sheath 100 is configured to receive therein a screw 200 which is effective to expand the sheath 100 to anchor the sheath 100 and the ligament attached thereto within a bone hole. As shown in Figure 8A , in one embodiment the screw 200 may have a generally cylindrical shape with a constant minor diameter D1 along at least a proximal portion 200p and preferably along most of the length, e.g. more half of the total length. A distal portion 200d of the screw 200 may taper distally inwardly to a reduced diameter at the most distal end. Screw 200 may have threads 202 formed along it and extending its entire length to facilitate engagement with sheath 100. Screw 200 may be fully cannulated to allow screw 200 to be applied over a wire-thread. guide 140, and screw 200 may have a proximally facing flat surface 206 and a distally facing flat surface 208. The proximal surface 206 and distal surface 208, however, may be of various shapes, and the shape may vary. be configured to conform to the sheath and/or bone surface. As further shown in Figures 8A and 9, the inner lumen 210 may have a diameter that is sized to receive a guidewire. At least a proximal portion of the inner lumen 210 may be shaped to receive a driving tool. For example, as shown in Figure 8A, the proximal portion 200p may have a hexagonal hole to receive a hexagonal driving tool.
[000146] Again with reference to Figure 1, the screw 200 can be inserted into the sheath 100 during use. Upon insertion into the sheath 100, the screw 200 can cause the sheath 100 to expand. In an exemplary embodiment, the threads 202 in the screw 200 have a height Ht (Figure 8) that is less than a height Hg (Figure 6) of the internal threads 124 formed in the sheath 100. This configuration will allow the smaller diameter D1 of the screw 200 contact the smaller inner diameter D1 (Figure 6) of the sheath 100 and thus cause the sheath 100 to expand. As a result, the threads 202 are not sized to cause the sheath 100 to expand and instead the diameter screw smaller than 200 causes expansion. Additionally, the screw 200 may be shaped to cause the thicker middle portion of the sheath 100 to expand radially outward by a distance that is greater than the proximal end 100p and the distal end 100d of the sheath, so that the middle portion 100 m forms the major diameter of the sheath 100 in the expanded state, as discussed above in connection with Figure 7.
[000147] One skilled in the art will understand that the expander may have a variety of other configurations, and the expander may be configured to be non-rotating into the sheath, rollable into the sheath, or partially into the sheath. non-rotating and partially rotating. Figure 8B illustrates one embodiment of an expander 220 that is configured to be partially non-rotably inserted into the sheath and then rotatably inserted into the sheath. In particular, expander 220 includes a proximal portion 220p having threads 222 formed thereon, and a distal portion 220d that is unthreaded and devoid of surface features. The length of the proximal and distal portions 220p and 220d may vary, but in an exemplary embodiment, each portion is about half the total length of the expander 220. The illustrated proximal portion 220p has a generally cylindrical shape with a constant minor diameter D1, and the distal portion 220d of the expander 220 tapers distally inward to a reduced diameter at the most distal end. Expander 220 may be fully cannulated to allow expander 220 to be applied over guidewire 140, and expander 220 may have a proximally facing flat surface 226 and a distally facing flat surface 228. In use , the unthreaded distal portion 220d of the expander 220 can be non-rotatably advanced into the sheath 100. Once the distal portion 220d is completely disposed within the sheath 100, the expander 220 can then be rotated to thread the proximal portion 220p in the sheath. The sheath may include corresponding threads along an entire inner surface thereof, or along a proximal portion of the inner surface thereof, for engagement with threads 222 on expander 220.
[000148] Figure 8C illustrates another embodiment of an expander 240 that is configured to be non-rotatably advanced into a sheath. In general, expander 240 has a generally cylindrical shape with a constant minor diameter D1 along a proximal portion 240p and a convex belly along a mid portion 240m to a distal portion 240d. Distal portion 240d of expander 240 is tapered distally inward to a reduced diameter at the most distal end. The middle portion 240m and the distal portion 240d may be free of any surface features, and may be relatively smooth. Proximal portion 240p, on the other hand, may include one or more ribs or flanges 242 formed thereon and extending circumferentially around it. In the illustrated embodiment, proximal portion 240p includes two longitudinally spaced ribs 242 formed thereon. Each rib 242 includes a proximally facing flat surface 242p and an outer side wall having a constant diameter proximal portion 242c and a tapered distal portion 242t. The ribs 242 have an outer diameter that is greater than the smaller inner diameter of the expander 240. The expander 240 may be fully cannulated to allow the expander 240 to be applied over a guidewire 140, and the expander 240 may have a flat surface. proximally facing 246 and a distally facing flat surface 248. In use, expander 240 may be non-rotatably advanced into sheath 100. Ribs 242 on proximal portion 240 may cause the sheath to expands outward, thereby anchoring the sheath within the bone hole. Sheath insertion device
[000149] Also shown are various insertion tools for inserting the sheath 100 and/or screw 200 into a bone hole. The insertion tool can also be used to perform various other functions in connection with inserting the sheath into a bone hole. For example, the anchor insertion tool can be effective for initially measuring a size of a tendon. Multiple insertion tools having different sizes can be obtained, with the sizes corresponding to the sheath and screw suitably sized for use with them. The insertion tool may also be configured to insert, or "insert" a tendon into a pre-drilled bone hole, and to hold the tendon within the bone hole while a sheath 100 is applied to the bone hole. The insertion tool may additionally be configured to receive a guidewire 140 therein, which is coupled to sheath 100. This may allow sheath 100, with guidewire 140 attached thereto, to be applied to a bone hole, and guidewire 140 can then remain with sheath 100 and facilitate application of an expander within the sheath. In certain exemplary embodiments, the insertion tool may be configured to fixedly engage the guidewire 140 so as to prevent movement thereof during insertion of the tendon and during application of the sheath 100, and may be configured to selectively release the guidewire. guidewire 140 once sheath 100 is deployed, to allow the tool to be removed from guidewire 140, leaving sheath 100 deployed with guidewire 140 extending therefrom.
[000150] Figures 10 to 17 illustrate an exemplary embodiment of a sheath insertion tool 300 and various components and features thereof. As shown, the sheath insertion tool 300 generally includes an outer component having a handle 302 with an outer shank 306 extending therefrom and an inner component including a trigger 304 that is slidably coupled to the handle 302, and an inner stem 310 extending from trigger 304 and through outer stem 306. Inner stem 310 includes features for sheath interaction. The sheath insertion tool 300 may also include features disposed within the handle 302 to control movement of the inner and outer rods 310 and 306 relative to one another, as will be discussed in more detail below.
[000151] The handle 302 can have a variety of configurations but, in the illustrated embodiment, the handle 302 in the outer component has a generally elongated cylindrical configuration to facilitate handling thereof. The handle 302 may have a hole extending therethrough from the distal end 302d and terminating in a position just distal to the most proximal end. In other embodiments, however, the hole may extend through the proximal end of the handle 302. The hole may be configured to receive various components to control the movement of the inner and outer rods relative to each other. A distal portion of the hole may receive the proximal end of the outer rod 306 to engage the rod in the handle. Cable 302 may additionally include elongated longitudinal cutouts 338a and 338b formed on opposite side walls thereof and in communication with the internal lumen. Cutouts 338a and 338b may allow the trigger 304 on the inner component to extend therethrough and move slidably along it.
[000152] Trigger 304 may also have various configurations but, as shown, trigger 304 is generally T-shaped and includes distally facing gripping surfaces 340a and 340b. Trigger 304 extends laterally outward from opposite sides of trigger 302 through cutouts 338a and 338b and thus allows a user to place proximal end 300p of handle 302 in their palm and hold trigger 304 with two fingers. to pull the trigger 304 proximally. The trigger can therefore slide proximally and distally with respect to the handle. As further shown in Figure 11A , trigger 304 may be fixedly fitted to, or integrally formed into, the proximal end of inner rod 310. As a result, movement of trigger 304 relative to handle 302 moves inner rod 310 relative to to the outer rod 306.
[000153] As noted above, the cable may include additional features to control the movement of internal and external components relative to each other. As shown in Figure 11A, the handle 302 includes a main displacement element 314, for example a spring, disposed therein and configured to apply a distal tilting force to the trigger 304. The main displacement element 314 thus pushes the trigger. trigger 304 and therefore inner rod 310 distally. To move trigger 304 and inner rod 310 proximally with respect to handle 302 and outer rod 306, the tilt force must be overcome to cause compression of the main displacement member 314. In an exemplary embodiment, a first force may be applied to move trigger 304 in a proximal direction along a first range of motion, i.e., a first distance, to cause at least partial compression of main displacement member 314. Trigger 304 may also move more proximally along a second range of motion, i.e., a second distance, but handle 302 may be configured to prevent proximal movement beyond the first range of motion, except when a second force is applied to trigger 304, with the second force being greater than the first force. The second displacement member 318, for example a spring, can provide the second force for proximal movement beyond the first range of movement. As shown in Figure 11A, secondary displacement element 318 is located proximal to primary displacement element 314.
[000154] The cable may also include a feature to engage the guidewire fitted to the sheath. In one embodiment, a guidewire retainer or guidewire clamp 316 may be disposed between the primary and secondary displacement elements 314 and 318. The guidewire retainer 316 may include a hole 342 formed therein. , which is configured to receive a proximal end of guidewire 140 fitted to sheath 100. Hole 342 is preferably sized to engage guidewire 140 by compression fit to hold guidewire 140 in place. a fixed position. In one embodiment, the guidewire retainer 316 may be formed from a compressible material to engage the guidewire. One skilled in the art will understand, however, that other techniques may be used to engage the guidewire. The guidewire jaw may move axially within the cable, and proximal movement to a certain position may cause the guidewire jaw to release the guidewire. Secondary displacement member 318 may apply distally oriented tilting force to guidewire retainer 316 to prevent proximal movement of the guidewire retainer until the second force is applied to cause the retainer to move proximally. and release the guide wire.
[000155] To allow the secondary displacement element to apply a secondary force, the proximal end of the secondary displacement element 318 may define a bearing surface. In particular, as shown, the handle 302 may include a more proximal element, for example a handle plunger 320, which abuts the most proximal inner surface of the handle 302, and which allows the secondary displacement element 318 to be compressed between this and guidewire retainer 316. In use, when trigger 304 is moved proximally a first distance through the first range of motion, primary displacement member 314 compresses. Secondary displacement member 318 applies a tilting force to guidewire retainer 316 that is sufficient to prevent proximal movement of guidewire retainer 316 and therefore to resist movement of trigger 304 beyond the first range of motion. movement. When desired, a greater force may be applied to move trigger 304 more proximally through the second range of motion. The greater force must be sufficient to overcome the tilting force of the secondary displacement element 318. As the trigger 304 is moved more proximally, beyond the first range of motion and through the second range of motion, the guidewire retainer 316 moves proximally to cause secondary displacement member 318 to exert compression. As will be discussed in more detail below, proximal movement of guidewire retainer 316 will release guidewire 140 as the mating connection between sheath 100 and guidewire 140, and the contiguity of sheath 100 against the end shaft 306, will prevent guidewire 140 from moving proximally with guidewire retainer 316. Sheath insertion tool 300 can thus be removed, leaving guidewire 140 behind.
[000156] One skilled in the art will understand that the cable may include other features, such as a locking mechanism, to releasably lock the internal and external components together. By way of non-limiting example, Figures 11B and 11C illustrate one embodiment of a locking mechanism that could be located on handle 302 and configured to engage a proximal portion of inner rod 310. The locking mechanism includes a latch 914 which may be arranged at various locations on the handle 302. The latch 914 is generally in the form of an elongate rod having a cutout formed therein. The cutout includes a longitudinally extending pin that is configured to be moved in and out of a hole in the proximal end of the inner rod 310. When the latch 914 is pushed toward one side of the handle 302 and the pin extends through a hole, the inner rod is prevented from moving. Conversely, when latch 914 is pushed towards the other side of the handle so that the pin is removed from the hole, the inner rod is free to move. Consequently, when in a locked position, lock 914 prevents proximal movement of the actuator and locks the inner and outer rods from moving longitudinally relative to each other. When in the unlocked position, the actuator and inner stem 310 can move proximally with respect to handle 302 and outer stem 306. One skilled in the art will understand that a variety of other locking mechanisms known in the art can be used to lock the internal and external components relative to each other.
[000157] As indicated above, the inner rod 310 is coupled to, and extends from, the trigger 304, and may have a generally elongated cylindrical shape with a fork 308 at a distal end 300d thereof. The fork 308 can function both to measure a tendon and to facilitate insertion of the tendon and sheath 100 into a bone hole. Figure 12A is an enlarged transparent view of yoke 308, and Figure 12B is an end view of yoke 308. As shown, yoke 308 includes first and second elongate pins 324a and 324b, which extend longitudinally along opposite sides of a cylindrical central portion 328. Each of the elongate pins 324a and 324b may have a generally square or rectangular cross-sectional shape, and the pins 324a and 324b may be coupled to the cylindrical central portion 328 by means of connectors 326 extending longitudinally along the entire length of the distal end. Connectors 326 may have a width Wc that is less than a width Wp of pins 324a and 324b. Central portion 328 may include a guidewire hole 330, or a channel extending therethrough and sized to slidably receive guidewire 140 fitted to sheath 100. The pair of pins 324a and 324b may extend distally. beyond connectors 326 and central portion 328 by a predetermined distance D to thereby define a U-shaped recess 322 between the pair of pins 324a and 324b. The U-shaped recess 322 may be configured to receive the sheath 100 therein, with the pins 324a and 324b extending into the recesses of the opposite side wall in the sheath 100. In one embodiment, the U-shaped recess 322 may include a cone-shaped protuberance formed thereon to support the sheath 100. The protuberance may have a proximal cylindrical portion with a tapered distal portion whose diameter decreases distally.
[000158] One of skill in the art will understand that the first and second elongated pins of the fork can have a variety of other configurations. Figures 12C and 12D illustrate an embodiment of an insertion tool that is similar to the insertion tool 300 and includes an outer shank 306' and an inner shank (not shown) with a fork 308' at the distal end thereof. In this embodiment, the yoke 308' has pins 324' which are deformable and which can be configured to curve or flex outward in a generally convex configuration. The inner rod and yoke 308' can be configured to be locked relative to the outer rod 306' and in use this type of configuration can help to fully introduce a sheath into a shallow bone hole where the sheath length is shorter. than the depth of the hole in the bone, but the total length of the extended and locked retractable insertion forks is longer than the depth of the hole in the bone. In particular, Figure 12C illustrates pins 324' having a generally linear configuration. Once inserted through a bone hole H and into bone B, the extended and locked retractable insertion fork 308' may be of a length that allows the pins 324' to be in contiguity against an opposite inner surface of bone B. pins 324' can thus deform and bend outward, as shown in Figure 12D. Outward expansion of pins 324' will occur below the proximal cortex, against the innermost cortical wall, thus helping to anchor the sheath (not shown) fully flush within the bone hole.
[000159] Figure 13 illustrates the yoke 308 extending from the distal end of the outer shank 306. As shown, the outer shank 306 has an outer diameter Db that is greater than a maximum width Wp of pins 324a and 324b. This type of configuration will allow the proximal end of the sheath to be in contiguity with the distal end of the outer rod 306 when the yoke 308 is inserted into the sheath 100.
[000160] As indicated above, the inner shank can move axially relative to the outer shank to retract and extend the yoke in and out of the outer shank 306. As shown in Figure 14A, the end surface facing the cylinder 306d may include a cutout 336 formed therein that is shaped to match the shape of the yoke 308 on the inner shank 310. The notch 336 thus allows the yoke 308 to be fully retracted into the outer shank 306 as shown in Figure 14A, and also allows the guidewire 140 to be received therein. When fully assembled, the guidewire 140 and the sheath 100 fitted thereto can be slid in a proximal direction into the distal end of the outer stem 306. The guidewire 140 can be moved proximally until the proximal end of the guidewire is guide 140 is received within, and engaged with, guidewire retainer 316 on handle 302. The sheath will abut the distal end of the cylinder to prevent further proximal movement of the sheath and guidewire.
[000161] In another embodiment, shown in Figures 14B and 14C, the outer rod 306'' may include indentations or recesses 307'' which are configured to seat the anti-sink tabs over the proximal end of the sheath 100. The recesses 307 '' may be formed on opposite sides of the cutout 336'' to allow the anti-sink tabs on the sheath to remain without the distal end of the outer shank 306''. As further shown in Figures 14A and 14B , outer shaft 306'' may optionally include features to facilitate percutaneous insertion of outer shaft 306'' through tissue. For example, a concavity 308'' (only one is shown) can be formed on opposite sides of the outer shaft 306'' adjacent to the distal end to reduce the profile of the outer shaft and thus facilitate insertion of the distal end through the distal end. tissue. The concavity 308'' in each side wall can also seat the tendon, providing relief to the tendon during advancement of the sheath into the bone hole.
[000162] Figure 15 illustrates the sheath 100 loaded onto the distal end of the inserter. As shown, the outer shank 306 may have a diameter 306d that is greater than the major diameter of the ribs in the sheath 100, and that is greater than a maximum width between the pins 324a and 324b on the fork of the insertion tool. The outside diameter of the outer rod 306 can be scaled to the width of the anti-sink tabs 110a, 110b, 110c and 110d so that the distal end of the outer rod 306d can thus operate in conjunction with the anti-sink tabs. 110a, 110b, 110c, and 110d into the sheath 100 to prevent over-insertion of the sheath 100 into the bone, as both the outer rod 306 and the anti-sink tabs 110a, 110b, 110c, and 110d may be in contiguity with the surface of the bone when the sheath is inserted into an appropriately sized bone hole. The bone hole is preferably milled using a drill that is sized to match the selected size of the sheath insertion tool 300. In particular, the bone hole may be milled to have a diameter that is slightly larger than the diameter of ribs 106a, 106b, 106c, 106d and 106e in sheath 100, but less than the maximum width of anti-sink tabs 110a, 110b, 110c and 110d in sheath 100. The distal end of outer rod 306 will also prevent proximal movement of the sheath 100 relative to the insertion tool, thereby maintaining the sheath and guidewire attached thereto in a fixed position, as will be discussed below.
[000163] In one embodiment, the sheath insertion device can be obtained in multiple sizes that correspond to the size of the tendon and anchor. Figures 16A and 16B illustrate the sheath inserter of Figures 10 and 11A, with Figure 16A showing a small size 300s sheath inserter and Figure 16B showing a large size 300l sheath inserter as This is evident from the increased size of the 306l outer shank and the 308l fork. Figures 17A to 17C illustrate the use of the inserter. In Figure 17A, yoke 308 is in the initial rest position, extending from outer shank 306. In Figure 17B, yoke 308 is shown fully retracted into outer shank 306, with trigger 304 moved proximally through the first range of motion. Figure 17C shows complete retraction of yoke 308 within outer shaft 306, and illustrates that further proximal movement through the second range of motion can release guidewire 140. Sheath insertion tool 300 is preferably inserted percutaneously through tissue, with fork 308 in the fully retracted position. driving device
[000164] Various driving devices are also presented to drive an expander into the sheath, once the sheath is implanted in a bone hole. Figures 18 and 19 illustrate an exemplary embodiment of a driving tool 400. As shown, the driving tool 400 generally includes a driving handle 402 having an inner shank 410 extending distally therefrom, and a handle. 404 having an outer stem 406 extending distally therefrom. The inner rod 410 extends through the gripper 404 and the outer rod 406, with the lead wire 402 positioned close to the gripper 404. An anti-rotation yoke 408 is located at a distal end of the outer rod 406 and can be configured to prevent rotation of sheath 100, as inner rod 410 is used to thread screw 200 into sheath 100. Inner rod 410 may include a guidewire channel 430 extending therethrough to allow guidewire 140, fitted to the sheath 100, is received therein.
[000165] Inserter handle 402 and inner shaft 410 can have a variety of configurations. In the illustrated embodiment, the lead wire 402 has a generally elongated cylindrical configuration to facilitate gripping. A hole 403 may extend through the handle and may include a proximal portion 403a that is sized to receive the guidewire, and an enlarged distal portion 403b to receive a proximal end of inner stem 410. Inner stem 410 is preferably , fixedly fitted with, or integrally formed with, the lead wire 402. As shown in Figure 19, the proximal end 410p of the inner stem 410 includes socket screws 418a, 418b, and 418c to securely and securely engage the inner stem 410 to the lead wire 402. However, other techniques, such as various mechanical coupling mechanisms, soldering, adhesives, etc., may be used.
[000166] Inner rod 410 may have a generally elongated cylindrical configuration with a distal end 410d that is configured to fit an expander, such as screw 200. For example, distal end 410d may include a driving tip 432 formed in the same by engagement with screw 200. In the illustrated embodiment, driving tip 432 has a hexagonal configuration to extend into a corresponding hex socket wrench formed in the screw to thereby allow inner rod 410 to rotate screw 200. In other embodiments, other alternative shapes may be used that non-swivel fit together. Inner rod 410 may additionally include a guidewire channel 430 extending therethrough to allow screw 200 and inner rod 410 to be slidably advanced over guidewire 140 fitted to sheath 100, as will be discussed in more detail below.
[000167] Handle 404 and outer rod 406 may also have a variety of configurations but, as shown in Figures 18 and 19, handle 404 is generally cylindrical, with first and second opposing alignment indicators or tabs 414a and 414b . Tabs 414a and 414b may be aligned with pins 424a and 424b on anti-rotation yoke 408, discussed below, to indicate the position of pins 424a and 424b to a user wielding handle 404. Outer rod 406 may have a cylindrical configuration. generally elongated, with a proximal end 406p that is received within an internal lumen that extends through handle 404. Proximal end 406p of outer rod 406 may be fixedly engaged with handle 404 using socket screws 412a and 412b , or other docking techniques.
[000168] As indicated above, the outer rod 406 and the handle 404 can be slidably arranged over the inner rod 410. In an exemplary embodiment, the outer rod 406 and the inner rod 410 can rotate freely with respect to each other, however, the longitudinal movement of the inner rod 410 and the outer rod 406 relative to each other is limited. As shown in Figure 19, the inner rod 410 may include locking pins 416a and 416b disposed thereon and projecting radially outward from opposite sides thereof. Locking pins 416a and 416b may be located just distal to the proximal end of inner stem 410. When handle 404 is disposed on inner stem 410, locking pins 416a and 416b may be positioned within inner lumen 434 , extending through gripper 404. Locking pins 416a and 416b and gripper 404 may be configured so that locking pins 416a and 416b only allow gripper 404 to slide proximally and distally a predetermined distance. In particular, handle 404 may include a reduced diameter region 428d adjacent the distal end, which limits distal movement of the pins 416a and 416b, and a reduced diameter region 428p adjacent the proximal end, which limits proximal movement of the pins. The proximal reduced diameter region 428p may, however, include opposing pin slots 420a and 420b formed therein to allow pins 416a and 416b to pass therethrough when properly aligned with slots 420a and 420b. This type of configuration allows the handle 404 and the outer shaft 406 to be removed from the inner shaft 410 and the lead wire 402, for example for cleaning.
[000169] As noted above, the distal end 406d of the outer shank 406 may include an anti-rotation yoke 408 having opposing first and second distal pins 424a and 424b, extending distally from opposite sides of the outer shank 406. The pins 424a and 424b may be configured to extend into side wall slots in sheath 100 to prevent rotation of sheath 100 when inner rod 410 is rotated to drive screw 200 into sheath 100. Figures 21 through 23 illustrates pins 424a and 424b in more detail. As shown, each pin has a generally triangular configuration, and extends from a semi-cylindrical side wall. The pins can therefore extend into the slots in the sheath 100 while the side wall is adjacent to a proximal end surface of the sheath. This type of configuration will limit the insertion of the driving tool 400 into the sheath 100.
[000170] As additionally shown in Figures 21 to 23, the external shank 406 may also include features to facilitate the visualization of the screw 200 coupled to the driving tool 400 and arranged inside the external shank 406. For example, the shank outer 406 may include one or more viewports or viewports 426 formed therein at a location adjacent the distal end. Viewing windows 426 in the illustrated embodiment are in the form of elongated oval indentations formed through both side walls on opposite sides of the shank and in alignment with pins 424a and 424b. However, viewports can be in various locations and can have various settings to allow visibility into the inner lumen. As further shown, outer shaft 406 may also include tendon cutouts 422a and 422b positioned on opposite sides of outer shaft 406 and offset relative to pins 424a and 424b and viewing windows 426 by about 90 degrees. The tendon cutouts 422a and 422b may allow a tendon wrapped around the sheath 100 to protrude into the cutouts if necessary.
[000171] In use, as shown in Figures 24A and 24C, the screw can be fitted to the driving tip 432 on the inner shank 410. The anti-rotation yoke 408 can be advanced over the screw 200 so that the anti-rotation yoke 408 can be advanced over the screw 200, so that the anti-rotation yoke 408 rotation 408 can extend into the slots in the sheath 100 to prevent rotation of the sheath during insertion of the screw into the sheath. When the pins are seated within the slots in the sheath, the lead wire 402 can be rotated with respect to the handle 404 to thereby rotate the inner rod 410 within the outer rod 406. The inner rod 410 will therefore rotate and driving screw 200 into sheath 100 while outer rod 406 holds sheath 100 stationary and prevents it from rotating. This type of configuration is particularly advantageous as it prevents tendon rotation as the tendon is positioned around the sheath. In addition, the anti-rotation yoke 408 may also be effective in preventing the sheath 100 from returning out of the tunnel during insertion of the screw 200. Without the anti-rotation yoke 408, the tendon may have a tendency to pull the sheath out of the bone hole. The anti-rotation fork 408 can thus be used to push the sheath into the bone hole until the anti-sink tabs on the sheath rest against the surface of the bone.
[000172] The driving device may also include markings for ease of use. For example, one or more laser-etched lines can be formed on the inner and/or outer shank to indicate the position of the outer shank relative to the inner shank, thereby indicating the position of the screw relative to the sheath. In the illustrated embodiment, a first marking, in the form of a laser engraved strip 407, extends around the distal end portion of the outer shank 406 on the insertion tool, as shown in Figure 21. A second marking, under the In the form of a laser engraved band 411, it extends around the distal end portion of the inner rod 410, as shown in Figure 19. Alignment of the band 411 on the inner rod with the band 407 on the outer rod will indicate that the expander screw is fully inserted into the sheath. A pair of markings may also or alternatively be formed on the proximal portion of the device. As shown in Figure 19, the inner rod 410 may include a pair of markings, in the form of laser-etched strips 413 and 415, which are located distal to the lead wire 402. The distal strip 415 will align with the surface. proximal end of handle 404 when the device is in the initial configuration, before driving the expander screw into the sheath. The distal band 413, when aligned with the surface of the proximal end of the handle 404, will indicate that the expander screw is fully inserted into the sheath. Charger
[000173] The driving tool 400 may also optionally be used with a screw magazine cartridge 500 to facilitate loading the screw 200 over the guide wire to apply the screw to the sheath. Figure 25 illustrates one embodiment of a bolt-loader cartridge 500. The bolt-loader cartridge 500 can be formed from a variety of materials, such as metal or a molded plastic, and can have a variety of shapes and configurations. In the illustrated embodiment, the screw-loader cartridge 500 includes a proximal portion 500p with tabs 502 formed therein to facilitate gripping, and a distal portion 500d that is shaped like a funnel 504 that is cut almost in half. Screw magazine cartridge 500 can thus have a generally flatter side, as shown. An elongated channel 506 may be formed in the proximal portion 500p, and may extend towards the funnel 504, and may communicate with the funnel 504. The channel 506 may be shaped to seat the screw 200 and, optionally, a distal portion of the driving tool 400, including anti-rotation yoke 408. For example, screw loader cartridge 500 can seat screw 200 and anti-rotation yoke 408 on the outer shank so that the outer shank is in its most comfortable position. proximal and is prevented from making any further movement. This type of configuration can help prevent rotation and axial translation of the inner and outer shanks of the driving tool when the magazine and expander are attached to the tool. This can be particularly desirable for packaging and preventing movement during transport, until use of the device. Screw 200 may be held within channel 506 by snap-fitting, or using other techniques known in the art. When the screw 200 is seated within the channel 506, the guidewire channel (not shown), extending through the screw 200, may align with the opening of the funnel 504. In use, the guidewire may, therefore, be inserted into the funnel 504, which will thereby guide the guidewire into the screw 200 for ease of insertion.
[000174] Figures 26A through 26D illustrate the use of the 500 screw loader cartridge to load the screw onto the guide wire. Figure 26A is a side view of the bolt magazine cartridge 500, showing the bolt 200 therein. As shown in Figure 26B, screw 200 can simply be loaded sideways into channel 506. As shown in Figure 26C, funnel 504 can receive and guide guidewire 140 into screw 200. As shown in Figure 26D, once As long as the bolt 200 is advanced along the guide wire 140, the tabs 502 on the bolt loader cartridge 500 can be grasped and used to pull back the bolt loader cartridge 500, and disengage the bolt loader cartridge 500 from the bolt 200 • The charger can be discarded or, optionally, sterilized and reused. Components can optionally be transported with the screw and magazine preloaded on the driving tool. tendon size gauge
[000175] As explained above, the fork in the inserter can be used to measure a size of a tendon to be anchored. In other embodiments, a separate tool may additionally or alternatively be used to measure a tendon. Figures 27A through 31 include various modalities for measuring the size of a tendon. In the embodiment of Figure 27A, tendon size gauge 710 generally includes a handle 711 with a shank 712 extending distally therefrom. A distal end of rod 712 includes a size gauge 713 having a number of indentations formed therein, each of a different size. A tendon can be positioned inside each cutout until the size of the tendon matches the size of the cutout. Markings (not shown) can be arranged on the tool to indicate either the size of the tendon, or the size of the implant and toolkit to be used in connection with a tendon anchoring procedure. Figure 27B illustrates a similar size 714 gauge, but the cutouts are aligned axially along the distal end, rather than positioned in a circular orientation as in the embodiment of Figure 27A.
[000176] Figure 28 illustrates another embodiment of a tendon measuring device 720 that is similar to the device of Figure 27A, but which includes a retractable wire loop 723 at a distal end thereof. A gripper 724 on handle 721 can be slid proximally and distally to adjust a size of loop 723. A tendon can thus be positioned within the loop, and once adjusted to match the size of the tendon, the device can indicate the size to the user.
[000177] Figures 29 to 31 illustrate another embodiment of a tendon measuring device 730 that is similar to the device of Figure 28, but instead of using an adjustable wire loop, the device 730 includes an adjustable arm 733 which moves relative to a stationary arm 734 to allow a size of a tendon to be measured.
[000178] In other embodiments, a combination of tendon measuring device and bone hole preparation device is shown. Figures 32 to 33C illustrate various other devices for determining tendon size and/or reaming a bone hole. In Figure 32, a guidewire and bone milling tool combination 760 is shown. In general, the device has a shank with a distal end in the form of a mandrel for milling a bone hole, and a guidewire extends through the stem. Figures 33A to 33C illustrate a device which is similar to the device of Figure 32, but which is in the form of a combination chuck and size measuring tool 770. In particular, the chuck includes a bifurcated size gauge 772 disposed over it in a sliding manner. As the 772 forked size gauge extends from the distal end of the chuck, the yoke expands in size to measure tendons of different sizes. The device may include markings or other features on a proximal end (not shown) to indicate the size of the measured tendon and/or the size of the implant and toolkit to be used with the tendon.
[000179] In another embodiment, as shown in Figures 34A to 34C, there is shown a tendon measuring device 780 which has a caliper 780 for measuring the size of a tendon. Device 780 includes a handle 781 having an elongate shank 782 extending distally therefrom, with feeler gauge 780 formed over the distal end thereof. In use, the 780 caliper can be inserted and pressed over the biceps tendon at the reamer and insertion site as shown in figures 34B to 34C. If the tendon compresses to a 780 gauge width, the tendon needs a small size implant and tool set. If the tendon compresses and is larger than the 780 caliper, as shown in Figure 34C, then the 780 caliper needs an oversize implant and tool kit.
[000180] Figures 35 to 37 illustrate another embodiment of a device 810 that can be used to prepare a bone hole. Device 810 includes a generally L-shaped handle 812 having first and second legs, 814 and 816, extending from opposite ends thereof. Each rod may include a bone hole cutter 814a and 816a formed at a distal end thereof. While the shape of the bone hole cutters 814a and 816a may vary, in an exemplary embodiment, as shown in Figure 37, each cutter may have a generally triangular configuration with truncated corners. One of the cutters, for example cutter 814a, may have a first size, and the other cutter, for example 816a, may have a second size that differs from the first size. For example, cutters can be supplied in small and large sizes, which correspond to small and large sizes of implants and tools. The user can thus select the rod and cutter having a suitable size. As indicated above, cutters can have a variety of configurations. Figures 38-39 illustrate additional cutting tip configurations to form a bone hole of a desired shape. In Figure 38, the cutting device 824 includes a tip that has a protuberance 824b extending from one side thereof to form a notch in a proximal end of a bone hole. The device may optionally include two protrusions to form two notches. In Figure 39, cutter 826b in device 826 has a configuration that forms a rounded edge on top of the bone hole. Method
[000181] The various implants and devices disclosed herein can be used to perform a variety of procedures in which it is desirable to anchor tissue to bone. Figures 40A to 40E illustrate an exemplary method for performing biceps tenodesis surgery. Although the method is described in connection with the system of Figure 1, one skilled in the art will understand that the method can be performed using various anchors and tools, and that it can be performed to anchor any tissue to any bone.
[000182] In a biceps tenodesis procedure, a biceps tendon is obtained, for example with the use of suture, and a size of the tendon needs to be determined to allow a surgeon to select appropriately sized implant and tools. This can be accomplished using the sheath insertion tool 300. In particular, with the yoke of the inner shank fully retracted into the outer shank, the sheath insertion tool 300 can be passed through tissue and placed adjacently. to the tendon and the implant site. As shown in Figure 40A, the yoke on the sheath insertion tool 300 can be manipulated to position the tendon 600 within the yoke. If multiple insertion tools are available, the smallest tool is preferably used first and the tendon is positioned between the forks at the distal end. If the tendon fits, then the implant (sheath and screw) that matches the size of the sheath insertion tool will be used. If the tendon is too large and does not fit between the yoke pins, the next size insertion tool can be used to re-measure the tendon. In an exemplary embodiment, a kit is shown having a small and a large sheath inserter (sheath and screw), as well as a small and a large screwdriver, and a small and a large magazine. After properly sizing the tendon, the appropriately sized mandrel can be used to mill a hole in the bone, for example the humerus.
[000183] Various bone hole preparation devices can be used. During a biceps tenodesis procedure, improper preparation of the bone hole, including rough or uneven edges, can cause tendon damage, including rupture or trauma. In some embodiments, a double- or triple-ended tool can be used, which breaks the edge of the opening in the bone with a quarter turn back and forth. For example, the tool in Figures 35-36 can be inserted percutaneously, and the appropriately sized tip can be selected, inserted into the bone hole, and rotated by hand to form a bone hole opening, as shown in Figure 37. Alternatively, the device of Figure 38 or Figure 39 can be used to create an angled surface within the bone hole. Angled surfaces can offer an alternative means of bone hole preparation that can mitigate the potential for tendon rupture or tearing at a sharp edge of bone.
[000184] After the bone hole has been prepared, the tendon can be introduced into the bone hole using the appropriately sized insertion tool. The sheath and guidewire can be loaded into the insertion tool before introducing the tendon. As shown in Figure 40B, guidewire 140 can be threaded into the internal hole in sheath 100, which can be loaded into the distal end of sheath insertion tool 300. This can be accomplished by advancing the proximal end of the guidewire. guide 140 into the distal end of sheath insertion tool 300, and guide wire 140 moving proximally until guide wire 140 is snap-fitted into the guide wire retainer on the handle. The guidewire and sheath, or the guidewire, sheath and insertion tool, can be optionally pre-packaged together in a docked configuration.
[000185] Figures 40C to 40E illustrate various steps of inserting the sheath 100 and tendon 600 into the bone hole 602. For example, the fork 308 may be retracted by pulling the trigger proximally through the first range of motion to allow percutaneous insertion through the skin. The sheath tip can serve as an obturator to pass the sheath and insertion tool through the fabric. Once through the tissue, the operator can release the trigger to allow the yoke 308 to extend distally off the outer shank. The fork 308 can be positioned around the tendon 600. A suture can be used to tension the tendon, and the forks can be placed proximal or distal to the hole with the tendon therebetween. The sheath will thus rest against the tendon. The fork 308, with the tendon attached thereto, can then be slid back toward the hole 602 and inserted into the hole 602, as shown in Figure 40C. The diameter of the bone hole can be sized to allow the fork 308 and sheath to be easily inserted therein. Some resistance may be encountered due to the tendon being wrapped around the sheath. As the outer shaft of the sheath insertion tool 300 is oversized compared to the tunnel 602, the outer shaft will be prevented from entering the bone hole 602. If resistance is encountered, the proximal end of the insertion tool can be struck with a mallet. . Cortical bone is typically only 1 mm to 2 mm thick. When striking with the mallet, the objective is to pierce the cortical retaining tabs into the hole, until the anti-sinking tabs of the sheath 100 are in contiguity with the surface of the bone, so that excessive insertion of the sheath into the hole. The cortical retention tabs are preferably sized so that they do not cut through the bone when inserted therethrough. During the insertion process, the fork 308 continues to hold the tendon 600 firmly against the bone 602. When the sheath 100 is fully inserted, the anti-sinking tabs and the distal end of the outer rod will rest against the bone, as shown in Figure 40D , and the cortical retention flaps will extend below the cortical bone. The sheath insertion tool 300 can be removed by pulling the trigger through the first range of motion to retract the yoke, and even more proximally through the second range of motion to thereby release the guidewire 140 from the cable. Sheath insertion tool 300 can then be slid off guidewire 140, leaving sheath 100 in bone hole 602 with guidewire 140 extending therefrom, as shown in Figure 40E.
[000186] Once the sheath insertion tool 300 has been removed, the screw 200 can be driven into the sheath 100 using the driving tool 400. The screw 200 can be loaded into the driving tool 400 using the use of the magazine cartridge or, as indicated above, the screw, magazine and driving device can be pre-packaged in a complete set configuration. As discussed above, the loading flap has a tapered distal tip to aid in positioning the guidewire on the screw 200. The funnel can therefore be advanced over the guidewire which is secured to the implanted sheath. The funnel will thus guide the guidewire into the screw, which can be slid a distance along the guidewire. If desired, the screw conductor can be advanced over the guide wire together with the screw. The magazine can then be removed and the driving tool 400 can be used to advance the screw 200 into the sheath 100, as shown in Figures 41A through 41C. The pins on the outer shank of the driving tool 400 will extend into the slots in the sheath 100, as shown in Figure 41D. The driving tool 400 can hold the sheath 100 inside the bone hole 602, preventing it from backing out during insertion of the screw 200. The viewing windows, opposite each other and aligned with the teeth, can facilitate visualization of the screw, and the lateral cutouts offset from the viewing windows can receive the tendon so as to allow the outer rod to rest against the sheath, as shown in Figure 41D. In some embodiments, the outer rod could be formed from a transparent material to allow visualization therethrough.
[000187] Once the driving tool 400 is supported with the outer shaft resting against the bone, the handle of the outer shaft is held stationary while the handle of the inner shaft is rotated to drive the screw 200 into the sheath 100, as shown in Figure 41E. In one embodiment, as discussed above, the shank may have two laser etched lines, one on the inner shank and the other on the outer shank. When they are aligned, screw 200 is fully inserted. The proximal end of the inner rod may also have a line that will align with the handle on the outer rod to indicate full insertion of the screw 200 into the sheath 100. The line can be particularly useful when the procedure is performed without a scope (eg. (e.g., sub-pectoral during mini-open procedure). When screw 200 is fully inserted into sheath 100, the screw will cause the sheath to expand radially outward to engage the tendon between the sheath and the bone hole, and thereby anchor the sheath and tendon within the hole. bone. The ribs on the outer surface of the sheath can engage the bone to prevent them from coming back out. The expanded middle portion of the sheath, as well as the cortical retaining flaps, may also help to retain the sheath within the bony orifice. As shown in Figures 41F through 41G, once the screw 200 is fully inserted into the bone hole, the driving tool 400 can be slid off the guide wire 140. The guide wire 140 can be removed, for example, by by bending the proximal end and rotating the guidewire 140 to unthread it from the sheath 100.
[000188] One skilled in the art will understand that the methods and devices for biceps tenodesis disclosed herein can be used in a variety of surgical procedures for trauma or damage to a tendon being attached to a bone through a bone hole. The present invention also has applications in conventional joint repair surgery.
[000189] The devices described here may be designed to be discarded after a single use, or they may be designed to be used multiple times. In either case, however, the device may be refurbished for reuse after at least one use. Refurbishment can include any combination of the steps of disassembling the device, followed by cleaning or replacing specific parts and then reassembly. In particular, the device can be disassembled and any number of specific parts or parts of the device can be selectively replaced or removed, in any combination. When cleaning and/or replacing specific parts, the device can be reassembled for subsequent use at the refurbishment facility, or by a surgical team, immediately prior to a surgical procedure. Those skilled in the art will understand that refurbishing a device can use a variety of techniques to disassemble, clean/replace, and reassemble. The use of such techniques and the resulting refurbished device are within the scope of this application.
[000190] Preferably, the present invention described herein will be processed prior to surgery. First, a new or used instrument is obtained and, if necessary, cleaned. The instrument can then be sterilized. In a sterilization technique, the instrument is placed in a closed and sealed container, such as a plastic or TYVEK bag. The container and instrument are then placed in a field of radiation that can penetrate the container, such as gamma radiation, X-rays, or high-energy electrons. Radiation kills bacteria on the instrument and container. The sterilized instrument can then be stored in a sterile container. The sealed container keeps the instrument sterile until it is opened in the medical facility.
[000191] It is preferred that the device be sterilized. This may be accomplished in any number of ways known to those skilled in the art including beta or gamma radiation, ethylene oxide or steam.
[000192] Those skilled in the art will understand other features and advantages of the invention based on the embodiments described above. Accordingly, the invention is not to be limited by what has been particularly shown and described, except as indicated by the appended claims. All publications and references cited are expressly incorporated herein by reference in their entirety.

权利要求:
Claims (12)
[0001]
1. An anchor driving tool, comprising: an outer shank (406) having first and second pins (424a, 424b) that extend distally from a distal end thereof and is configured to extend into opposing slots formed in a sheath (100) of an anchor assembly; an inner rod (410) which extends through the outer rod and which has a distal end configured to mate with an expander (200, 220, 240) of an anchor assembly; and a cable assembly coupled to a proximal end of each of the inner and outer rods, the cable assembly including an actuator configured to rotate the inner rod relative to the outer rod to drive an expander coupled to a distal end of the inner rod into a sheath coupled to the first and second pins of the outer rod, the outer rod being configured to hold the sheath in a fixed position during rotation of the inner rod; characterized in that at least one marking (407, 411) is formed on at least one of the inner and outer rods to indicate when an expander is fully seated within a sheath.
[0002]
2. An anchor driving tool, according to claim 1, characterized in that the actuator comprises a handle (402) at a proximal end of the inner rod, and the cable assembly includes a stationary cable (404) in a proximal end of the outer rod.
[0003]
3. An anchor driving tool, according to claim 1 or claim 2, characterized in that the outer shank includes opposing viewing windows (426) formed in a distal portion thereof.
[0004]
An anchor driving tool according to any one of claims 1 - 3, characterized in that the outer shank includes opposing cutouts (422a, 422b) formed at the distal end thereof to seat a graft.
[0005]
5. Anchor driving tool, according to any one of the preceding claims, characterized in that the outer shaft is movable to rotate freely with respect to the inner shaft, and the axial translation of the outer shaft in relation to the inner shaft is limited at a predetermined distance.
[0006]
6. A tendon anchor system, comprising: an anchor assembly having a sheath (100) having a generally elongated cylindrical configuration with at least two side walls (112a, 112b) at least partially separated by at least the first and the second slits (114a, 114b), the side walls defining an inner lumen therebetween, and an expander (200, 220, 240) configured to be received within the inner lumen of the sheath; and an inserter assembly (400) having an outer shank (406) having first and second pins (424a, 424b) formed at a distal end thereof, the pins being sized and sized to be received within the first and from the second slots in the sheath, an inner rod (410) extending through the outer rod and having a distal end configured to mate with the expander, and a cable assembly coupled to a proximal end of each of the inner rods and external, the cable assembly having an actuator configured to rotate the inner rod to drive the expander into the sheath while the pins on the outer rod hold the sheath in a fixed position; and characterized in that the tendon anchoring system further comprises at least one marking (407, 411) formed on at least one of the inner and outer rods to indicate when the expander is fully seated within the sheath.
[0007]
7. A tendon anchor system according to claim 6, characterized in that the actuator comprises a handle (402) at a proximal end of the inner rod, and the cable assembly includes a stationary cable (404) in a proximal end of the outer rod.
[0008]
8. A tendon anchor system, according to claim 6 or claim 7, characterized in that the external rod includes opposing viewing windows (426) formed in a distal portion thereof.
[0009]
A tendon anchor system according to any one of claims 6 - 9, characterized in that the outer rod includes opposing cutouts (422a, 422b) formed at the distal end thereof to seat a tendon.
[0010]
10. Tendon anchoring system, according to any one of claims 6 - 9, characterized in that the external rod is movable to rotate freely in relation to the internal rod, and the axial translation of the external rod in relation to the internal rod is limited to a predetermined distance.
[0011]
11. A tendon anchor system according to any one of claims 6 - 10, characterized in that the pins have a length that is less than a length of the first and second slots, so that the pins extend only partially on them.
[0012]
12. A tendon anchor system according to any one of claims 6 - 11, characterized in that it comprises a loader (500) that has a route that extends therethrough between the proximal and distal ends thereof to seat the expander and a distal portion of the outer shaft, the magazine including a tapered distal end (500d).

类似技术:

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公开号 | 公开日 | 专利标题

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BR102015026825B1|2022-01-11|ANCHOR DRIVING TOOL AND TENDON ANCHORING SYSTEM

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BR102015026738B1|2022-01-11|ANCHOR SET TO ANCHOR A TENDON TO A BONE

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BR102015026730A2|2016-04-26|biceps tenodesis implants and application tools

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US11065104B2|2021-07-20|Tenodesis anchoring systems and tools

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US10517613B2|2019-12-31|Systems, devices, and methods for guiding surgical devices into bone

同族专利:

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公开号 | 公开日

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EP3011932B1|2018-11-28|

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JP2016083363A|2016-05-19|

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CA2909946A1|2016-04-23|

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CN105559838A|2016-05-11|

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BR102015026825A2|2016-04-26|

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US20160113643A1|2016-04-28|

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AU2015243089B2|2020-05-14|

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US10729419B2|2020-08-04|

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US20200129171A1|2020-04-30|

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AU2015243089A1|2016-05-12|

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EP3011932A1|2016-04-27|

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JP6643039B2|2020-02-12|

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法律状态:
2016-04-26| B03A| Publication of a patent application or of a certificate of addition of invention [chapter 3.1 patent gazette]|

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2018-10-30| B06F| Objections, documents and/or translations needed after an examination request according [chapter 6.6 patent gazette]|

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2020-03-10| B06U| Preliminary requirement: requests with searches performed by other patent offices: procedure suspended [chapter 6.21 patent gazette]|

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2021-11-09| B09A| Decision: intention to grant [chapter 9.1 patent gazette]|

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2022-01-11| B16A| Patent or certificate of addition of invention granted [chapter 16.1 patent gazette]|Free format text: PRAZO DE VALIDADE: 20 (VINTE) ANOS CONTADOS A PARTIR DE 22/10/2015, OBSERVADAS AS CONDICOES LEGAIS. |

优先权:

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申请号 | 申请日 | 专利标题

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US201462067701P| true| 2014-10-23|2014-10-23|

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US62/067,701|2014-10-23|

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US14/610,618|US10729419B2|2014-10-23|2015-01-30|Biceps tenodesis implants and delivery tools|

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US14/610,618|2015-01-30|

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