CA1336058C

CA1336058C - Ligament attachment method and apparatus

Info

Publication number: CA1336058C
Application number: CA000566630A
Authority: CA
Inventors: E. Marlowe Goble; W. Karl Somers
Original assignee: Individual
Current assignee: Individual
Priority date: 1987-02-17
Filing date: 1988-05-12
Publication date: 1995-06-27
Anticipated expiration: 2012-06-27
Also published as: EP0342281A1; US4772286A; AU1618288A; JPH01314559A; AU606949B2

Abstract

The invention provides apparatus for use in a system for surgically implanting an allograft or prosthetic ligament as a replacement for a patient's cruciate ligaments. In a practice of the system, as a replacement for an anterior cruciate ligament, the patient's leg is bent and maintained at approximately a ninety degree (90°) angle, a single incision is made medial o the tibial tuberosity. From this incision, under fluoroscopic and arthroscopic control, a guidewire is driven through the tibia and across the cruciate ligament junctions with the proximal tibia and distal femur ends and into the femur cortex. Successively larger drills are then turned along the guidewire to form a ligament tunnel, with, as a last step in the tunnel formation process, the preparation of the femur cortex end of the tunnel to receive a femoral connector of the implanted ligament, which connector is arranged in one embodiment to be outwardly flared and in another embodiment to be turned into the appropriately prepared femur end of the ligament tunnel to lock therein. the invention, in addition to the embodiments of the ligament femur end connectors, further includes a tibial surface ligament tibial end connector for both securing the ligament end to the bone and for setting ligament tensioning, of which ligament connectors can be manufactured from a biodegradable material for absorption by the body.

Description

S P E C I F I C A T I O N

BACKGROUND OF THE INVENTION

Pield Of The Invention This invention relates to surgical implants and more particularly, to 05 surgical procedures and appliances for intraarticular anterior and posterior ligament reconstruction .
Prior Art It is well known by anyone who has participated in athletics that the human knee is injury prone, particularly from lateral forces applied thereto. Where the knee joint is considered by most laymen to be essentially a hinged joint, in reality it provides a complicated mechanical movement that would be nearly impossible toduplicate with present technology. In operation, the human knee joint permits movement of flexion and extension in certain positions and even provides for a slight inward and outward rotation. Considering only movement of flexion and extension,the mechanical actions that take place in such movement include a certain amountof gliding and rotation along with the hinge action such that the same part of one articular surface of the distal femur or proximal tibia will not alwHys be applied to the same part of the other articular surface, and the axis of motion is not fixed.
In fact, if the knee joint is examined while in a condition of extreme flexion, the posterior part of the articular surfaces of the tibia will be found to be in oontact with the femur posterior around the extremities of the condyles. Whereas, if themovement was simple hinge like movement, the axis around which the revolving movement of the tibia would occur should be in the back part of ~he condyle. With the same leg brought forward into a position of semi-flexion, the upper surface of the tibia will seem to glide over the condyle of the femur, such that the middle part of the articular facets are in contact, and the axis of rotation is therefore shifted forward to near the center of the condyle. When the leg is brought into the extended position, still further gliding takes place as does a further shifting forward of the axis of rotation. Knee joint flexure and extension is therefore not a simple ~vP cnt but is accompanied by a certain amount of outward rotation around a vertical axis drawn through the center of the head of the tibia. This rotation is due ,~

- 1 3~6~

to the greater length of the inte. nal condyle, and to the fact that the anterior portion of its srticular surface is inclined obliquely outward. In consequence, towards the close of the movement of extension, just before complete extension, the tibia will glide obliquely upward and outward over the obl.que surface of the inner condyle, 05 and the leg will be necessarily rotated outwardJy. In flexation of the joint, the converse of these movements takes pluce, the tibia gliding backwardly around the end of the femur, at the commencement of which movement, the tibia is directed downward and inward along the oblique curve of the inner condyle, thus causing an inward rotation to the leg.
The above sets out a brief summary of knee joint functioning that takes place in knee flexure and extension. It is provided to show that this functioning is far more than a hinge movement and involves inward and outward rotation. It should be apparent therefore that in a repair of one or more ligaments of the knee, particularly in an intraarticular anterior and posterior ligament reconstruction that involves the cruciate ligaments, it is of significant value that the replacement ligaments, either a graft or prosthetic ligament, be fitted so as to, 8S nearly as possible, duplicate the positioning of the natural ligament. Heretofore, procedures and devices for use in repairing damaged ligaments, particularly the cruciate ligaments, have generally involved attaching the ligament device across the knee at the juncture of the distal femur and proximal tibia surfaces. Where sn attempt has been made to replace a cruciate ligament that involves securing the replacement ligament ends to the points on the opposing bone surfaces where that natural ligament was attached, such procedure has involved extensively opening the patient's knee area and/or forming intersecting tunnels through the respective tibia and femur ends and positioning a ligament therebetween. An example of such surgical technique and an implant device is shown in a patent by Hunt, et al., U.S. Putent No. 4,590,928. This p~tent is directed to an implant and kit therefore but does not, as does the present invention, provide an arrangement that is a near duplication for the patient's natural ligument. Rather, the Hunt, et al. patent is devoted to connectors and an implant that incorporates carbon fibers and, where tunnels are shown formed in the respective bones, such are apparently formed where access is convenient. As the tunnels are not aligned and each is open to without the femur and tibia surfaces, their formation involves extensive opening of the knee to provide access to the bone surfaces.

Unlike the Hunt, et. al. patent procedure, the present invention provides for ligament reconstruction using essentially an arthroscopic technique where a single incision only is made to the bone below the tibia tuberosity. From that point, a tunnel is formed into the bone that passes through the respective points of connection of a 05 cruciate ligament between the proximal tibia and distal femur and into the femur cortex. The femur cortex is then prepared to receive a ligament end coupling fitted therein to secure one ligament end.
Earlier ligament replaccment procedures have involved an extensive opening of the knee and have included forming passages or tunnels in the tibia and femur from the bone surfaces wherethrough are pulled a natural or artificial ligament, the ends of which ligament are bent and secured as with staples to the bone surfaces.
Unlike such earlier procedures and arrangements, the present invention provides for both fitting a ligament to extend across the knee so as to most nearly duplicatethe natural ligament positioning and provides for internal coupling the one ligament within a bone cortex. Additionally, the present invention provides a convenient I . g~ ~nt for adjusting the implanted ligament tensioning to most nearly duplicate a natural condition. The present invention therefore provides both a unique surgical a~r.ach and attachment devices to produce and implant that most nearly duplicates the patient's natural ligament arrangement than has heretofore been possible.
BRIEF SUMMARY OF THE INVENTION
It is therefore a primary object of the present invention to provide an arthroscopic system or technique for replacing with an allograft or prosthetic ligament a ruptured ligament of the knee, preferably a cruciate ligament.
It is another object of the present invention to provide an arthroscopic procedure that employs a single incision only that is made medial to the pstient's tibial tuberosity and at this point tunneling through the bone, across the distal femur and proximal tibia surfaces and into the femur cortex, the tunnel to pass through the points of connection of the ligament ends to the bone of either the anterior or posterior cruciate ligament.
3 0 It is another object of the present invention to provide for forming the tunnel to end in the femoral cortex just beyond the medullary channel and to prepare it to receive a connector that is turned or expanded therein so as to positively lock a ligament end within that bone cortex.

~4~ 1 336058 ;~ It is another object of the present invention to provide a procedure for tunneling through the patient's tibia across the proximal tibia and distal fem ur surfaces and into the femur cortex that involves opening the patient's knee at a single point or location only on the tibial tuberosity and for closely controlling the 05 tunnel formation process through a use of fluoroscopic and/or arthroscopic procedures to form a passage that is essentially straight and intersects the connection points of the ruptured cruciate ligament on the bone surfaces so as to receive an allograft or prosthetic ligament that is fixed on one end within the femur cortex and extends from the tunnel end at the tibial tuberosity.
Still another object of the present invention is to provide an end coupling for the prosthetic ligament to secure it at the tunnel entrance at the tibial tuberosity and adjusting the ligament tensioning, Still another object of the present invention is to provide a surgical procedure for replacing a torn or damaged cruciate ligament with an allograft or prosthetic ligament that requires minimal patient trauma and minimizes the time required for healing.
Still another object of the present invention is to provide an allograft or prosthetic ligament for replacement of a ruptured or damaged ligament that includes connectors made of a biodegradable material for maintaining the ligament 2 0 in place and will be absorbed by the body in the healing process.
In accordance with the above objects, the present invention is in an arthroscopic surgical procedure for installation of an allograft or prosthetic ligament as a replacement for a ruptured knee ligament, preferably either an anterior or posterior cruciate ligament. In a practicc of the procedure, a patient's lower leg is maintained in approximately a ninety degrec (90) angle to their upper leg and a longitudinal incision is made medial to the tibial tuberosity, which incision is made to the bone. At that incision, a stainless steel guidewire is driven in the anterior medial tibia at a point that is approximately two (2) centimeters distance to the medial tibial plateau. Guidewire insertion is conducted under fluoroscopic and arthroscopic control. The guidewire, after insertion, is thereby visualized as it is forced through the joint of the distal femur and proximal tibia, crossing the intercondylar notch area of the knee to engage the posterior and lateral femoral condyle. The preferred point of femur entry is deep within the intercondylar notch, ~5~ 1 3 3 6 ~ ~ ~
ss identified under fluoroscopic visualization, approximately four (4) millimeters anterior to the junction of the femur posterior cortex and the intercondylar seam as would be seen in a true lateral x-ray film of the distal femur. Guidewire travel is continued to pass through the femur cancellous bone, the medullary channel and 05 into the anterior lateral cortex so as to be just proximal to the metaphysical flare of the distal femur. So instaJled, the guidewire is then used to direct drill points of increasing drill sizes along its course, the drilling operation to sequentially increase the passage or tunnel diameter from the tunnel entry at the tibial tuberosity.
In the passage or tunnel formation the increasing size drills are stopped in the medullary channel. As a final step in the tunnel formation, the tunnel end is drilled beyond the medullary channel into the femur anterior cortex where theguidepin has been lodged. This final hole is made in preparation for turning either a tap therein forming threads or a flaring drill to widen that tunnel end. In one embodiment the ligament femoral end connection is a threaded component to be turned into the threaded tunnel end. In another embodiment the ligament femoral end connector is arranged to be exrpnrled or outwardly flared to fill the widened tunnel end.
After tunnel formation, the ligament is inserted to where its end is secured in the femur cortex as by either turning or expanding the connector end therein. The ligament thereby extends from its cortex end to where it exits the tunnel at the tunnel point of entry on the tibial tuberosity. Where the ligament is an allograft, the ligament end can be bent at the tunnel end ucross the bone andstapled thereto. Where the ligament is a prosthetic ligament, a preferred end coupling involves forming threads in the ligament end to receive a flat disk that is 2 5 center tapped and slopes outwardly from one face to the other around the circumference, the small diameter face to nest in the tunnel end. This connectorarrangement provides a capability for ligament length adjustment to achieve a desired ligament tensioning. In both embodiments, the respective connectors can be formed of a biodegradable material, such as a polylactic acid that will be absorbed by the body during the healing process, the bone growing to either the prosthetic or allograft ligaments.

- -6- ~ 336058 Utilization of the above-described ligament and preferred connector installing procedure provides for ligament positioning to most neurly duplicste a damsged ligsment snd for setting a desired tensile stress in the ligament.
DESCRIPTION OF THE DRAWINGS
05In the drawings thst illustrste thst which is presently regarded as the best mode for carrying out the invention:
Fig. 1 shows a pstient's leg with their lower leg muintained at spproximately a ninety (90) angle to the upper leg, which positioning is to be maintained throughout a surgicsl procedure of the present invention;
10Fig. 2 is an enlarged side elevation view exposing the proximal tibia and distsl femur ends of the leg of Fig. 1, which distsl femur is shown as hsving hsd a section removed to the bone cortex, exposing a tunnel formed therein tllat contains one embodiment of a prosthetic ligament and end connectors therefore of the present invention;
15Fig. 3 is a front elevation view of the distal femur and proximal tibis ends of Fig. 2 showing a portion of the femur cortex removed exposing the tunnelwith the prosthetic ligsment end secured therein;
Fig. 4 shows sn enlsrged side elevstion view of the prosthetic ligsment of Figs. 2 and 3 removed from the pstient's knee, and shows the ligsment femorsl2 0and tibisl sttschment ends ~s they sppesr before instsllstion;
Fig. SA is an enlsrged end view of the femoral sttschment end of the prosthetic ligsment of Fig. 4;
Pig. SB is a view like Fig. 5A except that it shows the femoral attschment end having been eyppn~led to the flared configuration shown in Figs. 2 and 3;
25Fig. 6 shows another embodiment of a prosthetic ligsment that incorporstes a deep thresded end ss the femoral attschment end and includes the thresded tibisl sttschment end thst is like thst shown in Figs. 2 through 4;
Fig. 7 is a side elevstion view of a distal femur showing a section removed so as to expose the bone cortex and shows the ligament femoral attachment end of3 0Fig. 6 turned into a tapped tunncl end;
Fig. 8 shows a profilc perspective view of a thrended cylindrical sllogrsft ligsment end connector that is for turning into a tapped tunnel end in the femur cortex;

~7~ 1 3 3 6 0 5 8 Fig. 9 shows a sectionsl view taken along lines 9-9 of the end connector of Fig. 8;
Fig. 10 shows the end connector of Fig. 9 being sewn onto the end of an allograft ligament and shows a hex-sided driver fitted into a like sided longitudinal 05 hole in that end connector with the allograft ligament wrapped therearound; and Fig. 11 shows a front elevation view of a femur that has a tunnel formed into the bone cortex, showing a section of the bone removed to expose the end connector of Figs. 8 through 10 turned therein.
DETAILED DESCRIPTION
The present invention is in a surgical process or system whereby, from a single incision only made in a patient to their tibial tuberosity, a straight psssage or tunnel is formed that will cross the proximal and distal femur surfaces and extend into the femur cortex. The tunnel is for receiving a ligament, either allograft or prosthetic, that is secured therein by one of several ligament end attachment embodiments of the invention. The process is primarily directed to but should beunderstood is not limited to replacement of a patient's damaged anterior or external cruciate ligament. The present procedure is described herein with respect to a replacement of the anterior cruciate ligament that is the ligament that is attached on its one end to the depression in front of the spine of the tibia and is part of the external semi-lunar fibro-cartilage and is arranged to pass obliquely upwardly as well as backwardly and outwardly therefrom. The other ligament end is joined onto the inner and back part of the femur outer condyle. The anterior cruciate ligament, during leg rotation, is in a semi-flexed condition, and opposes inward rotation. It is this ligament that, in athletic play where the knee is subjected to an inward force, such as football, is most often damaged. Heretofore, repair of the anterior cruciate ligament has involved an extensive surgical opening of the knee along with a release of the outer ligaments and cartilage that surround the tibia to effectively lay open the knee. Whereafter, the ruptured ligament has been repaired, if possible, or replaced with an allograft or prosthetic ligament. Where replacement is in order, the procedure has involved tunneling through the femur and tibia, the tunnel exiting both bone surfaces, and a stapling of the ligament ends to the bone surfaces. Such procedure has required that the patient's leg be immobilized for an extended period of time to allow for healing, and, generally a full restoration of the patient's knee has not been obtained. Even in the best of circumstance, after a long restorative or healing period, extensive physical therapy is necessary torestore the knee to proper functioning. Unique to such former procedures, the present invention provides a reconstructive procedure for arthroscopic insertion of 05 either an allograft or prosthetic ligsment thst involves a single small incision only and provides, with a successful completion of the procedure, a ligsment thst is essentislly resdy for use.
Fig. 1 shows that in a prsctice of the arthroscopic procedure of the present invention for replscement of the anterior cruciste ligsment, the pstient's leg 10 is prefersbly msintsined st spproximstely a ninety degree (90) angle between the femur snd tibis. With the leg 10 so msintsined, a longitudinsl incision of approximately five (5) centimeters is msde in the lower leg just below the externsl semi-lunar fibro-cartilsge to open the skin to the tibial tuberosity. At this exposed bone section, the end of a stainless steel guidewire, not shown, is positioned on a point of the tibial tuberosity that is approximately two (2) centimeters distal to the medial tibial plateau. The guidewire is then urged into thst bone mass st thst point by an spplicstion of a force thereto ss by hsmmering the opposite guidewire end, or the like. This insertion process is made under fluoroscopic control to sllow a surgeon to follow the guidewire progress through the bone so as to ensure that it will exit a point on the proximal tibia surface where the anterior crucisl ligsment is connected to the tibia and is blended with the semi-lunar fibro-cartilsge. This point will be approximately two (2) centimeters posterior to the most anterior border of the tibisl plateau. Guidewire travel to verify its positioning as it enters the joint afterpiercing the tibisl connection of the snterior cruciste ligsment csn slso be visuslized arthroscopically through an opening made in the knee cap area.
Guidewire travel can thereby be observed both arthroscopically snd fluoroscopically, insuring that it trsvels across the intercondylar notch area of the knee to engage the posterior and lateral femorsl condyle st a point that is deepwithin the notch. This point is spproximstely where the opposite end of the anterior crucisl ligsment sttaches to the femur at the intercondylar notch area. It is generally located approximstely four (4) millimeters snterior to the junction of the femur posterior cortex and the intercondylar seam as would be seen in a true lateral x-ray film of the distal femur. During this procedure, as set out above and shown in Fig. 1, the knee is maintained or fixed in a ninety degree (90) position to ensure that the formed passage will be essentially straight and that points of engagement of the guidewire with the ends of the anterior crucial ligament will be optimal.After verifying that the guidewire pointed end is properly located on the 05 junction of the femur posterior cortex and the intercondylar seam, it is further forced into the bone mass. The guidewire is driven through the cancellous bone that surrounds the medullary channel to pQSS through that medullary channel and into the femur anterior lateral cortex to a point that is just proximal to the metaphysical flare. Guidewire positioning is again verified radiologically and is there~fter utilized to guide drill points of increasing sizes along the guidewire course.
Such drilling begins at the entry point on the anterior medial tibia and terminates at the femur medullary channel before the anterior lateral cortex. The drill points that are selected for forming the tunnel to receive a prosthetic ligament preferably begin at five sixteenths of an inch (5/16") and are progressively increased in size by one sixteenth of an inch (1/16") increments to approximately seven sixteenths of an inch (7/16") in diameter. In practice, it is preferred that the tunnel is not drilled beyond the femur medullary chQnnel so QS not to dislodge the guidewire end lodged in the anterior cortex. For forming a tunnel to receive an allograft ligament, the above described procedure is employed, except that the preferred drill sizes begin at six (6) millimeters and progress to eight (8) millimeters as the tunnel is enlarged.
After the required diameter of hole or tunnel is formed that is suitable for the selected ligament, a final drilling step is the insertion of a one quarter of an inch (1/4") canulated drill into the tunnel to pierce the anterior lateral cortex of the femur. This step is in preparation for fitting a tap or flaring drill into that cortex. With this drilling step the guidewire is released and can be removed. The tunnel end in the femur anterior lateral cortex is then ready to be prepared to receive a femoral attachment end of either an allograft or prosthetic ligament to be secured therein. For Q threaded end coupling the anterior lateral cortex willpreferably be tapped to approximately Q three eights of an inch t3/8") diameter.While, for a skirted end coupling QS will be described later herein, the tunnel end receives a flaring drill turned therein.

With the tibi~ msintsined st 8 ninety degree (90) angle to the femur, Pigs. 2 Qnd 3 show tunnel 11 formed between the distal femur snd proximsl tibis ends and show 8 section of the femur removed therefrom. The Figs. illustrate thepositioning of the respective bone ends snd show 8 prosthesis ligsment secured 05 therein. Tunnel lI exits the proximsl tibis st e point 14 that is spproximately two (2) centimeters posterior to the most anterior border of th~t tibisl plstesu 13 snd is approximstely the connection point of the end of the snterior cruciste ligament to the bone surfsce. The intercondylar notch sres, shown at lS in Fig. 3, is thepoint of entry of tunnel 11 into the distsl femur, the tunnel passing between the posterior nd luter~l femorsl condyles 16 snd 17. The preferred tunnel entry point is on the distal femur is determined radiologicslly and should be sppropristely four (~) miilimeters snterior of the juncture of the femur posterior cortex 18 snd the intercondyl_r ~e_m 19. From this point of entry the tunnel 11 pQsses through thecsncetlous bone 20 and through the medullsry channel 21, ss shown in broken lines, snd terminstes in the anterior latersl cortex 22.
prsctice of the sbove set out procedure therefore will produce 8 tunnel ~uitsble for receiving 8 ligament to replace the anterior cruciste ligsment ss shown in Figs. 2, 3, 7, and 11, with the tunnel end thst terminstes in the cortex to receive ligsment end connector secured therein, 8S will be discussed in detail hereinbelow.
It ~hould, ' ue~er, be understood thst, with sppropriste chsnges to the tunnel point ot entry and angle of trsvel therethrough lt csn be formed to psss through the unctions of Ihe posterior cruciste ligsment with the respective bone surfsces within the scope of this diC~ los~e.
Figs. 2 and 3 illustrste a first embodiment of sn expandsble cone 26 ss a femorsl sttschment end for a prosthetic ligsmcnt 25. The expsndable cone 26 iscylindricsl in shspe snd prefersbly includes longitudinsl slots 27 formed st spsced intervsls theresround. So srrsnged, the cone end csn be expsnded to the sttitudeshown in Pigs. 2 snd 3 when sn e~pancion snchor 33 is pulled therein, the cone end bresl~ing st longitudinsl slots 27 to form 8 skirt. To sccommodste the cone 26 th~t hss been flsred into 8 skirt, ss shown slso in Fig. SB, thc femorsl end of tunnel Il must also be outwsrdly fl_red 8t its most dist~nt point. From the flsred portion, the tunnel to tsper 8 lesser rsdius or circumference that is essentially the ligsment rsdius. Por forming such outwardly flsred tunnel end portion, a su~table dr;ll is preferred. Such drill inclubes scissoring blades that, at a certain depth of ~ L~Lion of the drill en~ relative to a guide sleeve thereof, will pivot apart. With the .c~i~cnring hl~
05 flaring cutwardly, the drill will then cut an inverted skirt shaped hole at the tunnel end to ~rcnm~f~te the prosthetic ~ m~nt expandable cone 26 after it has keen n ared cutwardly therein, ~hile a drill like that descriked is preferred, it should be un~erstood that okher drill arrangements for forming an inverted ~kirt or like enlarged fe ral end of turne~ 11 can be 1o so used within the soope of this disclo6ure.
Figs. 2, 3, ~nd 4 show the prosthetic ligsment 25, shown to be prefersbly formed from a brsided fabric and includes ss the femorsl sttschment end, the expandable cone 26. The e~g- dr'le cone 26 is prefersbly attsched to the prosthetic ligsmcnt 25 in the msnufscturine process. The opposite end of ligament 25 is shown threaded therealong at 29 for receiving, as a tibisl attachment end, 8 flattened cone 30. FJsttened cone 30 is holed and thresded longitudinslly therethrough to be turned over the threaded prosthetic ligsment tibial end 29. The flsttened cone outer circumference is shown to tsper outwardly from the edge of one face to the edge of the other f-ce with the lesser diameter cone fsce to wedge in tunnel 11 open end. To provide for e~p~ ng cone 26, ss shown best in Fig. 4, the prosthetic ligament 25 includes a bngitudinal passage thst is open therethrough and receives n inner shaft 31 telescoped to slide therein. The inner shsft 31, ss illustrsted best in Figs. SA and SB, includes a thresded end 32 thst is for turning }nto 8 thresded centraJ opening in s flst face of an expansion snchor 33. The e~pansion anchor 33 is shown to hsve, opposite to the flst fsce, a cylindrical nose snd is flsred or tapered outwsrdly back from the nose end into 8 cylindrical center section 34. Bsck therefrom the anchor tapers inwsrdly from an end edge 35 into a ssddle 36 snd then flares outwsrdly from 37 to terminate in a rear edge 38. The anchor resr edge 38 is aligned with the expanding cone 26 open end to trsvel therein. The cone 26 is tapered inwardly from a widest point at its open end, the opening therethrough reducing in dismeter, as illustrated in broken lines at 26a in Figs. SA snd 5B to a continuous groove 39 formed sround the cone inner circumference ~t spproximstely the closed ends 278 of longitudinsl slots 27. As shown best in Fig. SB, pulling the -12- l 336~58 ~Yp~n~;on anchor 33 into the expandable cone 26 causes that cone end to expand outwardly, flaring the cone at longitudinal slot ends 27a. With continued travel of the expansion anchor therein the anchor rear edge 38 will engage and seat in groove 39 having flsred the cone 26, as shown in broken lines in Fig SB, locking the 05 expansion anchor therein. Shaft 31 travel to so move expansion anchor 33 into the eYp~n~' hle cone 26 is shown by the arrow 8 in Fig. SB. So arranged, travel of the anchor within the expandable cone 26 causes it to break at the slot 27 end 27a flaring the cone end outwardly into a flattened cone. The ~oxp~qn~l~hle cone 26 is thereby erected to have to its greatest diameter at its rearmost point the tunnel 11, that cone flared portion filling the tunnel end and permanently seating therein.
This coupling has been found in pull-out tests performed thereon to resist separation at forces in excess of 1300 neutrons that is estimated to be a maximum force as could reasonably be expected to be exerted on the ligament.
Fig. 6 shows another embodiment of a prosthetic ligament 40 that includes, as a femoral attachment end, deep threads 41 that are formed in the ligament femoral end. These threads are preferabJy formed during the fabrication thereof as are smaller machine threads 42 that are formed in the ligament tibial attachmentend. Threads 41, as illustrated, are preferably cut deep and wide to bite deeplyinto the tunnel femoral anterior cortex end, which threads are cut or formed therein, as set out hereinabove, as a last step in the tunnel formation process. As with the description of prosthetic ligament 25, the machine threads 42 that are formed asthe tibial attachment end are to receive a flattened cone 43 turned thereover. In the prosthetic ligament 25 and 40 embodiments the tibia attachment component is preferably the flattened cone shaped collar that is longitudinally center threaded therethrough for turning over the threaded prosthetic ligament thre0ded end suchthat the cone lesser diameter end will travel into the tibia tunnel 11 end. Flattened cone 43 turning is preferably accomplished by fitting a tool, not shown, into a hole or holes 43a that extend through the cone to the greater diameter face thereof, and turning the collar with that tool. This arrangement provides for adjusting 3 0 ligament tension by appropriately turning the collar on the ligament to engage the tibia tunnel end.

As set out hereinabove, the tunnel 11 femoral end, sfter it has been tapped or otherwise machined to form threads therein, sccommodates the threaded end 41 of prosthetic ligament 40 turned therein. This tapping or threading can be nc.~, Fliched by insertion of the canulated drill into the femur anterior lateral cortex 05 end of tunnel 11, as described hereinabove, followed by a tap turned therein. Such tap is inserted along the prepared tunnel 11 and is turned to tap that femur anterior cortex at 44, as illustrated in Fig. 7. Whereafter, the prosthetic ligament 40 of Fig.
6 is turned into the tunnel end 44, as illustrated in Fig. 7, to where the ligament end butts sgainst the tunnel end, locking the ligament therein. Thereafter, prosthetic ligament length and tension adjustment is accomplished, as set out above, by turning the flattened cone 43 on the prosthetic ligament thread end 41, to where it engages the tibia end of tunnel 11. Setting prosthetic ligament tension is preferably accomplished while maintaining the patient's leg 10 in the attitude shown in Fig. 1.
Fig. 10 shows a threaded cylinder 50 that is a preferred configuration of 1 5 a femoral attachment for an allograft ligament 49 for securing a ligament end in the femoral anterior cortex end of tunnel 11. Cylinder 50 is shown to have the appearance of a set screw, in that it is threaded at 51 along its entire length, as shown in Figs. 8 and 9, and includes a center hex-sided cavity 53. Additionally,the cylinder 50 preferably includes longitudinal holes sa that are radially formed therethrough around the center hex-sided cavity 53. The cavity 53 is formed in aligament attaching end of cylinder 50 that is preferably dished below a circumferential lip 54. The cylinder 50 is preferably fabricated of a biodegradable material such as a polylactic acid plastic or like material, to be absorbed by the body in the healing process. Fig. 10 shows an end of allogrHft ligament 49 being attached to cylinder 50 by passing a suture 56 at spaced intervals around the ligament end, which suture is also selectively threaded through longitudinal passages 52 using a needle 57. The ligament end is then drawn tightly against the cylinder 50 dished out portion, fitting below the circumferential lip 54. Shown in Figs. 10 and lOA, for installation, the allograft ligament is unrolled and is wrapped around a hex-sided driver 58, which driver should be long enough to be turned from without the tunnel 11. The allograft ligament has an overlapping layered appearance, as shown in the sectional view of Fig. 10A. To install the hex-sided driver 58 the allograft ligament is unwrapped so as to loosen it at the center wherethrough the hex-sided driver is fitted. The ligament and driver are then fitted into tunnel 11 and the cylinder 50 threads 51 are turned into a tapped femur end 60 of tunnel 11. After seating of the cylinder, the hex-sided driver 58 is removed and the allograft ligament 49 stretched out, as illustrated in Fig. 11. The cylinder threads 51, are preferably machine type threads, 05 as shown in Figs. 8 through 11, and therefore thread 51 depth is not as great as is the depth of threads 41 of the prosthetic ligament 40 of Fig. 6. It should, however, be understood that the threaded femoral attachment end of both the prosthetic ligament 40 and cylinder 50 can have the same or different depth of thread within the scope of this disclosure.
With cylinder 50 seated as described and the allograft ligament 49 stretched therefrom, to complete the ligament rcconstruction, the allograft ligament 49 is pulled tight so as to achieve a certain tensile loading thereon. The ligament tibial end is then secured to the tibia as by bending the ligament 49 tibial endacross the bone surface from the tunnel 11 entry and is fixed thereat as by driving staples into the bone that span the ligament. Of course, a tibial attachment device such as a collar arrangement, that could be pinched around the ligament, not shown, or the like, can be used for attaching the allograft ligament tibial end to the tibia within the scope of this disclosure.
The above sets out the preferred end connector arrangements and system 2 0 for their use for ligament reconstructive surgery as particularly applicable to a replacement of the anterior cruciate ligament with a prosthetic or allograft ligament.
It should, however, be understood that the described procedures is and/or the devices described herein can be appropriately modified to be used to surgically replace the posterior cruciate ligament and/or other knee ligaments, within the scope of this disclosure. It should also be understood that any or all of the described ligament end connectors can be fabricated from a material or materials such as a polylactic acid plastic, or the like, to be absorbed by the body during the healing process.
Obviously, however, the described connectors can be manufactured from an appropriate metal to remain in the bone after the healing process has taken place.
The present disclosure has, of course, been directed to both prosthetic and allograft ligaments. Within present technology, a prosthetic ligament msnufactured by Zimmer U.S.A. is believed to be suitable for the described application.
Approval for this ligament for use as an implant is currently being sought from the Food and Drug Administration for human implant. It should, however, be understood that the present invention is not Jimited to use with such particulflr prosthetic ligsment only snd that the end connection devices set out herein can be used with other prosthetic ligaments ss may be now available or ss may be developed in the 05 future within the scope of this disclosure. Of course, allograft ligaments from csdavers are presently available for human implant.
The above described configurations of sn allograft femoral device, shown as cylinder 50 in Figs. 8 through 11, has been laboratory tested ss set out in Table I hereinbelow. Table I shows the pull out strength of the femoral attachment component, the cylinder 50 that incorporates three (3) sutures 56 each threaded through snd back through psssages 52, securing the ligament end to the cylinder end. Each suture was capable of sustaining a twenty (20) pound tensile load. The test standsrd thereby being that the attachment device, cylinder 50 snd its suture connection would sustain at least a pul~out tensile stress of sixty (60) pounds. The test data in Table I shows that this criterior was met, the minimum sustained load shown ss sixty seven (67) pounds. Additionally, it should be noted that all tests were performed using bones thAt csme from specimens that were older than sixty (60) years st the time of death. The advanced age of the bone specimens used, it can be sssumed, incresses the chances that the bones will be softer snd more porous, 2 0 grestly reducing the bone strength. Tests performed on younger bones, it csn reasonsbly be assumed, would likely show grester failure strengths. Even using the aged spe~h -, the tests demonstrated the utility of the connector as the minimum bsd sustained of siKty seven (67) pounds was still greater thsn the combined suture strength of sixty (60) pounds, with the other tests for the different thread configurations showing much greater failure strength.

-16- I 33605~

TABLE I
SPECIMEN SPECIFICATIONS

M ateriaJ Threads Test Note Thread'M ajorM inor Per Load Number Date Length DjA. Dia. Inch tLbs.) 7-ag-86 .702 .374 .236 9 267 2 7-29-86 .702 .374 .236 9 129 3 7-29-86 .702 .374 .236 9 165 4 8-07-86 1.134 .373 .236 9 169 8-07-86 .594 .374 .236 9 133 6 9-04-86 .750 .328 .236 12 115 7 9-04-86 .750 .328 .236 12 67 8 9-04-86 .750 .328 .236 12 85 9 9-04-86 .750 .328 .236 12 142 14 9-12-86 .750 .375 .280 18 120 9-12-86 .750 .375 .280 18 220 16 9-12-86 .750 .375 .280 18 520 17 9-12-86 .750 .375 .280 18 120 NOTE: MATERIAL TEST NOTE NUM13ER 10-13 INVOLVE TIBIAL
ATTACHMENT DEVICES AND DO NOT APPLY.

Herein has been set out a preferred surgical procedure or system and ligament end attschment devices. It should, however, be understood that the present disclosure is made by way of example only and that variations to the procedure or system and the described ligament end connectors are possible without departing 05 from the subject matter coming within the scope of the following claims, which claims we regard as our invention.

Claims

1. Apparatus for use in a surgical system for implanting a human knee joint ligament, particularly an anterior ligament, under fluoroscopic control, from a single incision to the tibial tuberosity a straight ligament tunnel of a diameter to accom-modate a selected allograft or prosthetic ligament of a certain cross section, is formed to a point within said femur cortex;
comprising, an allograft or prosthetic ligament; a femoral attachment connector secured to one ligament end that is arranged for insertion into the straight ligament tunnel to a point within the femoral tunnel portion; means for outwardly extending a component or components of said femoral attachment connector into the femur endosteum for permanent installation of said femoral attachment connected and connected ligament end endosteally in said femur endosteum; and securing a tibial end of said ligament in tension at the open tibia end of said straight ligament tunnel.

2. Apparatus for use in a surgical system as recited in Claim 1, wherein the tibial incision is made medial to the tibia tuberosity down to a point on the bone surface hat is ap-proximately two (2) centimeters distant from the medial tibial plateau with the tunnel into the tibia passing through the joint to the intercondylar notch at a point within said intercondylar notch that is approximately four (4) millimeters anterior to the junction to the femur posterior cortex and the intercondylar seam through the medullary channel and into the femur endosteum wherein a flaring drill means is turned to form an open inverted cone shaped section.

3. Apparatus for use in a surgical system as recited in Claim 2, wherein the ligament femoral attachment connector is an expansion cone formed as an open cylinder having a proximal end connected to an end of a prosthetic ligament that includes an open center longitudinal passage therethrough, which expansion cone is longitudinally slotted at spaced apart intervals around its distal end from said prosthetic ligament and includes a continuous groove formed around he cylinder inner circumference;

and an arrangement for expanding said expansion cone into a skirt at its longitudinally slotted end to conform to the inverted cone shape section formed at the ligament femur cortex end.

4. Apparatus for use in a surgical system as recited in Claim 3, wherein the arrangement for expanding the expansion cone consists of a cylindrical expansion anchor that is center holed on one end and receives an end of a rod that is releasably secured therein so as to be capable of breaking away when a certain pulling force is exerted thereon, which rod is tele-scoped through said prosthetic ligament open center longitudinal passage, the opposite rod end extending beyond said prosthetic ligament end for receiving a pulling force thereon to move said expansion anchor into said expansion cone so as to flare said expansion cone outwardly into a skirt at said longitudinal slots, a circumferential edge formed around said expansion anchor to travel into the continuous groove of the inner circumference of the expansion cone, locking therein.

5. Apparatus for use in a surgical system as recited in Claim 4, wherein the expansion anchor tapers inwardly from a central ring to a lesser diameter section and then outwardly to the end wherein the expansion anchor is center holed forming a circumferential edge that is the same diameter as the expansion anchor center portion; and the expansion anchor center hole is tapped to receive a threaded end of the rod, which rod and expansion anchor center hole threads are such as to disengage when a certain tension stress is applied therebetween.

6. Apparatus for use in a surgical system as recited in Claim 2, wherein, to provide for securing the prosthetic ligament tibial attachment end to the tibia, a flattened cone shaped disk is provided having a lesser diameter end wherefrom the cone shaped disk outer surface slopes uniformly outwardly to a greater diameter end, which lesser diameter end is for alignment with and installation in the tibia end of he ligament tunnel, the cone shaped disk having a center opening there-through that is tapped to be turned over a threaded tibial end of said prosthetic ligament, turning of which cone shaped disk on said prothetic ligament threaded end to move said lesser diameter cone shaped disk end into engagement with the bone around said ligament tunnel tibial end for setting prosthetic ligament tensioning.

7. Apparatus for use in a surgical system as recited in Claim 1, wherein the ligament tunnel closed end with the femur is tapped to form threads in the surrounding bone.

8. Apparatus for use in a surgical system as recited in Claim 7, wherein, for a prosthetic ligament, the ligament femoral attachment connector includes thread means formed on the prosthetic ligament femur end for turning into the threads formed in the ligament tunnel end.

9. Apparatus for use in a surgical system as recited in Claim 7, further including, for securing the prosthetic ligament tibial attachment end to the tibial end of the ligament tunnel, a flattened cone shaped disk having a lesser diameter end wherefrom the cone shaped disk slopes uniformly outwardly to a greater diameter end, which lesser diameter end is for align-ment with and installation in the tibia end of the ligament tunnel, the cone shaped disk having a center opening there-through that is tapped to be turned over a threaded tibial end of said prosthetic ligament, turning of which cone shaped disk on said prosthetic ligament to move said lesser diameter cone shaped disk end into engagement with the bone around said ligament tunnel tibial end for setting prosthetic ligament tensioning.

10. Apparatus for use in a surgical system as recited in Claim 7, wherein, for an allograft ligament, the femur attach-ment connector is a cylinder that includes threads formed along the length of its outer circumference, which threads are for turning into the threads formed in he femur end of the ligament tunnel, which femur attachment connector is holed longitudinally from end to end at radial spaced apart intervals o accommodate a suture that is threaded therethrough and through spaced points at the end of the allograft ligament, the cylinder further including a center longitudinal sided driver hole formed in one end hereof; and a tool that is sided to fit within the cylinder center longitudinal sided driver hole, wherearound the allograft ligament is arranged for turning said cylinder into the threaded femur end of the ligament tunnel, the tool opposite end to extend out from the tibia end of said ligament tunnel for turning.

11. Apparatus for use in a surgical system as recited in Claim 11, wherein the one end of the femur attachment connector is dished inwardly at the allograft ligament connection end, a circumferential lip extending from the cylinder end above that dished out portion to accommodate the end of said allograft ligament drawn therepast, against the dished surface of the cylinder, by tightening the sutures that have been passed at intervals through the allograft ligament end and threaded through the cylinder radial longitudinal holes.

12. Apparatus for use in a surgical system as recited in Claim 11, wherein the center longitudinal hole is hexagonally sided to accommodate, as the tool, a straight hexagonally sided shaft for sliding into said cylinder center longitudinal hole and accommodating the allograft ligament arranged therearound.

13. Apparatus for use in a surgical system as recited in Claim 1, wherein the respective femur cortex and tibial attach-ment connectors of the prosthetic and allograft ligaments are formed of a biodegradable material for absorption by the body.

14. Apparatus for use in a surgical system as recited in Claim 13, wherein the biodegradable material is polylactic acid.

15. Apparatus for use in a surgical system for a pros-thetic ligament implant as a replacement for knee ligament, particularly a cruciate ligament, for installation in a ligament tunnel formed to have a closed end in either the femoral or tibial cortex, said ligament tunnel extending across the knee joint and is open at the distal bone surface form the ligament tunnel closed end, which ligament tunnel closed end is prepared to receive and connect in binding engagement to an end of a prosthetic ligament; comprising, a prosthetic ligament; a femoral attachment connector and means secured to one end of said prosthetic ligament means for permanently securing said femoral attachment connector end means in the prepared ligament tunnel cortex end; and a tibial attachment connector means that is secured to said prosthetic ligament other end for maintaining and adjusting the prosthetic ligament tensioning at the ligament tunnel entrance.

16. Apparatus for use in a surgical system for a pros-thetic ligament implant as recited in Claim 15, wherein the ligament tunnel closed end is formed to have an open inverted cone shaped section and the femoral attachment connector means is an expansion cone that is formed as an open cylinder that is longitudinally open therethrough and has a proximal end that is secured to an end of the prosthetic ligament, which prosthetic ligament includes an open center longitudinal passage there-through, and he expansion cone is longitudinally slotted at spaced apart intervals around its distal end from its coupling to said prosthetic ligament end; as the means for permanently securing said femoral attachment connector a continuous groove is formed around the open cylinder inner circumference, at approximately the center thereof; and means for expanding said expansion cone into a skirt at its longitudinally slotted end.

17. Apparatus for use in a surgical system as recited in Claim 16, wherein the means for expanding the expansion cone consists of an expansion anchor means that is cylindrical in shape and is center holed on one end to receive an end of a releasably secured rod, which coupling is capable of breaking apart when a certain pulling ;force is exerted thereon, and which rod is telescoped in sliding arrangement through said prosthetic ligament open center longitudinal passage, the opposite rod and extending beyond said prosthetic ligament end;
and said expansion anchor means is fitted to travel on he end of said rod into said expansion cone, where a circumferential edge of said expansion anchor means will travel into the continuous groove that is formed around the inner circumference of said expansion cone to flare said expansion cone outwardly into a skirt at said longitudinal slots, locking therein.

18. Apparatus for use in a surgical system as recited in Claim 17, wherein the expansion anchor tapers inwardly from a central ring to a lesser diameter section and then outwardly to the end wherein the expansion anchor is centered holed forming a circumferential edge that is the same diameter as the expansion anchor center portion; and the expansion anchor center hole is tapped to receive a threaded end of the rod, which rod and expansion anchor center hole threads are such as to disengage when a certain tension stress is applied therebetween.

19. Apparatus for use in a surgical system for a pros-thetic ligament implant as recited in Claim 15, wherein the ligament tunnel closed end is tapped to form threads in the surrounding bone and the end means of the prosthetic ligament for permanent attachment in that ligament tunnel closed end includes thread means formed therearound for turning into the threads formed in said closed end of the ligament tunnel.

20. Apparatus for use in a surgical system for a pros-thetic ligament as recited in Claim 15, wherein the respective prosthetic ligament attachment connector means are formed of a biodegradable material for absorption by the body.

21. Apparatus for use in a surgical system for a pros-thetic ligament as recited in Claim 20, wherein the biodegrad-able material is polylactic acid.

22. Apparatus for use in a surgical system for installing an allograft ligament implant as a replacement for a knee ligament, particularly a cruciate ligament, for installation in a straight ligament tunnel formed to have a closed end in either he femoral or tibial cortex, which ligament tunnel extends across the knee joint and is open at the distal bone surface form the ligament tunnel closed end, the ligament tunnel closed end to be tapped to form threads in the surrounding bone;
comprising, an allograft ligament; an allograft ligament connector, that is a cylinder that has threads formed around the length of its outer circumference, which threads are for turning into the threads formed in the threaded closed end of he ligament tunnel, which cylinder is holed longitudinally from end to end at radial spaced apart intervals to accommodate a suture that is threaded therethrough and through spaced points at the end of the allograft ligament, said cylinder further including a center longitudinal sided driver hole formed in one end thereof;
sided tool means appropriate for removable fitting into said center longitudinal sided driver hole for turning said cylinder into said ligament tunnel threaded end; and the unattached allograft ligament end is bent into engagement with the bone at

23 said ligament tunnel open end to receive connector means for securing said ligament end to said bone surface.
23. Apparatus for use in a surgical system for installing an allograft ligament as recited in Claim 22, wherein the one end of the allograft ligament connector is dished inwardly and includes a circumferential lip that extends above said dished portion to accommodate the end of said allograft ligament drawn therein by tightening the sutures that have been passed there-through and through the cylinder radial longitudinal holes.

24. Apparatus for use in a surgical system as recited in Claim 22, wherein the cylinder center longitudinal hole is hexagonally sided to accommodate, as the tool means, a straight hexagonally sided shaft for sliding into said cylinder center longitudinal hole and accommodating the allograft ligament arranged therearound.

25. Apparatus for use in a surgical system as recited in Claim 22, wherein the allograft ligament connector is formed of a biodegradable material for absorption by the body.

26. Apparatus for use in a surgical system as recited in Claim 24, wherein the biodegradable material is polylactic acid.