reference is now made to the figures wherein like parts are designated with like numerals throughout . fig1 to 3 represent a device 1 for replacing a heart valve by a percutaneous route . this device comprises a tubular catheter 2 formed from three tubes 5 , 6 , 7 engaged one inside the other and on which there are placed , from the proximal end to the distal end ( considered with respect to the flow of blood , that is to say from right to left in fig1 ), a prosthetic valve 10 , two series of blades 11 , 12 , a balloon 13 and a filter 14 . the three tubes 5 , 6 , 7 are mounted so that they can slide one inside the other . the interior tube 5 delimits a passage 15 , the cross section of which is large enough to allow blood to flow through it . at the proximal end , the intermediate tube 6 forms a bell housing 6 a delimiting , with the interior tube 5 , an annular cavity 17 in which the prosthetic valve 10 is contained in the furled condition . fig4 shows that this valve 10 comprises an armature 20 and valve leaflets 21 mounted so that they are functionally mobile on this armature 20 . the armature comprises a collection of wires 22 , 23 , 24 made of shape memory material , particularly of nickel - titanium alloy known by the name of “ nitinol ;” namely , ( i ) a proximal end wire 22 which , when the valve 10 is in the deployed state , has a roughly circular shape ; ( ii ) a distal end wire 23 forming three corrugations in the axial direction , these corrugations being distributed uniformly around the circumference of the valve 10 , and ( iii ) an intermediate wire 24 forming longitudinal corrugations between the wires 22 and 23 , this wire 24 being connected to the latter ones via the ends of each of these corrugations . the valve leaflets 21 for their part are made of biological material ( preserved human or animal valve leaflets ) or of synthetic material , such as a polymer . the armature 20 may , when its material is cooled , be radially contracted so that the valve 10 can enter the cavity 17 . when this material is heated to body temperature , this armature 20 returns to its original shape , depicted in fig4 , in which it has a diameter matched to that of a bodily vessel , particularly the aorta , in which the native valve that is to be treated lies . this diameter of the armature 20 is such that the valve 10 bears against the wall of the bodily vessel and is immobilized in the axial direction with respect to that vessel . each series of blades 11 , 12 comprises metal elongate blades 30 and an inflatable balloon 31 situated between the catheter 2 and these blades 30 . the blades 30 have a curved profile and are arranged on the circumference of the catheter 2 , as shown in fig2 , 3 and 3 a . the blades 30 of the proximal series 11 are connected pivotably to the tube 6 by their proximal ends and comprise a cutting distal edge 30 a , while the blades 30 of the distal series 12 are connected pivotably to the exterior tube 7 by their distal ends and comprise a cutting proximal edge 30 b . the connection between the blades 30 and the respective tubes 6 and 7 is achieved by welding the ends of the blades 30 together to form a ring , this ring being fixed axially to the corresponding tube 6 , 7 by crimping this ring onto this tube 6 , 7 , the pivoting of the blades 30 being achieved by simple elastic deformation of these blades 30 . this pivoting can take place between a position in which the blades 30 are furled , radially internally with respect to the catheter 2 and shown in fig1 and 2 , and a position in which these blades 30 are unfurled , radially externally with respect to this catheter 2 and shown in fig3 . in the furled position , the blades 30 lie close to the wall of the tube 6 and partially overlap each other so that they do not impede the introduction and the sliding of the device 1 into and in the bodily vessel in which the native valve that is to be treated lies ; in said unfurled position , the blades 30 are deployed in a corolla so that their cutting edges 30 a , 30 b are placed in the continuation of one another and thus constitute a circular cutting edge visible in fig3 . each balloon 31 , placed between the tube 3 and the blades 30 , may be inflated from the end of the catheter 2 which emerges from the patient , via a passage 32 formed in the tube 6 . it thus , when inflated , allows the blades 30 to be brought from their furled position into their unfurled position , and performs the reverse effect when deflated . the axial sliding of the tube 6 with respect to the tube 7 allows the series of blades 11 , 12 to be moved axially toward one another , between a spaced - apart position shown in fig1 , and a close - together position . in the former of these positions , one series of blades 11 may be placed axially on one side of the native valve while the other series of blades 12 is placed axially on the other side of this valve , whereas in the latter of these positions , the circular cutting edges of these two series of blades 11 , 12 are brought into mutual contact and thus cut through the native valve in such a way as to detach it from said bodily vessel . the tubes 5 to 7 further comprise marks ( not visible in the figures ) in barium sulfate allowing the axial position of the device 1 with respect to the native valve to be identified percutaneously so that , each of the two series of blades 11 , 12 can be placed on one axial side of this valve . these tubes 5 to 7 also comprise lateral distal openings ( not depicted ) to allow the blood to reach the bodily vessel , these openings being formed in such a way that the length of catheter 2 through which the blood flows is as short as possible , that is to say immediately after the filter 14 , in the distal direction . the balloon 13 is placed on the exterior face of the tube 7 , distally with respect to the series 12 . this balloon 13 has an annular shape and is shaped to be able to occupy a furled position in which it has a cross section such that it does not impede the introduction and sliding of the device 1 into and in said bodily vessel , and an unfurled position , in which it occupies all of the space between the exterior face of the tube 7 and the wall of said bodily vessel and , via a peripheral edge 13 a which it comprises , bears against this wall . the filter 14 is placed distally with respect to the balloon 13 , on the tube 7 , to which it is axially fixed . this filter 14 is made of flexible material , for example polyester netting , and is shaped to be able to occupy a furled position in which it has a cross section such that it does not impede the introduction and sliding of the device 1 into and in said bodily vessel , and an unfurled position in which it occupies all of the space between the exterior face of the catheter 2 and the wall of this vessel and , via a peripheral edge 14 a which it comprises , bears against this wall . an inflatable balloon 35 is placed between the tube 7 and the filter 14 so as , depending on whether it is inflated or deflated , to bring the filter 14 into its respective unfurled and furled positions . in practice , as shown by fig5 to 9 , the device 1 is introduced into said bodily vessel 50 by a percutaneous route and is slid along inside this vessel 50 until each of the series 11 , 12 of blades is placed on one side of the native valve 55 that is to be treated ( fig5 ). this position is identified using the aforementioned marks . when the device is in this position , the proximal part of the catheter 2 is situated in the heart , preferably in the left ventricle , while the aforementioned distal lateral openings are placed in a peripheral arterial vessel , preferably in the ascending aorta . the balloons 13 and 35 are inflated in such a way as to cause blood to flow only through the passage 15 and prevent blood reflux during the ablation of the valve 55 . a peripheral perfusion system is set in place to facilitate this flow , as further described below in connection with fig5 through 52 . the blades 30 of the two series 11 , 12 are then deployed ( fig6 ) by inflating the balloons 31 , then these two series 11 , 12 are moved closer together by sliding the tube 6 with respect to the tube 7 , until the valve 55 is cut through ( fig7 ). the blades 30 are then returned to their furled position by deflating the balloons 31 while at the same time remaining in their close - together position , which allows the cut - out valve 55 to be held between them . the device 1 is then slid axially in the distal direction so as to bring the bell housing 6 a to the appropriate position in the vessel 50 ( fig8 ), after which the valve 10 is deployed by sliding the tube 6 with respect to the tube 5 ( fig9 ). the balloons 13 and 35 are deflated then the device 1 is withdrawn and the cut - out valve 55 is recovered ( fig1 ). fig1 shows a second embodiment of the device 1 , allowing operation on a mitral valve 56 . the same reference numerals are used to denote the same elements or parts as the aforementioned , as long as these elements or parts are identical or similar in both embodiments . in this case , the tubular catheter is replaced by a support wire 2 , on which one of the series of blades is mounted and by a tube engaged over and able to slide along this wire , on which tube the other series of blades is mounted ; the passages for inflating the balloons 31 run along this support wire and this tube ; the balloon 13 and the filter 14 are separate from the device 1 and are introduced into the aorta via a peripheral arterial route , by means of a support wire 40 along which the passages for inflating the balloons 13 and 35 run . the device 1 , devoid of balloon 13 and the filter 14 , is for its part introduced into the heart through the peripheral venous system , as far as the right atrium then into the left atrium through the inter - auricular septum , as far as the valve 56 . for the remainder , the device 1 operates in the same way as was mentioned earlier . the invention thus provides a device for replacing a heart valve by a percutaneous route , making it possible to overcome the drawbacks of the prior techniques . indeed the device 1 is entirely satisfactory as regards the cutting - away of the valve 55 , 56 , making it possible to operate without stopping the heart and making it possible , by virtue of the filter 14 , to prevent tiny dispersion of valve fragments 55 , 56 into the circulatory system . the above device may comprise a fourth tube , engaged on and able to slide along the tube 7 , this fourth tube comprising the balloon and the filter mounted on it and allowing said series of blades to be moved in the axial direction independently of said balloon and / or of said filter ; the blades may be straight as depicted in the drawing or may be curved toward the axis of the device at their end which has the cutting edge , so as to eliminate any risk of lesion in the wall of the bodily vessel , as shown in fig1 ; the filter 14 may be of the self - expanding type and normally kept in the contracted position by a sliding tube , which covers it , making the balloon 35 unnecessary . fig1 to 16 represent tubular support 101 for positioning , by percutaneous route , of replacement heart valve 102 . the support structure 101 includes median portion 103 , which contains valve 102 , two extreme wedging portions 104 and wires 105 for connecting these portions 103 and 104 . median portion 103 also includes peripheral shell 106 provided with anchoring needles 107 and shell 108 made of compressible material . as is particularly apparent from fig1 , each of portions 103 and 104 is formed with an undulating wire , and wires 105 connect pointwise the ends of the undulations of portion 103 to the end of an adjacent wave of portion 104 . portions 104 , seen in expanded form , have lengths greater than the length of portion 103 , so that when the ends of the wires respectively forming portions 103 and 104 are connected in order to form the tubular support structure 101 , the diameter of portion 103 is smaller than the diameter of portions 104 . the diameter of portion 103 is such that portion 103 can , as shown by fig1 , support cardiac ring 110 that remains after removal of the deficient native valve , while portions 104 support walls 111 bordering ring 110 . these respective diameters are preferably such that said supporting operations take place with slight radial restraint of ring 110 and walls 111 . portion 103 presents in the deployed state a constant diameter . portions 104 can have a constant diameter in the form of a truncated cone whose diameter increases away from portion 103 . the entire support structure 101 can be made from a material with shape memory , such as the nickel - titanium alloy known as “ nitinol .” this material allows the structure to be contracted radially , as shown in fig1 , at a temperature different from that of the body of the patient and to regain the original shape shown in fig1 and 15 when its temperature approaches or reaches that of the body of the patient . the entire support structure 101 can also be made from a material that can be expanded using a balloon , such as from medical stainless steel ( steel 316 l ). valve 102 can be made of biological or synthetic tissue . it is connected to portion 103 by sutures or by any other appropriate means of attachment . it can also be molded on portion 103 . shell 106 may be made of “ nitinol .” it is connected to the undulations of portion 103 at mid - amplitude , and has needles 107 at the sire of its regions connected to these undulations . needles 107 consist of strands of metallic wire pointed at their free ends , which project radially towards the exterior of shell 106 . this shell can take on the undulating form that can be seen in fig1 in the contacted state of support 101 and the circular form which can be seen in fig4 in the deployed state of this support 101 . in its undulating form , shell 106 forms undulations 106 a projecting radially on the outside of support 101 , beyond needles 107 , so that these needles 107 , in the retracted position , do not obstruct the introduction of support 101 in a catheter or , once support 101 has been introduced into the heart using this catheter , do not obstruct the deployment out of this support 1 . the return of shell 106 to its circular form brings needles 107 to a position of deployment , allowing them to be inserted in ring 110 in order to complete the anchoring of support 101 . shell 108 is attached on shell 106 . its compressible material allows it to absorb the surface irregularities that might exist at or near ring 110 and thus to ensure complex sealing of valve 102 . fig1 shows a support structure 101 having a single portion 104 connected to portion 103 by wires 105 . this portion 104 is formed by two undulating wires 114 connected together by wires 115 . fig1 shows a support structure 101 that has portion 103 and portion 104 connected by connecting wires 105 . these portions 103 and 104 have diamond - shaped mesh structures , these mesh parts being juxtaposed in the direction of the circumference of these portions and connected together at the site of two of their opposite angles in the direction of the circumference of these portions 103 and 104 . wires 105 are connected to these structures at the site of the region of junction of two consecutive mesh parts . these mesh parts also have anchoring hooks 107 extending through them from one of their angles situated in the longitudinal direction of support 101 . fig2 illustrates , in an enlarged scale , the structure of this portion 104 and of a part of wires 105 , as cut , for example , with a laser from a cylinder of stainless steel , and after bending of sharp ends 107 a of hooks 107 . these hooks , in a profile view , can have the shape as shown in fig2 or 26 . the structure represented in fig1 also has axial holding portion 120 , which has a structure identical to that of portion 104 but with a coarser mesh size , and three wires 105 of significant length connecting this portion 120 to portion 103 . those wises 105 , on the side of portion 120 , have a single link 105 a and on the side of portion 103 , a double link 105 b . their number corresponds to the three junctions formed by the three valves of valve 102 , which facilitates mounting of valve 102 on support 101 thus formed . the support according to fig1 is intended to be used , as appears in fig2 , when the body passage with the valve to be replaced , in particular the aorta , has a variation in diameter at the approach to the valve . the length of wires 105 connecting portions 103 and 120 is provided so that after implantation , portion 120 is situated in a non - dilated region of said body passage , and this portion 120 is provided so as to engage the wall of the passage . fig2 shows a structure similar to that of fig1 but unexpanded , except that the three wires 105 have a single wire structure but have an undulating wire 121 ensuring additional support near portion 103 . this wire 121 is designed to support valve 102 with three valve leaflets . fig2 to 26 show an embodiment variant of the structure of portions 103 , 104 or 120 , when this structure is equipped with hooks 107 . in this case , the structure has a zigzagged form , and each hook 107 has two arms 107 b ; each of these arms 107 b is connected to the other arm 107 b at one end and to an arm of structure 101 at its other end . the region of junction of the two arms 107 b has bent hooking pin 107 a . fig2 shows portion 103 that has two undulating wires 125 , 126 extending in the vicinity of one another and secondary undulating wire 127 . as represented in fig2 , wires 125 , 126 can be used to execute the insertion of valve 102 made of biological material between them and the attachment of this valve 102 to them by means of sutures 127 . fig2 shows a part of support 101 according to fig1 to 17 and the way in which the compressible material constituting shell 108 can absorb the surface irregularities possibly existing at or near ring 110 , which result from calcifications . fig3 shows support 101 whose shell 106 has no compressible shell . a material can then be applied , by means of an appropriate cannula ( not represented ), between ring 110 and this shell 106 , this material being able to solidify after a predetermined delay following application . fig3 shows support 101 whose shell 106 has a cross section in the form of a broken line , delimiting , on the exterior radial side , a lower shoulder . housed in the step formed by this shoulder and the adjacent circumferential wall is peripheral shell 108 which can be inflated by means of a catheter ( not represented ). this shell 108 delimits a chamber and has a radially expandable structure , such that it has in cross section , in the inflated state , two widened ends projecting on both sides of shell 106 . this chamber can receive an inflating fluid that can solidify in a predetermined delay following its introduction into said chamber . once this material has solidified , the inflating catheter is cut off . fig3 and 33 show support 101 whose shell 106 receives inflatable insert 108 which has a spool - shaped cross section in the inflated state ; this insert 108 can be inflated by means of catheter 129 . insert 108 is positioned in the uninflated state ( fig3 ) at the sites in which a space exists between shell 106 and existing cardiac ring 110 . its spool shape allows this insert ( cf . fig3 ) to conform as much as possible to the adjacent irregular structures and to ensure a better seal . fig3 shows balloon 130 making it possible to deploy support 101 according to fig1 to 21 . this balloon 130 has cylindrical portion 131 whose diameter in the inflated state makes possible the expansion of holding portion 120 , a cylindrical portion 132 of lesser diameter , suitable for producing the expansion of portion 103 , and portion 133 in the form of a truncated cone , makes possible the expansion of portion 104 . as shown by fig3 , portion 132 can be limited to what is strictly necessary for deploying portion 103 , which makes it possible to produce balloon 130 in two parts instead of a single part , thus limiting the volume of this balloon 130 . fig3 shows support 101 whose median portion 103 is in two parts 103 a , 103 b . part 103 a is made of undulating wire with large - amplitude undulations , in order to support valve 102 , and part 103 b , adjacent to said part 103 a and connected to it by bridges 135 , is made of undulating wire with small - amplitude undulations . due to its structure , this part 103 b presents a relatively high radial force of expansion and is intended to be placed opposite ring 110 in order to push back the native valve sheets which are naturally calcified , thickened and indurated , or the residues of the valve sheets after valve resection against or into the wall of the passage . this axial portion 103 a , 103 b thus eliminates the problem induced by these sheets or residual sheets at the time of positioning of valve 102 . it is apparent from the preceding that one embodiment of the invention provides a tubular support for positioning , by percutaneous route , of a replacement heart valve , which provides , due to its portions 103 and 104 , complete certitude as to its maintenance of position after implantation . this support also makes possible a complete sealing of the replacement valve , even in case of a cardiac ring with a surface that is to varying degrees irregular and / or calcified , and its position can be adapted and / or corrected as necessary at the time of implantation . referring to fig3 and 38 , the present invention also comprises an alternative prosthetic valve assembly 310 , which further comprises a prosthetic valve 312 , a valve support band 314 , distal anchor 316 , and a proximal anchor 318 . valve 312 can be made from a biological material , such as one originating from an animal or human , or from a synthetic material , such as a polymer . depending upon the native valve to be replaced , the prosthetic valve 312 comprises an annulus 322 , a plurality of leaflets 324 and a plurality of commissure points 326 . the leaflets 324 permit the flow of blood through the valve 312 in only one direction . in the preferred embodiment , the valve annulus 322 and the commissure points 326 are all entirely supported within the central support band 314 . valve 312 is attached to the valve support band 314 with a plurality of sutures 328 , which can be a biologically compatible thread . the valve could also be supported on band 314 with adhesive , such as cyanoacrylate . in one embodiment , valve 312 can be attached to , or may integral with , a sleeve or sheath 313 . the sheath is secured to the valve support band 314 such that the outer surface of the sheath is substantially in contact with the inner surface of the valve support band 314 . in such embodiment , the sheath can be attached to the valve support band 314 with sutures 328 . fig4 is a schematic of the concept of this alternative embodiment . if desired , the sheath 313 can be secured to the outside of valve support band 314 ( not shown ). referring to fig3 and 38 , in one embodiment , valve support band 314 is made from a single wire 342 configured in a zigzag manner to form a cylinder . alternatively , valve support band 314 can be made from a plurality of wires 342 attached to one another . in either case , the band may comprise one or more tiers , each of which may comprise one or more wires arranged in a zigzag manner , for structural stability or manufacturing ease , or as anatomical constraints may dictate . if desired , even where the central valve support 314 is manufactured having more than one tier , the entire valve support 314 may comprise a single wire . wire 342 can be made from , for example , stainless steel , silver , tantalum , gold , titanium or any suitable plastic material . valve support band 314 may comprise a plurality of loops 344 at opposing ends to permit attachment to valve support band 314 of anchors 316 and / or 318 with a link . loops 344 can be formed by twisting or bending the wire 342 into a circular shape . alternatively , valve support band 314 and loops 344 can be formed from a single wire 342 bent in a zigzag manner , and twisted or bent into a circular shape at each bend . the links can be made from , for example , stainless steel , silver , tantalum , gold , titanium , any suitable plastic material , solder , thread , or suture . the ends of wire 342 can be joined together by any suitable method , including welding , gluing or crimping . still referring to fig3 and 38 , in one embodiment , distal anchor 316 and proximal anchor 318 each comprise a discrete expandable band made from one or more wires 342 bent in a zigzag manner similar to the central band . distal anchor band 316 and proximal anchor band 318 may comprise a plurality of loops 344 located at an end of wire 342 so that distal anchor band 316 and proximal anchor band 318 can each be attached to valve support band 314 with a link . loop 344 can be formed by twisting or bending the wire 342 into a circular shape . as desired , distal and / or proximal anchors 316 , 318 may comprise one or more tiers , as explained before with the valve support 314 . likewise , each anchor may comprise one or more wires , regardless of the number of tiers . as explained above in regard to other embodiments , the distal anchor may be attached to the central valve support band 314 directly , as in fig3 , or spaced distally from the distal end of the valve support 314 , as shown above schematically in fig1 , 19 , 21 and 22 . in the later instance , one or more struts may be used to link the distal anchor band to the valve support band , as described above . distal anchor band 316 has a first end 350 attached to the central valve band 314 , and a second end 352 . similarly , proximal anchor band 318 has first attached end 354 and a second end 356 . the unattached ends 352 , 356 of the anchors 316 , 318 , respectively are free to expand in a flared manner to conform to the local anatomy . in such embodiment , the distal and proximal anchor bands 316 , 318 are configured to exert sufficient radial force against the inside wall of a vessel in which it can be inserted . applying such radial forces provides mechanical fixation of the prosthetic valve assembly 310 , reducing migration of the prosthetic valve assembly 310 once deployed . it is contemplated , however , that the radial forces exerted by the valve support 314 may be sufficient to resist more than a minimal amount of migration , thus avoiding the need for any type of anchor . in an alternative embodiment , distal and proximal anchors may comprise a fixation device , including barbs , hooks , or pins ( not shown ). such devices may alternatively or in addition be placed on the valve support 314 . if so desired , the prosthetic valve assembly 310 may comprise an adhesive on the exterior thereof to adhere to the internal anatomical lumen . prosthetic valve assembly 310 is compressible about its center axis such that its diameter may be decreased from an expanded position to a compressed position . when placed into the compressed position , valve assembly 310 may be loaded onto a catheter and transluminally delivered to a desired location within a body , such as a blood vessel , or a detective , native heart valve . once properly positioned within the body the valve assembly 310 can be deployed from the compressed position to the expanded position . fig3 is a schematic of one embodiment of the prosthetic valve assembly described with both distal and proximal anchor bands 316 , 318 while fig4 is a schematic showing only a distal anchor 316 . in the preferred embodiment , the prosthetic valve assembly 310 is made of self - expanding material , such as nitinol . in an alternative embodiment , the valve assembly 310 requires active expansion to deploy it into place . active expansion may be provided by an expansion device such as a balloon . as referred to above in association with other embodiments , the prosthetic valve assembly of the present invention is intended to be percutaneously inserted and deployed using a catheter assembly . referring to fig4 a , the catheter assembly 510 comprises an outer sheath 512 , an elongate pusher tube 514 , and a central tube 518 , each of which are concentrically aligned and permit relative movement with respect to each other . at a distal end of the pusher tube 514 is a pusher tip 520 and one or more deployment hooks 522 for retaining the prosthesis assembly ( not shown ). the pusher tip 520 is sufficiently large so that a contracted prosthesis assembly engages the pusher tip 520 in a frictional fit arrangement . advancement of the pusher tube 514 ( within the outer sheath 512 ) in a distal direction serves to advance the prosthesis relative to the outer sheath 512 for deployment purposes . at a distal end of the central tube 518 is an atraumatic tip 524 for facilitating the advancement of the catheter assembly 510 through the patient &# 39 ; s skin and vasculature . the central tube 518 comprises a central lumen ( shown in phantom ) that can accommodate a guide wire 528 . in one embodiment , the central lumen is sufficiently large to accommodate a guide wire 528 that is 0 . 038 inch in diameter . the guide wire can slide through the total length of the catheter form tip to handle (‘ over the wire ’ catheter ) or the outer sheath 512 can be conformed so as to allow for the guide wire to leave the catheter before reaching its proximal end (‘ rapid exchange ’ catheter ). the space between the pusher tube 514 and the outer sheath 512 forms a space within which a prosthetic valve assembly may be mounted . hooks 522 on the distal end of the pusher tube 514 may be configured in any desired arrangement , depending upon the specific features of the prosthetic assembly . with regard to the prosthesis assembly of fig3 and 38 , the hooks 522 preferably comprise an l - shaped arrangement to retain the prosthesis assembly axially , but not radially . with a self - expanding assembly , as the prosthesis assembly is advanced distally beyond the distal end of the outer sheath 512 , the exposed portions of the prosthesis assembly expand while the hooks 522 still retain the portion of the prosthesis still housed within the outer sheath 512 . when the entire prosthesis assembly is advanced beyond the distal end of the outer sheath , the entire prosthesis assembly is permitted to expand , releasing the assembly from the hooks . fig4 through 45 show the distal end of one embodiment of the catheter assembly , three of which show sequenced deployment of a valve prosthesis . fig4 shows an alternative embodiment of the valve prosthesis , where loop elements extend axially from one end of the prosthesis and are retained by the hooks 522 on pusher tube 514 during deployment . fig4 and 47 show a catheter assembly used for deploying the alternative prosthesis assembly of fig4 . by adding loop elements to the prosthesis , the prosthesis may be positioned with its support and anchors fully expanded in place while permitting axial adjustment into final placement before releasing the prosthesis entirely from the catheter . referring to fig5 , an alternative embodiment of a self - expanding valve prosthesis and delivery system comprises loop elements 694 on prosthetic assembly 310 retained by disks 696 on pusher tube 514 by outer sheath 512 . when outer sheath 512 is pulled back to expose disks 696 , self - expanding loop elements 694 are then released from pusher tube 514 . fig4 b shows the proximal end of the catheter assembly 510 that , to a greater extent , has many conventional features . at the distal end of the pusher tube 514 is a plunger 530 for advancing and retreating the pusher tube 514 as deployment of the prosthesis assembly is desired . as desired , valves and flush ports proximal and distal to the valve prosthesis may be provided to permit effective and safe utilization of the catheter assembly 510 to deploy a prosthesis assembly . in one embodiment , prosthetic valve assembly 310 ( not shown ) is mounted onto catheter 510 so that the valve assembly 310 may be delivered to a desired location inside of a body . in such embodiment , prosthetic valve assembly 310 is placed around pusher tip 520 and compressed radially around the tip 520 . the distal end of prosthetic valve assembly 310 is positioned on the hooks 522 . while in the compressed position , outer sheath 512 is slid toward the atraumatic tip 524 until it substantially covers prosthetic valve assembly 310 . to deliver prosthetic valve assembly 310 to a desired location within the body , a guide wire 528 is inserted into a suitable lumen of the body , such as the femoral artery or vein to the right atrium , then to the left atrium through a transseptal approach , and maneuvered , utilizing conventional techniques , until the distal end of the guide wire 528 reaches the desired location . the catheter assembly 510 is inserted into the body over the guide wire 528 to the desired position . atraumatic tip 524 facilitates advancement of the catheter assembly 510 into the body . once the desired location is reached , the outer sheath 512 is retracted permitting the valve prosthesis to be released from within the outer sheath 512 , and expand to conform to the anatomy . in this partially released state , the position of prosthetic valve 310 may be axially adjusted by moving catheter assembly 510 in the proximal or distal direction . it is apparent that the invention advantageously contemplates a prosthesis that may have a non - cylindrical shape , as shown in several earlier described embodiments including but not limited to fig2 , 37 - 40 , 49 and 59 . this non - cylindrical shape results from controlling the diameters at some portions of prosthetic valve assembly 310 . referring to fig5 a , yet another non - cylindrical prosthesis is shown . central support band 314 comprises a diameter - restrained portion of valve assembly 310 attached to distal and proximal anchors 316 , 318 , that comprise discrete self - expandable bands capable of expanding to a flared or frusta - conical configuration . anchors 316 , 318 further accentuate the non - cylindrical shape of central support band 314 . fig5 a shows one embodiment of the invention for limiting the diameter of portions of the valve assembly 310 from excessive expansion , whereby valve assembly 310 further comprises a radial restraint 690 to limit the diameter of central support band 314 . radial restraint , as used herein , shall mean any feature or process for providing a desired diameter or range of diameters , including but not limited to the selection of materials or configurations for valve assembly 310 such that it does not expand beyond a preset diameter . controlling radial expansion to a preset diameter at central support band 314 helps maintain the coaptivity of valve 312 and also preserves the patency of the coronary ostia by preventing central support band 314 from fully expanding to the lumen or chamber wall to cause occlusion . restraint 690 may be sufficiently flexible such that restraint 690 may contract radially with valve assembly 310 , yet in the expanded state resists stretching beyond a set limit by the radial expansion forces exerted by a self - expanding valve assembly 310 or from a balloon catheter applied to valve assembly 310 . referring to fig5 a and 56b , restraint 690 may take any of a variety of forms , including wires 700 of a specified length that join portions of central support band 314 , threads may also be used for radial restraint 690 . the slack or bends in the wires allow a limited radial expansion to a maximum diameter . once the slack is eliminated or the bends are straightened , further radial expansion is resisted by tension created in wires 700 . these wires may be soldered , welded or interwoven to valve assembly 310 . by changing the length of wire joining portions of valve assembly 310 , radial restraints of different maximum diameters are created . for example , by using short wires to form the radial restraint , the valve support structure may expand a shorter distance before tension forms in the short wires . if longer wires are used , the support structure may expand farther before tension develops in the longer wires . fig5 depicts central support band 314 with a radial restraint 700 of a smaller diameter and another portion of the same valve assembly 310 with longer lengths of wire 701 and allowing a larger maximum diameter . the portion of valve assembly 310 with the larger diameter can be advantageously used to allow greater dilation around cardiac ring 110 and native valve sheets . the degree of resistance to expansion or recollapse can be altered by changing the diameter of the radial restraint or by changing the configuration of the restraint . for example , a cross - linked radial restraint will have a greater resistance to both expansion and recollapse . referring to fig5 , restraint 690 may alternatively comprise a cuff 691 encompassing a circumference of central support band 314 that resists expansion of central support band 314 beyond the circumference formed by cuff 691 . cuff 691 may be made of eptfe or any other biocompatible and flexible polymer or material as is known to those skilled in the art . cuff 691 may be attached to valve assembly 310 by sutures 692 or adhesives . fig7 illustrates one embodiment of the invention where radial restraints are integrally formed as part of valve assembly 310 by using a laser cutting manufacturing process , herein incorporated by reference . fig7 a depicts a schematic view of a laser - cut portion of valve assembly 310 in the unexpanded state with several radial restraints 706 , 708 , 710 . each end of radial restraints 706 , 708 , 710 is integrally formed and attached to valve assembly 310 . an integrally formed radial restraint may be stronger and may have a lower failure rate compared to radial restraints that are sutured , welded or soldered to valve assembly 310 . fig7 b depicts a shorter radial restraint 706 along one circumference of valve assembly 310 . fig7 c depicts another portion of valve assembly 310 with a longer radial restraint 70 s and a cross - linked radial restraint 710 positioned along the same circumference . thus , the segments of a radial restraint along a given circumference need not have the same characteristics or size . another embodiment of the radial restraint comprises at least one protrusion extending from valve assembly 310 to provide a mechanical stop arrangement . the mechanical stop arrangement restricts radial expansion of valve assembly 310 by using the inverse relationship between the circumference of valve assembly 310 and the length of valve assembly 310 . as valve assembly 310 radially expands , the longitudinal length of valve assembly 310 may contract or compress as the diameter of valve assembly 310 increases , depending upon the particular structure or configuration used for valve assembly 310 . for example , fig3 , 38 , 56 a , 57 and 71 depict embodiments of the invention wherein valve assembly 310 comprises a diamond - shaped mesh . the segments of the mesh have a generally longitudinal alignment that reorient to a more circumferential alignment during radial expansion of valve assembly 310 . by limiting the distance to which valve assembly 310 can compress in a longitudinal direction , or by restricting the amount of angular reorientation of the wires of valve assembly 310 , radial expansion in turn may be controlled to a pre - set diameter . fig7 a shows one embodiment of the mechanical stop arrangement comprising an angular stop 730 and an abutting surface 732 on the wire structure of valve assembly 310 . a plurality of stops 730 and abutting surfaces 732 may be used along a circumference of valve assembly 310 to limit expansion to a preset diameter . angular stop 730 may be located between two adjoining portions of valve assembly 310 forming an angle that reduces with radial expansion . as shown in fig7 b , as valve assembly 310 radially expands , angular stop 730 will come in closer proximity to surface 732 and eventually abut against surface 732 to prevent further diameter expansion of valve assembly 310 . the angular size 734 of stop 730 can be changed to provide different expansion limits . the radial size 736 of stop 730 can also be changed to alter the strength of stop 730 . one skilled in the art will understand that many other configurations may be used for valve assembly 310 besides a diamond - shape configuration . for example , fig1 and 16 depict support 101 with an undulating wire stent configuration that exhibits minimal longitudinal shortening when expanding . the mechanical stop arrangements described above may be adapted by those skilled in the art to the undulating wire stent configuration , or any other stent configuration , for controlling the diameter of the support structure or valve assembly 310 . the particular method of maintaining the valve diameter within a preset range described previously relates to the general concept of controlling the expanded diameter of the prosthesis . the diameter attained by a portion of the prosthesis is a function of the radial inward forces and the radial expansion forces acting upon that portion of the prosthesis . a portion of the prosthesis will reach its final diameter when the net sum of these forces is equal to zero . thus , controlling the diameter of the prosthesis can be addressed by changing the radial expansion force , changing the radial inward forces , or a combination of both . changes to the radial expansion force generally occur in a diameter - related manner and can occur extrinsically or intrinsically . radial restraint 690 , cuff 691 and mechanical stop 730 of fig5 a , 58 and 74 a , respectively , are examples of extrinsic radial restraints that can limit or resist diameter changes of prosthetic valve assembly 310 once a preset diameter is reached . other ways to control diameter may act intrinsically by controlling the expansion force so that it does not expand beyond a preset diameter . this can be achieved by the use of the shape memory effect of certain metal alloys like nitinol . as previously mentioned , when a nitinol prosthesis is exposed to body heat , it will expand from a compressed diameter to its original diameter . as the nitinol prosthesis expands , it will exert a radial expansion force that decreases as the prosthesis expands closer to its original diameter , reaching a zero radial expansion force when its original diameter is reached . thus , use of a shape memory alloy such as nitinol is one way to provide an intrinsic radial restraint . a non - shape memory material that is elastically deformed during compression will exhibit similar diameter - dependent expansion forces when returning to its original shape . the other way of controlling diameter mentioned previously is to alter the radial inward or recoil forces acting upon the support or prosthesis . recoil forces refer to any radially inward force acting upon the valve assembly that prevents the valve support from maintaining a desired expanded diameter . recoil forces include but are not limited to radially inward forces exerted by the surrounding tissue and forces caused by elastic deformation of prosthetic valve assembly 310 . countering or reducing recoil forces help to ensure deployment of prosthetic valve assembly 310 to the desired diameter or diameter range , particularly at the native valve . for example , when the prosthetic valve assembly 310 of fig3 , 38 , 56 a , 57 and 58 is deployed , some recoil or diameter reduction may occur that can prevent portions of valve assembly 310 from achieving it pre - set or desired diameter . this recoil can be reduced by applying an expansion force , such as with a balloon , that stresses the material of valve assembly 310 beyond its yield point to cause plastic or permanent deformation , rather than elastic or transient deformation . similarly , balloon expansion can be used to further expand a self - expanded portion of valve assembly 310 where radially inward anatomical forces have reduced the desired diameter of that portion . balloon expansion of a self - expanded portion of valve assembly 310 beyond its yield point provides plastic deformation to a larger diameter . in addition to the use of a balloon catheter to deform valve assembly 310 beyond its yield point , other means for reducing recoil are contemplated . in the preferred embodiment of the invention , a separate stent may be expanded against cardiac ring 110 in addition or in place of valve assembly 310 . the separate stent may further push back the native valve sheets or residues of the resected valve and reduce the recoil force of these structures on valve assembly 310 . if the separate stent is deployed against cardiac ring 110 prior to deployment of valve assembly 310 , a higher radial force of expansion is exerted against ring 110 without adversely affecting the restrained radial force of expansion desired for the central support band 314 supporting valve 312 . alternatively , the separate stent may be deployed after valve assembly 310 and advantageously used to reduce the recoil of valve assembly 310 caused by the elastic deformation of the material used to form valve assembly 310 . the separate stent may be self - expanding or balloon - expandable , or a combination thereof . another means for addressing recoil involves providing the radial restraint and mechanical stop arrangements previously described with an additional feature that forms an interference fit when the valve assembly 310 is at its preset diameter . by forming an interference fit , the radial restraint or mechanical stop will resist both further expansion and recollapse from recoil . fig7 a through 73e depict an embodiment of a radial restraint with a recoil - resistant configuration integrally formed with valve assembly 310 . in this embodiment , each segment of the radial restraint comprises a pair of protrusions 712 having a proximal end 714 and a distal end 716 . proximal end 714 is integrally formed and attached to valve , assembly 310 while distal end 716 is unattached . each pair of protrusions 712 is configured so that distal end 716 of one protrusion 712 is in proximity to the proximal end 714 of other protrusion 712 in the unexpanded state , and where distal ends 716 come close together as valve assembly 310 radially expands . distal ends 716 comprise a plurality of teeth 718 for providing an interference fit between distal ends 716 upon contact with each other . the interference fit that is formed will resist both further radial expansion and collapse of valve assembly 310 . as mentioned earlier , collapse may result from the inherent elastic properties of the materials used for valve assembly 310 or from radially inward forces exerted by the tissue surrounding valve assembly 310 . the interference fit may be provided over a range of expansion , as depicted in fig7 b and 72c from the self - expanded state through the extra - expanded state . this allows the inference fit to act even when a self - expanded valve assembly 310 is further expanded by a balloon catheter to an extra - expanded state as the expansion diameter is further adjusted . the lengths of protrusions 712 will determine the amount of radial restraint provided . shorter protrusions 712 have distal ends 716 that contact each other after a shorter distance of radial expansion , while longer protrusions 712 will form an interference fit after a longer distance . fig7 a and 75b depict another embodiment of a radial restraint with a recoil resistant feature . angular stop 730 from fig7 a and 74b is provided with a notch 736 that forms an interference fit with a latch 738 protruding from valve assembly 310 adjacent to surface 732 . as valve assembly 310 expands , angular stop 730 will eventually abut against to surface 732 to prevent further expansion . latch 738 will also move closer to notch 736 as valve assembly 310 expands . when the preset diameter is reached , latch 738 forms an interference fit with notch 736 that resists collapse to a smaller diameter . it is contemplated that a balloon catheter may be used to expand valve assembly 310 to the desired diameter and to engage latch 738 to notch 736 . although both shape memory and non - shape memory based prostheses provide diameter - dependent expansion forces that reach zero upon attaining their original shapes , the degree of force exerted can be further modified by altering the thickness of the wire or structure used to configure the support or prosthesis . a prosthesis can be configured with thicker wires to provide a greater expansion force to resist , for example , greater radial inward forces located at the native valve site , but the greater expansion force will still reduce to zero upon the prosthesis attaining its preset diameter . changes to wire thickness need not occur uniformly throughout a support or prosthesis . wire thickness can vary between different circumferences of a support or prosthesis , or between straight portions and bends of the wire structure . as illustrated in fig5 , the decreased diameter 702 may be generally symmetrical about the longitudinal axis of the wire . alternatively , as in fig6 , the decreased diameter 704 may be asymmetrical , where the diameter reduction is greater along the lesser curvature of the wire bend or undulation relative to the longitudinal axis of the wire . at portions of the prosthesis where the exertion of a particular expansion force against surrounding tissue has importance over the actual diameter attained by that portion of the prosthesis , the various methods for controlling diameter can be adapted to provide the desired expansion force . these portions of the prosthesis may include areas used for anchoring and sealing such as the axial wedging portions or anchors previously described . referring to fig6 , a method for deploying the preferred embodiment of the invention using the separate stent is provided . the method of deployment comprises a guidewire 640 inserted via a venous approach 642 and passed from the right 644 to left atrium 646 through a known transseptal approach , herein incorporated by reference . after transseptal puncture , guidewire 640 is further directed from left atrium 646 past the mitral valve 648 to the left ventricle 650 and through the aortic valve 652 . an introducer ( not shown ) is inserted via an arterial approach and a snare ( not shown ), such as the amplatz goose neck ® snare ( microvena , mn ), is inserted through the introducer to grasp the distal end of guidewire 640 and externalize guidewire 640 out of the body through the introducer . with both ends of guidewire 640 external to the body , access to the implantation site is available from both the venous 642 and arterial approaches 654 . in fig6 , aortic valve 652 is pre - dilated by a balloon catheter 656 using a well - known valvuloplasty procedure , herein incorporated by reference . the prosthesis is then implanted as previously described by passing the delivery system from either the venous or arterial approaches . as illustrated in fig6 , the prosthesis 658 may be implanted using arterial approach 654 with prosthetic valve 658 implanted above the level of native valve 652 . as shown in fig6 , a balloon catheter 660 may be passed by venous approach 642 for further displacement of native valve 652 and / or to further secure the sower stent 662 to the annulus . hooks 664 , shown in fig6 , connecting the delivery catheter to prosthetic valve 658 allow full control of prosthetic valve 658 positioning until the operator chooses to fully release and implant prosthetic valve 658 . a separate stent may then be implanted by venous approach 642 at the valvular ring to further push back the native valve or valve remnants and reduce recoil forces from these structures . passing balloon 660 by the venous approach 642 avoids interference with superiorly located prosthetic valve 658 . implantation of replacement valve 658 by arterial approach 654 prior to the ablation of the native valve 652 or valve remnants by venous approach 642 may reduce the risks associated with massive aortic regurgitation when native valve 652 is pushed back prior to implantation of replacement valve 658 . reducing the risks of massive aortic regurgitation may provide the operator with additional time to position replacement valve 658 . it is further contemplated that in the preferred embodiment of the invention , valve assembly 310 also comprises a drug - eluting component well known in the art and herein incorporated by reference . the drug - eluting component may be a surface coating or a matrix system bonded to various portions of valve assembly 310 , including but not limited to central support band 314 , anchors 316 318 , valve 312 , loop elements 352 or wires 342 . the surface coating or matrix system may have a diffusion - type , erosive - type or reservoir - based drug release mechanism . drugs comprising the drug - eluting component may include antibiotics , cellular anti - proliferative and / or anti - thrombogenic drugs . drugs , as used herein , include but are not limited to any type of biologically therapeutic molecule . particular drugs may include but are not limited to actinomycin - d , batimistat , c - myc antisense , dexamethasone , heparin , paclitaxel , taxanes , sirolimus , tacrolimus and everolimus . as previously mentioned , one embodiment of the system for implanting the prosthesis and / or excising the native valve leaflets contemplates maintaining blood flow across the native valve site during the excision and implantation procedure . by maintaining blood flow across the native valve , use of extracorporeal circulation or peripheral aorto - venous heart assistance and their side effects may be reduced or avoided . major side effects of extracorporeal circulation and peripheral aorto - venous heart assistance include neurological deficits , increased bleeding and massive air emboli . fig5 through 52 depict one embodiment of the invention for maintaining blood perfusion during the procedure . this embodiment comprises a blood pump 600 and an opening 602 positioned in the wall of tubular catheter 2 of the excision system . when the tabular catheter 2 is positioned at the excision site , blood pump 600 allows continued blood flow across the excision site that would otherwise be interrupted during the excision procedure . blood pump 600 may comprise a motor , a shaft and an impeller . blood pump 600 is insertable through passage 15 of tubular catheter 2 . the motor is connected to a shaft 604 that in turn is coupled to an impeller 606 . the motor is capable of rotating shaft 604 , resulting in the rotation of impeller 606 . impeller 606 comprises a proximal end 608 , a distal end 610 and a plurality of fins 612 angled along the longitudinal axis of impeller 606 , such that when impeller 606 is rotated in one direction , fins 612 are capable of moving blood from a proximal to distal direction . when impeller 606 is rotated in the other direction , fins 612 are capable of moving blood in a distal to proximal direction . the ability to rotate impeller 606 in either direction allows but is not limited to the use of the blood pump in both anterograde and retrograde approaches to a heart valve . the blood pump is positioned generally about catheter opening 602 . the blood pump has an external diameter of about 4 - mm and the passage of the catheter has a 4 - mm internal diameter . catheter opening 602 has a longitudinal length of about 4 - mm . catheter opening 602 may comprise a plurality of openings located along a circumference of tubular catheter 2 . to reduce interruption of blood flow through tubular catheter 2 during the implantation portion of the procedure , catheter opening 602 should preferably be about 30 mm from the tip of catheter 2 or distal to the bell housing 6 a . this positioning of catheter opening 602 reduces the risk of occlusion of catheter opening 602 by the replacement valve . fig5 depicts an optional feature of blood pump 600 further comprising an impeller housing 614 having at least one proximal housing opening 616 and at least one distal housing opening 618 . housing 614 protects passage 15 of tubular catheter 2 from potential damage by rotating impeller 600 . proximal 616 and distal housing openings 618 provide inflow and outflow of blood from the impeller , depending on the rotation direction of impeller 600 . to reduce interruption of blood flow through catheter 2 during the implantation portion of the procedure , catheter opening 602 should preferably be at least a distance of about 30 mm from the distal tip of the catheter or about distal to the bell housing 6 a to avoid occlusion of catheter opening 602 by the replacement valve . fig5 and 54 depict an alternative embodiment , where blood pump 620 is located in a second catheter 622 in the prosthesis delivery system . once blood pump 620 and second catheter 622 are in position , the prosthesis delivery system 624 is slid over the separate catheter 622 to position the prosthesis for implantation , while avoiding blockage of blood flow in separate catheter 622 . in this embodiment , the diameter of the delivery system is preferably about 8 mm . one method of using the blood flow pump during the implantation of the prosthesis is now described . this procedure may be performed under fluoroscopy and / or transesophageal echocardiography . fig6 shows vascular access made through the axillary artery 666 . a guidewire 668 is inserted past the aortic valve 670 and into the left ventricle 672 . in fig6 , a blood pump 674 is inserted into a hollow catheter passed 676 over guidewire 668 inside the aorta 678 and pushed into left ventricle 672 . blood pump 674 is started to ensure a steady and sufficient blood flow of about 2 . 5 l / min from left ventricle 672 downstream during the valve replacement . fig6 depicts valve prosthesis 680 , retained on the delivery system 682 and positioned by sliding over blood pump catheter 676 . prosthesis 680 is positioned generally about the valve annulus 684 and the coronary ostia 686 , with the assistance of radiographic markers . as shown in fig6 and 70 , the sheath 688 overlying prosthesis 680 is pulled back and prosthesis 680 is deployed as previously described catheter hooks 690 connecting the delivery catheter to the prosthetic valve allow full control of prosthetic valve positioning until the operator chooses to fully release and implant the prosthetic valve . optional anchoring hooks , described previously , may be deployed generally about the annulus , the ventricle and the ascending aorta . deployment of the anchoring hooks may be enhanced by radial expansion of a balloon catheter that further engages the hooks into the surrounding structures . blood pump 674 is stopped and hood pump catheter 676 is removed . other configurations may be adapted for replacing a valve at other site will be familiar to those skilled in the art . the present invention may be embodied in other specific forms without departing from its spirit or essential characteristics . the described embodiments are to be considered in all respects only as illustrative , and not restrictive and the scope of the invention is , therefore , indicated by the appended claims rather than by the foregoing description . for all of the embodiments described above , the steps of the methods need not be performed sequentially . all changes that come within the meaning and range of equivalency of the claims are to be embraced within their scope .
a prosthetic heart valve comprises a biological tissue valve and a collapsible and expandable support frame having a longitudinal axis . the frame comprises an outflow circumferential structure defining an outflow end of the frame and consisting essentially row of diamond - shaded expandable cells . the frame also comprises three v - shaped structures spaced apart from the outflow circumferential structure and three struts longitudinally aligned with the longitudinal axis of the frame . the three struts are configured to facilitate mounting the biological tissue valve to the frame and interconnect the outflow circumferential structure to the three v - shaped structures . the frame also includes three undulating structures , each of the three undulating structures interconnecting respective adjacent v - shaped structures of the three v - shaped structures . the prosthetic heart valve is configured to be collapsed for introduction into a patient using ; a catheter and to be expanded for deployment at an implantation site .