this detailed description will again use the femoral side of an acl reconstruction as an example of the multiple uses of this new concept ; however , as noted above , this application is intended to be merely exemplary and the invention may be used on the tibial side of an acl reconstruction , or in connection with some other type of ligament reconstruction , etc . using this new approach , the initial steps in the acl reconstruction are unchanged from that usually done when using interference screws for graft fixation . autografts or allografts , with or without attached bone blocks , can be utilized . arthroscopic examination of the knee is done in the standard fashion , with debridement of the residual anterior cruciate ligament tissue and preparation of the femoral notch . the tendon graft is harvested , prepared , and measured . the bone tunnels are made in the tibia and femur in the standard fashion , typically using one of the commercially available guidance systems . as always , care should be taken with tunnel and tendon preparation , optimizing tunnel location and size , and utilizing appropriate tendon suturing methods . the graft ligament is then inserted into the bone tunnels . see fig1 , which shows the tendon graft inserted into the bone tunnel formed in the bottom of the femur and extending back into the interior of the knee joint . the present invention diverges from the standard practice once the tendon has been passed into the bone tunnels . a significant aspect of the present invention is ( i ) the creation of a small , preferably wedge - shaped , layer of bone between the tendon and the wall of the host bone , and then ( ii ) the compression of this layer of bone against the tendon using an interference compression device set outside , and bearing against , the intervening layer of bone . the layer of bone is incompletely broken away from its native position , hinging downwards while maintaining some of the bone - to - bone apposition on its edges . with this new method , nearly the entire tendon graft is compressed by native , cancellous bone . all of the benefits of interference fixation are retained , such as exclusion of synovial fluid from the bone tunnel ; at the same time , the area of contact between the graft and the host bone is increased . as described here , the creation of the intervening bone layer can have a positive impact on the effectiveness of the ligament reconstruction procedure . therefore , the nature and use of the osteotome used to create the bone layer can obviously have a significant impact on the successful execution of this procedure . to this end , a unique osteotome specific for this system will now be described , although the use of other designs and methods may also be utilized to practice the present invention . one possible osteotome system comprises a guide 100 ( fig2 , 3 a and 3 b ) and an osteotome 200 ( fig4 and 5 ). guide 100 is used to establish the path that is to be followed by osteotome 200 , and osteotome 200 is then used to create the bone layer ( preferably wedge - shaped ) that is displaced by the interference screw so as to fix the graft ligament to the host bone . the present invention may also be practiced without the guide 100 , or without the osteotome 200 , or without both ; however , it is believed that the use of guide 100 and osteotome 200 facilitate practicing of the present invention . more particularly , and looking now at fig2 and 3 , guide instrument 100 preferably comprises a handle 105 having a foot 110 and an aimer 115 . foot 110 has a semicircular cross - section ( fig3 a ) so that it will fit between the graft ligament and the wall of the bone tunnel . aimer 115 includes a bore 120 adapted to receive and guide a guide pin or guidewire 125 , which will itself subsequently guide osteotome 200 . a slot 122 ( fig3 b ) connects bore 120 to the top of aimer 115 , so that guidewire 125 can be released from aimer 115 , i . e ., when the distal end of the guidewire is deployed in a bone and guide instrument 100 is to be withdrawn proximally . the geometry of guide 100 ensures that the osteotome 200 is driven in line with the tunnel . preferably aimer 115 is constructed so that its bore 120 and slot 122 follow an axis that converges with the axis of foot 110 , so that the osteotome following this line converges with the deep end of the tunnel , whereby to create a wedge - shaped layer of bone ( fig6 and 7 ). the geometry of guide 100 also determines the thickness of the heel of the bone wedge . the exact optimal thickness of this wedge can vary , but is typically between about 3 – 6 mm ( discussed in more detail below ). however , if desired , aimer 115 can be constructed so that its bore 120 and slot 122 follow an axis that is parallel to the axis of foot 110 , so that the osteotome following this line will pass substantially parallel to the bone tunnel , whereby to create a relatively flat layer of bone ( fig7 a and 7b ). the geometry of guide 100 will determine the thickness of the bone layer . in still another form of the invention , aimer 115 may be constructed so that its bore 120 and slot 122 follow an axis that diverges from the axis of foot 110 , so that the osteotome following this line will move away from the bone tunnel , whereby to create a distally - thickening layer of bone ( fig7 c and 7d ). osteotome 200 is shown in fig4 and 5 . osteotome 200 generally comprises a handle 205 and a blade 210 . when used with the cannulated system , lumen 215 extends through handle 205 and blade 210 . lumen 215 is sized to receive guidewire 125 therein , so that osteotome 200 can ride down guidewire 125 and create the desired layer of bone . as noted above , the shape of osteotome 200 and its angle of insertion are important elements of this technique . the osteotome 200 is preferably passed into the knee through the same anterior - medial knee portal normally used for screw insertion . this angle of insertion is preferably approximately 20 – 50 degrees different than the tunnel angle , depending on the degree of knee flexion . with the osteotome anterior to the tunnel , the converging angles of the osteotome and the bone tunnel create an intervening bone wedge layer terminating about 20 – 30 mm from the tunnel entrance as the osteotome penetrates into the tunnel itself . the osteotome shape preferably includes several elements , and the particular instrument described here incorporates these elements . it should include a slim , narrow , pointed tip 220 to help guide the instrument and keep it in line with the tunnel . the osteotome should flare fairly steeply on its inferior surface 225 so as to aid in the initial compression of the bone wedge against the tendon . the overall width 230 ( fig5 ) of the osteotome should be slightly narrower than the bone tunnel diameter , creating a bone wedge just narrow enough to allow it to fit into the bone tunnel , with a slight break - away of each side of the wedge from the adjacent bone . downwardly directed flanges 235 ( fig5 ) on each side of the osteotome aid in separating the intact wedge from the surrounding bone . the bone layer should be thin enough to allow easy compression into the tunnel but thick enough to help maintain the structural integrity of the bone wedge . the shape of the osteotome , at the level of the outer bone edge , is preferably arcuate , rounded or oval , creating an easy starting point for placement of the fixation device . during use , the ligament is first placed in the bone tunnel ( fig1 ). if using guide 100 , the guide is inserted into the tunnel so that its foot 110 ( fig2 and 3a ) extends between the outer surface of the ligament and the deep wall of the bone tunnel . then the guidewire 125 is run down aimer 115 ( fig2 and 3b ) and into the bone . the guidewire 125 is preferably advanced until it passes into the end of the tendon graft . guide 100 is then withdrawn , leaving the guidewire 125 in place ( fig6 ). then osteotome 200 is advanced over the guidewire , into the bone and then withdrawn . withdrawal of the osteotome leaves behind a small “ tunnel above the tunnel ”, with an intervening wedge shaped layer of bone ( fig7 ). the bone wedge is depressed inferiorly , into the bone tunnel , with slight micro - fracturing of the bone layer edges , permitting displacement of the wedge . the interference fixation device ( e . g ., a traditional interference screw or a specially designed interference fixation device 300 such as shown in fig8 ) is then advanced above the wedge of bone , with or without use of a guidewire , and through the osteotomy site , and preferably directly into the end portion of the tendon - graft substance . see fig8 . one of the currently commercially available interference screws may be used to provide fixation . alternatively , a wedge - shaped element , or a frusto - conical pin , or some other form of object , preferably with ribs or ridges so as to retard withdrawal , may be used to force the formed layer of bone away from the host bone and thereby effect fixation . however , creation of a new screw shape and configuration specific for this technique represents a new device that should help improve tendon - graft fixation strength . optimal screw length can be estimated by the use of measurement markings etched directly on the osteotome or by use of a depth gauge , if desired . lengthening the tip of the screw and making the tip relatively “ sharper ” than the currently blunt - tipped screws creates a pin - like configuration that allows the tip of the screw to penetrate the tendon substance at the osteotomy / bone tunnel interface , providing some degree of tendon transfixation and thereby improving pullout strength . altering the pitch and lead of the screw may also be beneficial , as the screw will be primarily interfacing with bone , as opposed to half bone , half tendon as is normally the situation . also , a screw that has a degree of taper may also work better ; the increased diameter at the butt end of the screw may increase compression of the bone wedge into the tendon ( fig8 ). thus , for example , in fig9 there is shown a novel interference screw 300 which comprises one preferred form of interference fixation device . screw 300 generally comprises a body 305 including screw threads 310 . a cutting flute 315 may also be provided . an elongated leading tip 320 is disposed at the distal end of body 305 . tip 320 is preferably sufficiently sharp to be able to transfix a ligament by passing at least partially therethrough . screw 300 also includes a non - circular ( e . g ., hexagonal ) recess 325 at its proximal end for receiving a driver ( not shown ) whereby the interference screw may be turned . if desired , screw 300 may be cannulated with a lumen 330 so that it may be deployed over a guidewire or the like . as noted above , the foregoing description of the femoral side of an acl reconstruction is intended to be merely one example of the multiple uses of the present invention . thus , for example , the invention may also be used on the tibial side of an acl reconstruction ( see , for example , fig1 , which shows the invention being used on both the femoral and tibial sides of an acl reconstruction ). or the invention may be used in other types of ligament reconstruction . it is also possible to form the desired layer of bone with a non - cannulated osteotome . more particularly , guide 100 can be used to form a guide hole into the bone with its guide pin or guidewire 125 , whereupon the guide 100 and guide pin or guidewire 125 are removed , leaving a guide hole in the bone . then an osteotome 200 a ( fig1 a – 10c ) is used to form the desired layer of bone . osteotome 200 a is preferably substantially identical to the osteotome 200 described above , except that its lumen 215 is replaced by a guide tip 215 a . during formation of the desired bone layer , guide tip 215 a is advanced into the guide hole in the bone , whereby to regulate the path and / or depth of penetration of the osteotome . fig1 – 25 show further aspects of the present invention in the context of an acl reconstruction . if desired , the techniques of the present invention may be used alone , as the sole manner of fixing the graft ligament in the bone tunnel . alternatively , the present invention may be used in addition to another type of fixation system , e . g ., an endobutton ™ system or cross - pinning , etc . there are several significant advantages to using this fixation system over the conventional systems currently in use . first , the tendon is still held in place by tight interference compression , but it is now surrounded by native bone . compression on each side of the graft by cancellous bone significantly enhances circumferential bone ingrowth potential . the bone wedge has not been displaced significantly , thus allowing rapid bony healing circumferentially around the tendon graft . with the deep end of the screw at least partially imbedded into the deep portion of the tendon , any traction on the graft will likely have a “ deadmanlike ” pull on the screw tip , wedging the butt end of the screw into the overlying bone as tension on the graft pulls on the screw tip , thereby enhancing fixation . also , any fixation benefits derived from the presence of a bone block or the use of fixation - augmentation devices attached to the end of the tendon , such as the endo - pearl ™ or similar devices , would be enhanced . the displacement of the graft attached to any of these devices or bone blocks would be inhibited by the presence of the bone wedge between the device or bone block and the tunnel outlet . also , exclusion of synovial fluid from the bone tunnel , an ingrowth - enhancing advantage of interference fixation , is maintained . a key but often under - appreciated element of the high pullout values in some of the more recent interference fixation studies is that the high values are usually very technique dependent . an interference screw that diverges during insertion can negate the benefits of even the best tunnel and graft preparation . the precise positioning of the screw in the bone tunnel is crucial . however , this is not always easy to control . also , spinning of the tendon graft during insertion of the screw is a well - documented problem that is difficult to control once it has begun . this “ tendon spin ” can damage the graft and result in impingement and less than ideal graft positioning , possibly affecting the clinical results . one of the obvious immediate benefits of this new fixation approach is that tendon spin is completely eliminated . the fixation screw device turns against bone on all sides , preventing any occurrence of tendon spinning during insertion of the device . screw location and placement is more controllable with the new system described here , making the results more predictable .
a new approach for reconstructing a ligament , the new approach comprising : creating a bone tunnel within a host bone , the bone tunnel having a proximal end and a distal end , and defining a central axis extending from the proximal end to the distal end ; creating an intervening layer of bone between the central axis of the bone tunnel and a rigid portion of the host bone , the intervening layer having a first side and a second side in opposition to one another , the first side of the intervening layer facing toward the central axis of the bone tunnel and the second side of the intervening layer facing toward the rigid portion of the surrounding host bone ; and compressing the intervening layer of bone against a graft ligament positioned within the bone tunnel .