referring now more particularly to the drawings , procedures and anchoring devices for repairing soft tissue are illustrated . in fig1 , one embodiment of an implant 10 , constructed in accordance with the principles of the present invention , is shown . the implant 10 comprises a deployment screw 12 , which protrudes through a pair of compression pads 14 and 16 . the implant 10 comprises a body 18 , through which the deployment screw 12 also protrudes . the deployment screw 12 , at its distal end , is threaded into a wedge 20 . the left compression pad 14 slides into the right compression pad 16 , and they attach to one another . two pins 22 attach a pair of arms 24 to the body 18 . there is a track 26 on each side of the wedge 20 , best seen in fig1 a . each wedge track 26 attaches to a track post 28 ( fig1 b ) on a corresponding one of the arms 24 . the wedge tracks 26 function to prevent the wedge from rotating during deployment of the implant . the compression pads 14 , 16 slide into a pair of body tracks 30 ( fig1 ) in the body 18 , which allow the pads 14 , 16 to expand when the deployment screw 12 is rotated clockwise , as shown in fig2 - 4 . the body tracks 30 also prevent the pads 14 , 16 from rotating . in fig1 , the deployment screw 12 is shown in detail . this screw 12 comprises a quad lead section 32 , with four separate thread starts . this means that , for every single turn on the screw , the linear distance it travels is four times what a single lead screw would be . this feature enables the user to turn the screw fewer times than would be required with a single start thread , approximating the same number of turns that the user would need during the implantation of an interference screw such as the above described smith & amp ; nephew rci screw . often , during implantation , an interference screw requires a notch to be placed at the edge of the femoral tunnel aperture to allow the screw to start engaging into the bone . advantageously , the need for this step is eliminated when deploying the implant of the present invention , resulting in a substantially easier implementation procedure . accordingly , the present invention is easy to deploy as an interference screw , and requires fewer steps than in prior art approaches . the deployment screw 12 also provides a rigid backbone to support the implant . a screw head or compression pad deployer 34 deploys the compression pads 14 , 16 as the screw 12 moves axially into the implant . another feature of the screw 12 is a load transfer disk 36 that transfers some of the axial load from a junction between the screw head 34 and the body 18 to a junction between the load transfer disk 36 and the body 18 . this load transferring feature allows for thinner side walls or struts 38 on the body 18 due to a decreased load on struts 38 ( fig1 ), which , in turn , allows a larger tendon to fit between the deployment screw 12 and the body 18 . with reference now particularly to fig1 a and 11b , the compression pads 14 and 16 are shown in greater detail . the left and right compression pads 14 , 16 , respectively , compress the tendons against the femoral tunnel wall to promote tendon - to - bone healing at the aperture of the tunnel . unlike current approaches for more intimate tendon - to - bone contact that only reduce the space between the tendon and the tunnel wall , the present invention actively compresses the tendons against the bone tunnel . compression pad tracks 40 engage the body tracks 30 and interlock them to the body 18 . this joint also provides torsional resistance while moving the implant into place , and during initial deployment until the arms 24 start to engage with the bone . there are engagement slots 42 in each compression pad 14 , 16 , as shown , that engage with a deployment device that keep the implant 10 from rotating until the arms 24 engage the bone . the two compression pads 14 , 16 snap together using compression pad snaps 44 to prevent premature deployment of the pads . now referring to fig1 , the body 18 functions to trap the tendons on either side of the deployment screw 12 . the compression pads 14 , 16 engage the body tracks 30 and provide torsional strength to the body while inserting the implant into the femoral tunnel , thus allowing the compression pads 14 , 16 to expand parallel to one another . the struts 38 also provide structural support for the deployment screw 12 , wedge 20 , and arms 24 to deploy against . the arms 24 have a few key design features , as best shown in fig1 a and 13b . fins 46 on the top of each arm provide torsional strength for the wedge - to - arm junction . the fins 46 also allow easier insertion into the femoral tunnel when inserting into a femoral tunnel that is drilled off - axis from the tibial tunnel . the portion of the arm 24 that engages with the bone has a tapered edge 48 which allows for ease of bone displacement during deployment . a support rib 50 disposed along the length of the arm 24 is also tapered for ease of bone displacement , and provides structural support during axial loading . torsion pins 52 engage with a torsion hole 54 to provide additional torsional strength while the implant is being implanted into the femoral tunnel . fig1 a and 14b show , in greater detail , particular constructional features of the wedge 20 . the wedge 20 is threaded with a female quad lead thread 56 that matches the male quad lead thread 32 of the deployment screw 12 . the track posts 28 engage with the wedge tracks 26 to provide torsional strength through deployment . a tapered nose 58 on the wedge 20 allows easier off - axis insertion into the femoral tunnel . referring now to fig2 - 9 , a preferred method of using the disclosed inventive implant will now be discussed . in fig2 a and 2b , the implant 10 of fig1 is shown in its undeployed orientation . a preferred procedure for deploying the implant is generally similar in many respects to the procedure disclosed in u . s . patent application publication no . 2006 / 0155287 , herein already expressly incorporated by reference . thus , to accomplish tendon fixation using the exemplary methods and devices described herein , standard surgical preparation of the site and / or arthroscopic portals for access to the procedural region are performed . the joint is dilated with arthroscopic fluid if the procedure is to be performed arthroscopically . with open procedures , the device may easily be manipulated and deployed with a single hand . for arthroscopic procedures , the deployment device is introduced through a standard 5 , 6 , or 8 mm cannula placed into the joint . a range of preferred cannula sizes would be 2 - 11 mm . the procedures described herein are specifically adapted to repair of the acl in a patient &# 39 ; s knee . however , it should be kept in mind that the implants described herein may be used in numerous other soft tissue repair applications , using surgical procedures which are adapted to those applications . fig8 and 9a illustrate , from two different orientations , a hamstring acl reconstruction , wherein the implant 10 is utilized to secure the acl graft proximal to the femur 60 and distal to the tibia 62 of a patient . to deploy the implant 10 , a bone tunnel 64 is drilled completely through the tibia 62 and partially through the femur 60 . an actuator ( not shown ) is employed to insert the implant 10 distally through a tibial inlet aperture 66 and through the tibial tunnel 64 , so that the implant 10 is finally disposed in a portion of the tunnel 64 which is within the femur 60 , distal to a femoral aperture 68 , as shown in fig8 and 9a . now with respect to fig3 and 3a , once the implant 10 is in place within the femoral tunnel 64 , as shown in fig8 , the deployment screw 12 is actuated ( rotated ) in order to advance the screw 12 axially distally into the implant body 18 , and thus begin to deploy or expand the compression pads 14 and 16 outwardly . fig4 and 4a depict the next step , wherein advancement of the deployment screw 12 has caused the compression pads 14 , 16 to fully deploy . as noted above , the screw head or compression pad deployer 34 acts to deploy the compression pads 14 , 16 as it moves distally into the implant 10 , as shown . as the deployment screw 12 continues to move distally through the implant 10 , the distal end of the screw 12 , comprising the male quad lead section 32 ( fig1 ), engages the female quad lead thread 56 of the wedge 20 ( fig1 b ). continued axial distal movement of the screw 12 causes the threaded sections 32 and 56 to cooperate to move the wedge 20 axially in a proximal direction , as shown in fig5 . this proximal movement of the wedge 20 causes the arms 24 to begin to deploy outwardly . in fig6 , the wedge 20 is shown in a position where it is about halfway engaged within the separating arms 24 . in fig7 a and 7b , the wedge 20 is fully proximally engaged with the body 12 of the implant 10 , such that the arms 24 are , consequently , fully deployed . in fig8 , the implant 10 is shown in this fully deployed condition . fig9 a and 9b illustrate tendon compression as effected by the deployed implant 10 . in these figures , tendons 70 are compressed by deployed compression pads 14 , 16 against the femoral tunnel wall in order to promote tendon - to - bone healing at the aperture of the tunnel . advantageously , the inventive approach actively compresses the tendons against the bone tunnel . alternative implant designs are shown in fig1 and 16 . in particular , fig1 a and 15b illustrate an alternative embodiment ( with like elements being labeled with like reference numerals to those used in connection with the embodiment of fig1 ) wherein the arms 24 are flipped to the other side of the body 18 . the modified arms 24 are designed to permit the tendons ( not shown ) to pass by them and engage with the cortical bone . the arm - to - body joint is a pin - less design with a track way in the body that secures the arm 24 in place . fig1 a and 16b illustrate yet another modified embodiment wherein , once again , like elements are labeled with like reference numerals as those used in connection with the earlier embodiments . in this embodiment , the implant 10 uses the body 18 as a wedge . testing has been done by the inventors to verify the functionality of the disclosed invention of fig1 - 7 . as shown in fig1 , the inventors found that pull - out forces for the implant 10 were significantly higher than those of a predicate device , the rci interference screw available from smith & amp ; nephew . in fig1 - 21 there is shown another implant embodiment 110 , wherein like elements are identified with like reference numerals as for the embodiment of fig1 - 14 , preceded by the numeral 1 . as shown , the deployment screw 112 protrudes through the compression pads 114 and 116 , which are each integrated into the body 118 . the deployment screw 112 is threaded at its distal end into the wedge 120 . two pins 122 attach a pair of arms 124 to the body 118 , as shown . as noted above , in this embodiment the compression pads 114 , 116 are 25 integrated into the body 118 . this feature permits the use of a shorter implant than is the case for the implant of fig1 . a track 126 in the wedge 120 attaches to track posts 128 on the arms 124 ( fig2 ), which keep the wedge 120 from rotating during deployment . the compression pads expand as the implant is deployed . in particular , the screw 112 expands the pads 114 , 116 outwardly by sliding on a compression taper 72 ( fig2 ), as shown in fig2 - 23 . moreover , as the deployment screw 112 rotates , the wedge 120 expands the arms 124 as also shown in fig2 - 23 . once the screw 112 is fully seated , the expanded arms 124 fully engage with adjacent cancellous bone 74 , thus locking the anchor in place , as shown in fig2 . the deployment screw 112 ( fig2 ) has a male quad lead section 132 with four separate thread starts , as in the prior disclosed embodiment . this means that for every one rotation of the screw , the linear distance it travels is four times that which a single lead screw would travel . this enables the user to turn the screw fewer times than would be required with a single start thread , approximating the same number of turns that the user would need during the implantation of an interference screw such as the rci screw available from smith & amp ; newphew . oftentimes , during implantation , an interference screw such as the rci screw requires a notch to be placed at the edge of the femoral tunnel aperture to permit the screw to start engaging the bone . however , the present invention avoids the need for such a step , resulting in an easier implantation procedure . the invention is easy to deploy as an interference screw , and requires fewer steps . the deployment screw 112 also provides a rigid backbone to support the implant . a reverse threaded hex 75 is preferably provided to drive the screw . the screw head or compression pad deployer 134 deploys the compression pads 114 , 116 as the screw 112 advances axially into the implant . another feature of the screw is the provision of a load transfer disk 136 that transfers some of the axial load from the screw head 134 to body junction to the disk to body junction . this allows for thinner side walls or struts 138 on the body 118 due to the decreased load on the struts , which in turn allows a larger tendon to fit between the deployment screw 112 and the body 118 . as shown in fig2 , the compression pads 114 , 116 compress the tendons 170 against the femoral tunnel wall to promote tendon - to - bone healing at the aperture of the tunnel . unlike prior art approaches for more intimate tendon - to - bone contact that only reduce the space between the tendon and the tunnel wall , the present invention actively compresses the tendons against the bone tunnel . the compression pads 114 , 116 in this embodiment are integral with the body 118 . the body 118 functions to trap the tendons 170 on either side of the deployment screw 112 . the struts 138 are split , as shown at reference numeral 76 ( fig2 ), to allow the integrated compression pads 114 , 116 to expand and compress the tendon against the bone tunnel . they also provide structural support for the deployment screw 112 , wedge 120 , and arms 124 to deploy against . the arms 124 include a few key design features , as particularly shown in fig2 and 30 . fins 146 on the top provide torsional strength for the wedge 120 to arm 124 junction . they also allow easier insertion into the femoral tunnel when inserting into a femoral tunnel that is drilled off - axis from the tibial tunnel . the portion of the arm 24 that engages with the bone has a tapered edge 148 which allows for ease of bone displacement during deployment . the support rib 150 along the length of the arm 124 is also tapered for ease of bone displacement and provides structural support during axial loading . the torsion pins 152 engage with a torsion hole 154 to provide additional torsional strength while inserting into the femoral tunnel . as in the prior embodiment , the wedge 120 is threaded with a female quad lead thread 156 that matches the complementary threads 132 on the deployment screw 112 . the track posts 128 on the arms 124 engage with the wedge track 126 to provide torsional strength through deployment . a tapered nose 158 allows easier off - axis insertion into the femoral tunnel . fig3 is a table similar to that of fig1 , presenting data generated by the inventors which indicates that pull - out forces for the implant 110 were significantly higher than those of a predicate device , the rci interference screw available from smith & amp ; nephew . still another embodiment of the inventive implant is illustrated in fig3 - 54 , wherein like elements to those of the prior embodiments are identified by like reference numerals , preceded by the numeral 2 . this embodiment 210 utilizes the cortical bone for fixation in combination with tendon - to - bone compression . in this version of the invention , the deployment screw 212 is offset to one side of the implant 210 , for the purpose of permitting easier passing of tendon through the orifice . this implant deploys in two steps . the deployment screw 212 is rotated clockwise as an arm 78 and wedge 220 slide together across tapered faces 80 ( fig4 ) and 82 ( fig4 ) until they lock together with their respective cortical locks 84 , 86 . the wedge 220 and the arm 78 lock into place by filling a majority of the cross section of the femoral tunnel . thus , the implant is free to move in the femoral tunnel , allowing tactile feedback to ensure engagement of a cortical tab 88 with the cortex . the screw is then rotated so that it is advanced the remainder of the way , and the compression wedge 90 engages with the compression pads , thereby pressing the tendon against the bone tunnel wall . a track 92 , 94 in the compression pads 214 , 216 and compression wedge 90 prevents the compression wedge from 20 engaging unevenly . a progression of deployment of the implant 210 is illustrated in fig3 - 42 . fig4 - 50 illustrate various components of the embodiment . in the undeployed state , the arm is engaged with the wedge with the arm &# 39 ; s track posts 228 engaging with a t - bar 96 of the wedge 220 . this prevents the arm 78 from moving during insertion . also , to prevent the wedge 220 from rotating during deployment , the track post 228 is inserted into a torsion slot 100 . modified cortical fixation implant designs are illustrated in fig5 - 54 . fig5 and 52 illustrate a modified wedge and only one arm which allows engagement with the cortical bone . fig5 and 54 illustrate the same embodiments as in fig5 and 52 , wherein the screw is to one side of the implant . fig5 has been incorporated into this application to illustrate a substantially completed acl repair procedure . fig8 and 9 , as well as fig2 and 25 and fig4 and 42 , illustrate the installation of the femoral anchor of the present invention , in various embodiments . however , as one skilled in the art would understand , to complete the repair procedure further steps are necessary . once the femoral anchor has been deployed and installed , as previously described , the anchored tendons 70 extend proximally from the femoral tunnel through the tibial tunnel and out through tibial aperture 66 . to complete the procedure , a tibial anchor 102 is preferably installed , to anchor the tendon bundles in place , as shown in fig5 . once this anchor is in place , the proximal ends of the tendon bundles are trimmed to complete the procedure . this portion of the acl reconstruction procedure is fully explained in co - pending u . s . application ser . no . 11 / 725 , 981 , which has already been fully and expressly incorporated by reference herein . any suitable tibial anchor 102 may be used in conjunction with femoral anchors of the type disclosed in this application , but the tibial anchors shown and described in the &# 39 ; 981 patent application are presently preferred . accordingly , although exemplary embodiments of the invention has been 20 shown and described , it is to be understood that all the terms used herein are descriptive rather than limiting , and that many changes , modifications , and substitutions may be made by one having ordinary skill in the art without departing from the spirit and scope of the invention .
a soft tissue fixation system , most typically applicable to orthopedic joint repairs , such as anterior cruciate ligament knee repair procedures , comprises an implant which is placeable in a tunnel disposed in a portion of bone , wherein the tunnel is defined by walls comprised of bone . a first member is deployable outwardly to engage the tunnel walls for anchoring the implant in place in the tunnel , and a second member is deployable outwardly to engage tissue material to be fixed within the tunnel . the second member also functions to move the tissue material outwardly into contact with the tunnel walls to promote tendon - bone fixation . extra graft length is eliminated by compression of the tendon against the bone at the aperture of the femoral tunnel , which more closely replicates the native acl and increases graft stiffness . the inventive device provides high fixation of tendon to bone and active tendon - bone compression . graft strength has been found to be greater than 1 , 000 n , which is desirable for acl reconstruction systems .