the following description is merely exemplary in nature and is not intended to limit the present disclosure , application , or uses . it should be understood that throughout the drawings , corresponding reference numerals indicate like or corresponding parts and features . fig1 and 2 represent a system and method of forming a prosthetic 20 about a graft or graft replacement material 22 to form an artificial bone - tendon or bone - tendon - bone prosthetic assembly 24 according to one embodiment disclosed herein . shown is a mold 23 having a first and second dies 26 and 28 , which define a cavity 30 therethrough . defined by the first die 26 is an injection port 32 , which allows for the filling of the through cavity 30 with biocompatible material . as shown in fig1 , a suture 34 is threaded through a loop 36 of the replacement graft material 22 , or tied to the ends of the graft material 22 . the suture 34 and loop 36 of graft material 22 are pulled through the through cavity 30 to position the loop 36 of graft 22 in the cavity 30 . after the loop 36 of graft material 22 is placed within the through cavity 30 , an uncured biocompatible polymer material 31 , bone cement , or a calcium phosphate containing mixture is then injected through injection port 32 . after the curing or setting of the polymer 31 , the first and second dies 26 and 28 are separated exposing the prosthetic 20 intimately frictionally and / or mechanically coupled to the graft 22 . in this regard , the exterior surface of a portion of the replacement graft is completely enclosed or encapsulated by the prosthetic 20 . in other words , the prosthetic can function to protect this portion of the graft replacement 22 from interaction with hardware used to couple the graft assembly 24 to the bone . the replacement graft 22 may be a preoperative or intraoperatively harvested tendon such has a hamstring or may be xenograft , allograft , or artificial graft material . as shown in fig3 a - 3 c , the exterior surface 38 of the prosthetic 20 can be textured by modifying the interior surface of the cavity 30 . in this regard , the exterior surface 38 can be smooth , porous , or define an external thread . as described below , the exterior surface 38 can also define locking features which interface with a fastener or an interior surface of an implant accepting bore to fix the prosthetic assembly 24 within an aperture . additionally , the exterior surface 38 can be shaped or machined after molding . fig4 represents an alternate mold 33 for forming the prosthetics shown in fig3 a - 3 c . as shown , the cavity 30 can be defined by a single die 26 ′. this die 26 ′ defines a generally cylindrical cavity 30 , which has a conical injection port 32 . the suture 34 can be threaded through the injection port 32 , pulling the soft tissue replacement within the cavity 30 . after the biocompatible material is placed into the conical injection port 32 , a plunger - type cap 46 can be inserted into the conical injection port 32 to press the biocompatible material into the cylindrical cavity . it is envisioned that the injection port 32 can be threaded or configured to be formed to accept a syringe , which can be used to inject biological material or bone cement . the cavity 30 can be tapered to facilitate removal of the prosthetic assembly 24 after setting of the polymer 31 . alternately , the interior surface of the molds 26 can have a plurality of members ( not shown ) which function to position the graft material 22 centrally within the mold 26 . further , these members can compress the graft material 22 at discrete locations to allow the formation of a plug with interdigitation of cement . ( see fig6 a ). fig5 a - 5 d represent optional tying mechanisms 42 a - 42 d , which are used to bind the loop 36 of graft material 22 . as shown in fig6 b , a plurality of tying mechanisms 42 a - 42 d can be annularly disposed about the loop 36 of the graft material 22 . the interior surface of the tying mechanisms 42 a - 42 d can be textured 43 so as to prevent the relative displacement of the tying mechanism 42 a - 42 d with respect to the loop 36 of the graft material 22 . as shown in fig5 c , the tying mechanism 42 a - 42 d can have structures 45 that allow for the non - releasable or releasable tightening of the tying mechanism about the graft loop 36 . as shown in fig6 c , a single tying member 42 d can be formed as a coil spring 42 d . the coil spring 42 d can be radially expanded so as to allow for the insertion of the loop 36 into an inner space defined by the coils of the coil spring 42 d . after the tying mechanism is coupled to the graft loop 36 , the subassembly is positioned within the mold as disclosed above to form the prosthetic assembly 24 . depicted is a cross - sectional view of the graft loop 36 disposed within the formed prosthetic 20 . shown is the tying mechanism 42 d disposed about the graft loop 36 which is fully disposed within the prosthetic 20 . while a distal end of the loop 36 of graft material is shown being exposed to allow acceptance of a suture , it is equally envisioned the distal end of the loop 36 can be fully incorporated into the prosthetic 20 . fig7 a represents an alternate prosthetic 50 configured to be coupled to the loop 36 of the graft material 22 . the prosthetic 50 , as well as those described below , are formed of first and second members 52 and 54 which are mechanically , ultrasonically , or adhesively coupled together . the members 52 and 54 together define a graft - accepting through - passage 56 . disposed within the through - passage 56 are a plurality of counter - posed graft - engaging members 58 . the counter - posed graft - engaging members 58 are configured to pierce or frictionally engage the graft material 22 . additionally , optional coupling surfaces can be formed on the counter - posed graft - engaging members 58 to couple the first and second members 52 and 54 together . as described above , optionally disposed on an exterior surface of the prosthetic 50 is a bone - engaging bearing surface 60 . this bone - engaging bearing surface 60 can be on either or both of the first and second members 52 and 54 . fig7 b shows the prosthetic 50 disposed within a bore 64 defined in a tibia 66 . as shown , the bone - engaging bearing surface 60 has an angled bearing surface 62 , which interfaces with a counter sunk surface 65 formed in an outer surface of the tibia 66 . the prosthetic 50 is formed of a biocompatible material . in this regard , the material can be any biocompatible material such as metal or polymer such as ultrasonically bondable peek , pekk , or can be a resorbable material such as lactosorb ®. fig8 a and 8 b represent perspective views of an alternate prosthetic 68 according to the disclosure herein . the prosthetic 68 is formed of first and second members 70 and 72 . the first member 70 is generally cylindrical having a graft loop accepting through - passage 74 . the first member 70 can be formed of an inner member 77 and an outer member 78 . the inner member 76 defines a plurality of graft - engaging member accepting apertures 77 . these apertures 77 can be formed on opposite sides of the first member 70 to facilitate the locking of the graft - engaging second member 72 to the first member 70 . the outer member 78 is annularly disposed about the inner member 76 . in this regard , the outer member 78 defines a groove 80 , which generally surrounds the graft - engaging member apertures 76 . the second member 72 is generally arcuate and is configured to be disposed within the groove 80 formed by the outer member 78 . disposed on a convex inner surface 82 of the second member 72 are a plurality of graft - engaging members 79 . these graft - engaging members 79 are configured to be aligned with the graft - engaging member apertures 77 formed in the first member 70 . as shown in fig8 b , the graft loop 36 is fed through the loop - accepting aperture 81 . the graft - engaging members 79 are aligned with the apertures 77 . the second member 72 is displaced toward the first member 70 , causing the graft - engaging member 79 to pierce or frictionally engage the graft loop 36 . the first and second members 70 and 72 are then ultrasonically , adhesively , press - fit or heat bonded together to form a single prosthetic . as shown in fig9 a - 9 d , the prosthetic 50 can have a plurality of coupling flanges 84 , which can be disposed about a mating surface 86 . these flanges 84 are configured to interface with corresponding slots 88 in the first member . as described above , the exterior surface 90 of the implant 50 can be textured . as shown , the exterior surface 90 can define an angled threaded depression 92 , which is configured to accept a bone - engaging screw 100 ( see fig1 ). additionally the exterior surface can define a generally concave threaded depression 93 which runs the length of the length of the implant . fig1 represents an artificial bone - tendon - bone prosthetic assembly 24 . the assembly 24 includes a pair of prosthetics 20 as shown in fig9 d coupled to proximal and distal ends of a loop of graft material . it is envisioned that the prosthetics 20 used to form the artificial bone - tendon - bone prosthetic assembly 24 can utilize any of the aforementioned prosthetics 20 . additionally shown is the suture used to install the artificial bone - tendon - bone prosthetic assembly 24 into the bone . fig1 depicts an implant 50 coupled to a graft 22 disposed within a tibial and femoral tunnel . as mentioned above , the graft 22 is coupled to the prosthetic 20 to form an artificial bone - tendon or bone - tendon - bone prosthetic assembly 24 . it is envisioned the physician can intraoperatively determine the desired graft or graft assembly length and appropriate graft tension . the first prosthetic 20 is coupled to a first end of the replacement graft either preoperatively or intraoperatively using any of the methods described above . the physician then determines an appropriate length for the graft material 22 by measuring an anatomical distance . an appropriate amount of tension is applied to the graft and the length of the graft is then marked . a second prosthetic 20 ′ is then coupled to the prosthetic assembly at the marked location . this location is a function of the measured anatomical distance , which takes into account mounting structures . this provides an appropriately sized artificial bone - tendon - bone prosthetic . it is envisioned the second prosthetic 20 would then be coupled to the graft material intraoperatively . optionally , a kit of preformed artificial bone - tendon graft assemblies with an associated second prosthetic can be provided . additionally , the kit can contain the molds 26 or 26 ′ shown in fig1 or 4 , and a package of premeasured castable material . once the graft assembly 24 is formed , a suture 34 is coupled to the assembly . the suture 34 and prosthetic assembly 24 are threaded into the tunnel formed in the bone or bones , so as to position the prosthetics 20 and 20 ′ near an opening of the tibial and femoral tunnel . a fastener 100 is engagably driven between the implants 50 and the internal surface 94 of the bore 96 formed in the tibia . this locks the graft assembly 24 to the bone . appropriate tension is applied to the graft , which is fixed at its second end by a soft tissue / bone - engaging fastener 100 or other suitable means . the description of the teachings is merely exemplary in nature and , thus , variations that do not depart from the gist of the teachings are intended to be within the scope of the teachings . such variations are not to be regarded as a departure from the spirit and scope of the teachings .
a device for surgically coupling a soft tissue graft into a tunnel of a bone . the device includes a first member and a second member . the first member includes a first graft - engaging surface extending from a first end to a second end of the first member . the second member includes a second graft - engaging surface extending from a first end to a second end of the second member . the first graft - engaging surface and the second graft - engaging surface define a graft - accepting through - passage with a longitudinal axis extending therethrough when the first member is secured to the second member .