a valve graft 1 according to the present disclosure is shown in fig1 - 3 . the valve graft generally comprises a valve frame 10 defining a valve frame open area ( 18 in fig4 ). the open area is spanned by a pair of valve flaps 12 constructed of a biomaterial , discussed below . the valve flaps have positioned therebetween an aperture 14 . the valve frame 10 is preferably a closed loop and is commonly constructed of fine - gauge metal ( e . g ., 0 . 014 inch diameter ), although other materials can be effectively employed . for example , the valve frame can alternatively be made of a synthetic material such as teflon ( polytetrafluoroethylene ). as well , the valve frame can be fabricated of a resorbable or biodegradable composition . in one embodiment , the valve frame 10 is a memory wire formed into a desired shape . as illustrated herein , the valve frame is rhomboidal , although other shapes can be utilized to effect a variety of valve shapes and dimensions . such a shape memory wire frame is known in the art as a frame that substantially returns to its original shape after it is deformed and then released , as described in u . s . pat . no . 4 , 512 , 338 ( to balko et al .). the alternative compositions disclosed above also can be of a memory character if desired . the valve flaps 12 span the valve frame open area 18 and are suturelessly bonded to the valve frame 10 . an aperture 14 separates the valve flaps and serves as a port through which fluid can traverse the valve graft when in use in a patient &# 39 ; s vessel . the valve flaps 12 preferably are of a collageneous biomaterial and can be constructed using a variety of collagen - rich biomaterials , e . g ., a synthetic collagen matrix or of native tissue - derived , collagen - rich biomaterials such as pericardium , peritoneum , dura mater , fascia and bladder or ureteral acellular matrices . an exemplary method for making the valve graft described above is shown in fig4 - 8 . in this method , a valve frame 10 is distorted into a flexed state ( fig4 ). in this flexed state , the ratio of the long axis of the frame to its short axis is increased as compared to the base state . in the preferred embodiment wherein the frame is composed of a memory material , it should be apparent that the valve frame will therefore be under tension when flexed . the valve frame is then placed on a first major surface 22 of a sheet of biomaterial 20 ( fig5 - 6 ). a cross - section through line 6 - 6 of fig5 , corresponding to the short axis of the valve frame , is shown in fig6 . an edge 24 of the biomaterial 20 is folded over the valve frame 10 to contact the edge with the first major surface 22 of the biomaterial ( fig7 ) and form thereby a first bonding locus 30 . in this embodiment , the biomaterial 20 is a trimmed portion of porcine intestinal submucosa . the intestinal submucosa graft is harvested and delaminated in accordance with the description in u . s . pat . nos . 4 , 956 , 178 and 4 , 902 , 508 ( both to badylak et al .). an intestinal submucosa segment is thereby obtained that can be effectively used as a biomaterial sheet as described herein . sutureless bonding of the edge 24 of the biomaterial sheet to the first major surface 22 of the sheet is illustrated in fig8 . the sutureless bonding can be achieved using thermal bonding or chemical cross - linking techniques . in thermal bonding shown in fig8 , the at least first bonding locus 30 , in which the edge 24 of the biomaterial 20 is apposed to the first major surface 22 thereof , is irradiated with energy 32 sufficiently to heat , denature and fuse together the components of the biomaterial . the bonding technique is preferably confined to the selected bonding loci , such that the sutureless bonding effectively “ spot - welds ” the biomaterial edge to the first major surface of the sheet . alternatively , the edge can be welded to the first major surface in one or more weld lines . in irradiating the at least first bonding locus with energy from an energy source 34 , wherein the energy source is an 800 nm diode laser , propagation of laser energy is preferably directed perpendicular to the biomaterial . the biomaterial , preferably being transparent to the laser light at the chosen light wavelength , absorbs little energy and hence sustains minimal thermal damage . however , the energy - absorbing material at the at least first bonding locus absorbs energy and thereby conducts heat to the adjacent biomaterial . sutureless bonding using thermal energy preferably creates a weld while minimizing transfer of heat to surrounding tissues , thereby reducing collateral thermal damage . the chromophore also can aid in thermal confinement and thereby reduce denaturation of surrounding tissue . with sufficient energy irradiation , the biomaterial edge and first major surface at the at least first bonding locus are denatured at the protein level . it is believed that the molecules in the biomaterial intertwine with one another . upon cooling , the bond site is weld - sealed , wherein the biomaterial edge and first major surface of the biomaterial are welded together . as has been mentioned , the valve frame alternatively can be constructed so as to comprise a biological material amenable to laser fusion techniques . with such an embodiment , the collagen - rich biomaterial sheet can be attached to the valve frame by fusion directly thereto , rather than folding the sheet around it and fusing the edge to the first major surface . the combination of an energy - absorbing material ( i . e ., a chromophore , such as indocyanine green ( icg )) and an 800 nm diode laser is the preferred equipment for sutureless bonding in the method herein disclosed . the chromophore can be an endogenous or exogenous substance . the at least first bonding locus at the folded - over edge preferably includes the chromophore , either by treatment of the biomaterial before sutureless bonding or by topical application of a chromophore during sutureless bonding . thermal bonding can be accomplished according to either of two models . in a first model as discussed above , a device is remotely employed to generate heat within the biomaterial . a second thermal bonding model involves contacting a device with the at least first bonding locus for direct generation of heat at the biomaterial contact site . such devices for contact - heating are known in the art and include a contact thermo - electric transducer . in a first alternative sutureless bonding model , the biomaterial edge can be bonded to the first major surface by photo - chemical cross - linking . in a first embodiment of this technique , methylene blue is introduced to the at least first bonding locus and the region is irradiated with white light or other non - collimated light . conventional chemical or photo - crosslinking agents frequently present toxicity concerns if introduced into a patient . for this reason , it is preferable that such agents be avoided or the valve graft well rinsed to remove as much of the agent as possible . methylene blue is a preferred substance for photochemical cross - linking as described above , because the dye has been shown to be easily rinsed from collagen - rich biomaterials such as sis . the sutureless bonding technique used can vary according to desired locus size , biomaterial , speed , cost , and procedural considerations . in all cases , however , it is apparent that the disclosed method avoids the use of sutures to attach the biomaterial to the prosthesis frame . sutureless bonding as disclosed herein possesses a satisfactory bond strength to permit the valve graft to be implanted into a patient &# 39 ; s tubular vessel without increasing the risk of bond failure over that of conventional sutured attachment schemes . as has been mentioned , the presence of sutures at an implantation site increases the probability of post - procedure complications , such as foreign body reaction , thrombogenesis , leakage and reflux of fluid . use of the sutureless bonding method therefore produces a valve graft more readily received by a patient &# 39 ; s body . the present method results in thermal fusion of the biomaterial to generate a strong bond . as well , the resulting valve graft provides a high affinity , migratory , and integrative capability for host cell and tissue ingrowth . the bioprosthesis also prevents fluid leakage while retaining a soft , pliable character . employment of a biomaterial sheath and avoidance of sutures provide a non - carcinogenic valve stent that greatly minimizes calcification and foreign body reactions . an aperture 14 is formed in the biomaterial sheet 20 , creating the bidentate valve graft shown herein . the width of the aperture can be varied to control the flexibility of the valve and the maximum flow rate through the valve . fig9 - 10 are diagrams of one embodiment of a method for implanting a valve graft 1 at an implantation site 40 in a patient &# 39 ; s tubular vessel 50 . the valve graft 1 first is folded along one axis ( i . e ., along reference line a - a in fig1 ), bringing proximate the distal corners of the frame . the biomaterial sheet typically is stretched thereby and preferably curves below the short axis and toward the distal corners , taking on a saddle - like shape . owing to both the composition of the valve frame and the tensile strength of the biomaterial , tension on the biomaterial is not so great as to tear the biomaterial or to pull open the aperture . a catheter 60 is preferably employed to introduce the folded valve graft to the implantation site . the valve graft 1 is sufficiently tightly folded to permit the valve graft to be placed within the catheter 60 . this fitment is generally achieved by bringing the distal corners closer and also compressing the frame along the fold axis . the resultant folded valve graft has a high aspect ratio relative to its relaxed orientation ( i . e ., as shown in fig9 ). the catheter 60 is then maneuvered to position the distal tip thereof at the implantation site 40 , such as in a vein 50 . the tightly - folded valve graft is introduced into the vein or other tubular vessel by deployment from the distal tip of the catheter 60 , as shown in fig1 . such release can be achieved by pushing the valve graft from inside the catheter with a ramrod - type element 62 , such as a guidewire . upon release from the catheter , the valve graft will tend to spring back to its original conformation , limited by the walls of the tubular vessel ( fig1 - 11 , with the valve aperture shown open ). this expanding tendency is due to the shape memory material of which the valve frame is constructed . the valve graft will remain at the implantation site in a folded state , though not so tightly folded as in fig9 . over time , native tissue overgrowth occurs , further anchoring the valve graft in place . a collagen - rich biomaterial sheet can serve as a layer ( s ) ( single or multiple sheets ) applied to a supporting structure ( e . g ., valve frame ) to control fluid flow direction through the conduit while preventing leakage out of the conduit . such valve grafts might be used , for example , in the cardiovascular system ( blood vessels ), gastrointestinal tract , urinary tract , and trachea fig1 - 13 show simplified views of the implanted valve graft of fig1 - 11 , illustrating unidirectional flow control via valve action . for purposes of explanation , it will be assumed that a valve graft has been implanted in a vein of a patient . it should be noted that the flaps 12 or leaflets of the valve graft 1 have a flexible character imparted by the composition of the biomaterial sheet 20 . the flaps 12 therefore can be flexed or bowed by the force of the incident fluid . such pliant or elastic property is known in the art for “ natural tissue ” valves , as opposed to mechanical valves . in fig1 , anterograde blood flow in the vein 50 is occurring , consistent with normal circulation , i . e ., from right to left . pressure on the upstream surface of the valve graft flaps 12 by the blood ( solid arrow ) causes the flaps 12 to be bowed toward the walls of the vein 50 . the valve graft aperture 14 is opened thereby , permitting the blood to flow through the valve graft 1 and further downstream ( solid arrow ) through the vein 50 . in retrograde blood flow to the valve ( solid arrow , fig1 ), blood fills and is trapped in the “ dead - end ” regions between the valve graft flaps 12 and the vein wall 50 . this phenomenon , coupled with the continuing - fluid pressure on the flaps 12 caused by physiological blood flow , causes blood to contact and press on the downstream surface of the valve graft flaps , flexing them inward and away from the vessel walls 50 . by bowing the flaps inward , the valve graft aperture 14 is effectively closed and retrograde flow through the valve graft is substantially prevented ( dashed arrow ). a valve graft preferably is constructed in which the aperture is substantially closed when the valve graft is in a resting - state conformation ( i . e ., its state when implanted in a vessel having no fluid flow ). such construction is dependent on the size , shape , and dimensions of the valve frame , the presence and degree of tension that can be applied to the biomaterial sheet during valve graft fabrication , and the dimensions and orientation of the aperture . in another alternative valve graft , the aperture can be designed to incompletely close or to substantially narrow in the face of retrograde flow , depending on the particular configuration and dimensions of the implanted valve graft . if a partial retrograde flow is desired , for example , the aperture dimensions can be chosen to prevent complete closure of the aperture in an in situ implantation . implantation of a valve graft according to the present disclosure provides several benefits over prior art prostheses . collagen and sis are known to provide a matrix that encourages native cell repopulation and may ultimately enhance tissue repair and regeneration as well as integration of implanted supporting structure materials . one advantage of the disclosed method for making a valve graft is that thermal bonding , and especially laser fusion of the biomaterial edge to the first major surface is a rapid technique that yields water - tight bonds . as well , laser fusion has the capability of attaching multiple biomaterial sheets at numerous locations on their major surfaces , reducing the chance of leakage between the biomaterial sheets . heretofore , laser fusion has not gained widespread acceptance for bonding approximated tissue edges , largely because of weak bond strength . however , laser fusion of collagen - rich biomaterials as described herein resulted in strong tissue bonds . further , collagen - rich biomaterials have been observed to readily incorporate chromophores such as icg , further enhancing the efficacy of laser fusion in the present invention . another advantage of the present valve graft over prior art prostheses is that the use of sutures is obviated in the present invention . the risk of a foreign body response is therefore substantially mitigated . a further advantage is that a valve graft as disclosed herein and constructed with collageneous biomaterial flaps will retain the excellent bio - active properties of small intestinal submucosa graft with greatly reduced risk of cytotoxicity and foreign body reactions . the sutureless bonding welds provide sufficient mechanical and structural strength to enable the valve graft to be employed in medical procedures and to function acceptably in situ . a person skilled in the art will be able to practice the present invention in view of the description present in this document , which is to be taken as a whole . numerous details have been set forth in order to provide a more thorough understanding of the invention . in other instances , well - known features have not been described in detail in order not to obscure unnecessarily the invention . while the invention has been disclosed in its preferred form , the specific embodiments presented herein are not to be considered in a limiting sense . indeed , it should be readily apparent to those skilled in the art in view of the present description that the invention can be modified in numerous ways . the inventor regards the subject matter of the invention to include all combinations and sub - combinations of the various elements , features , functions and / or properties disclosed herein .
a bioprosthetic valve graft comprises a valve frame and valve flaps , the latter acting to open or close a valve aperture to directionally control fluid flow through the bioprosthesis . the bioprosthetic valve graft comprises method for suturelessly attaching a biomaterial suturelessly bonded to the a method for securing a biomaterial to a valve frame includes positioning a flexible valve frame defining an open area on a first major surface of a biomaterial sheet having a peripheral edge , wherein positioning serves to approximate the valve frame and the peripheral edge of the biomaterial sheet to form an at least first bonding locus ; and suturelessly bonding the biomaterial to the valve frame at the at least first bonding locus . the method avoids the disadvantages associated with conventional sutures and substantially reduces medical complications in implantations .