in this description of illustrative examples , like reference numerals refer to like element throughout the drawings . like reference numerals with prime (′) marks or double prime (″) marks refer to like structure except for minor differences which will be apparent . fig1 a and 1b illustrate an improved catheter delivered fastener system 50 ′ which involves placing a permanent fastener or anchor 60 from the cs 46 through the wall of the left atrium 12 proximate annulus 40 for anchoring purposes . this improvement may be applied to the prior cinching method illustrated in fig . i discussed above . the fastener 60 may be deployed and anchored in various manners , including those discussed further below . because the fastener 60 extends not only through the delicate cs tissue , but also through the thicker tissue of the left atrium 12 , secured anchoring takes place and , upon cinching using a flexible tensile member 54 , the annulus 40 may be reduced to correct for a prolapsed valve or other mitral valve insufficiency with less risk of tearing tissue . fig2 a and 2b illustrate the anatomical relationship between the cs 46 and the mitral annulus 40 . in particular , the cs 46 can be noncoplanar with the mitral annulus 40 , causing cs based cinching approaches to the inefficient to effectively modify the shape of the annulus 40 . in many cases , the cs 46 extends above the mitral annulus 40 along the left atrial wall and , instead of pulling the annulus 40 toward the valve opening or gap 32 , the left atrial wall is instead pulled inwardly as shown in fig2 b . this causes more of a restriction of the atrium 12 above the valve 20 , rather than a reduction of the annulus 40 itself and , therefore , prevents a complete correction of the valve insufficiency in this case . in an approach which is similar to the approach shown in fig1 a and 1b , but having additional benefits , a fastener or anchor 62 extends from the cs 46 into the left ventricle side of the annulus 40 . this plicates the tissue between the cs 46 and the left ventricle 14 thereby bringing the cs 46 closer to and / or more in line with the annulus 40 . once this plication has taken place as shown in fig2 c , a cs cinching device can more efficiently and effectively reduce the mitral annulus 40 . that is , when cinched toward the valve opening or gap 32 , the cinching device , which is more in line with the valve annulus 40 , can better pull the posterior leaflet 24 toward the anterior leaflet 22 thereby closing the gap 32 between the leaflets . as shown in fig3 a and 3 b , a pair of magnetically attractive catheters 64 , 66 can be used in concert with each other using the cs 46 as an approximate guide to locate and position the tip of another catheter or catheter portion at the mitral annulus 40 . more specifically , as one example , one catheter 66 includes both a magnetic guiding portion 66 a and an anchor delivery portion 66 b positioned in a predetermined manner , such as at a predetermined acute angle relative to the magnetic portion 66 a . another catheter 64 is placed in the cs 46 and includes a magnetic guiding portion 64 a . the two magnetic guiding portions 64 a , 66 a magnetically couple with one another to lock up the position of the anchor delivery catheter portion 66 b at a predetermined angle which will properly deliver a fastener or anchor 68 into a desired portion of the tissue . as shown in fig3 a , the magnetically locked catheters 64 , 66 can deliver a first loop type anchor or fastener 68 through the valve annulus 40 on a skewed or otherwise known trajectory from the axis of magnetic attraction , such that the loop type anchor or fastener 68 is accurately placed , for example , through the annulus 40 from the left ventricle side to the left atrium side of the mitral valve 20 . as shown in fig3 b , the cs catheter 64 can be translated to a different position within the cs 46 causing the magnetic tip 66 a of the left ventricle catheter 66 to follow along the annulus 40 where subsequent loop type anchors or fasteners 68 may be placed in a similar fashion to the first applied anchor or fastener 68 . fig3 c illustrates that a loop type fastener or anchor 68 may capture a t - bar type anchor or fastener 70 passing from the cs 46 through the left atrial wall using a catheter delivery system 72 guided within the cs 46 . in this embodiment , fasteners 68 are therefore placed from the left ventricle 14 into the left atrium 12 , and additional connecting fasteners 70 are placed from the cs 46 into the left atrium 12 for engagement with the other fasteners 68 . as shown in fig3 d , multiple loop and t - bar anchors or fasteners 68 , 70 may be cinched together with a flexible tensile member 74 similar to a drawstring - type configuration , resulting in alignment of the cs 46 and the annulus 40 into a more coplanar relationship at several locations . the cinching or drawstring action therefore closes the gap 32 between the posterior leaflet 24 and the anterior leaflet 22 in a more even and effective manner . fig4 illustrates magnetically attractive catheter portions 64 a , 66 a respectively in the cs 46 and under the mitral annulus 40 used to deliver a series of anchors or fasteners 76 with a t - bar shape from the left ventricle side of the mitral valve 20 to the left atrium side of the mitral valve 20 . as also shown in fig4 , the t - bar shaped anchor fasteners 76 are delivered in a daisy chained fashion from catheter portion 66 b such that a second catheter 78 may be used to cinch a drawstring or flexible tensile member 80 to shorten or reduce the valve annulus 40 . as shown in fig5 , the anchors or fasteners 76 may be cinched together using the drawstring or flexible tensile member 80 within catheter 78 to pull the posterior leaflet 24 toward the anterior leaflet 22 . the flexible tensile member 80 is then locked in place or otherwise secured to retain the fasteners 76 in their new positions , such as in one of the manners described below . fig6 a - 6f respectively illustrate catheters 82 , 84 being placed into the heart 10 through the aortic valve into the left ventricle 14 and through the cs 46 generally adjacent the valve annulus 40 . this top view of the heart 10 shows how a first t - bar type anchor or fastener 86 having a tail , forming a flexible tensile member 88 , is loaded into the cs catheter 84 at the proximal end 84 a so that it may be pushed down to the distal tip 84 b to be in position for delivery . the position of the left ventrical catheter 82 with a magnetic tip 82 a is also shown generally opposite to the distal tip 84 b of the cs catheter 84 . as shown in fig6 b , a second anchor or fastener 90 is delivered in a daisy chain fashion by running an eyelet 90 a on the second anchor 90 over the tail or flexible tensile member 88 associated with the first anchor 86 . fig6 c illustrates the second anchor 90 of the daisy chain delivered through the valve annulus 40 at a spaced apart location from the first anchor 86 . fig6 d illustrates a third anchor 92 at the annulus 40 similarly delivered along flexible tensile member 88 using an eyelet portion 92 a . anchor 92 is threaded through the cs catheter 84 and driven through the tissue generally at the valve annulus 40 . in the case of this type of anchor , respective transverse bar portions 86 b , 90 b , 92 b of the anchors or fasteners extend into the left ventricle 14 . fig6 e illustrates a locking member 94 , including a crimp 96 delivered over the daisy chain tail or flexible tensile member 88 within the proximal cs 46 . locking member 94 is shaped or otherwise configured to hold its position within the cs 46 . fig6 e - 1 illustrates the crimp 96 before crimping onto the flexible tensile member or tail 88 . as shown in fig6 f and 6 f - 1 a catheter device 98 , which may be deployed through a suitable delivery catheter ( not shown ) may be used to pull the flexible tensile member 88 thereby cinching the assembly and pulling the posterior leaflet 24 toward to the anterior leaflet 22 . once this cinching is accomplished , the crimp is crimped against the flexible tensile member 88 adjacent to the lock member 94 to keep the assembly at the desired position . fig7 a illustrates how magnetically attractive portions 82 a , 84 b of the lv and cs catheters 82 , 84 should be strongly attracted when the gap distance ( d 1 ) is relatively short . if this gap distance d 1 is not relatively short , then other methods of increasing the lock up force may be necessary as further described herein below . fig7 b and 7c illustrate how a t - bar type anchor or fastener 86 would be pushed from an opening 84 c in the cs catheter through the tissue from the cs 46 into the left ventricle 14 until it is fully deployed across the tissue . fig7 d illustrates a larger gap d 2 , through which two magnetic portions 82 a , 84 b of the respective lv and cs catheters may magnetically couple , depending on the magnetic attractive forces developed . in fig7 e and 7f , the magnetic catheter in the lv 14 has not been illustrated ( only for purposes of clarity ), such that the delivery of a t - bar type fastener or anchor 86 may be shown in its fully deployed state across the tissue . as shown in fig7 f , the t - bar portion or transverse portion 86 b of the fastener 86 self - rotates in order to fit snugly along the annulus 40 under the posterior leaflet 24 . in fig7 g , the relative position of the cs 46 to the annulus 40 is improved after cinching of the anchor 86 plicates the tissue between the annulus 40 and the cs 46 as previously described . fig8 a - 8c illustrate that multiple magnets 102 a , 102 b may be used in the cs , such as on a cs catheter 102 , to attract an opposite magnet pole at the tip 100 a of the lv catheter 100 . this allows the lv catheter 100 to be steered in three axes to deliver a fastener through a second catheter portion 100 b into the annulus 40 . it will be appreciated that multiple magnets may also or alternatively be used in the lv 14 and / or in the la for steering purposes and / or additional magnetic force . fig8 c illustrates in detail how a pair of magnets 102 a , 102 b in the cs 46 mounted such that like poles are facing each other results in a 360 ° magnetic field which attracts the opposite pole of a magnetic catheter tip 100 a within the lv 14 . this can eliminate the need to rotationally orient the cs catheter 102 so that its pole is facing an opposite pole in the lv 14 . fig9 illustrates the use of electromagnets 104 in a cs catheter 106 which may be used in conjunction with or as replacements for permanent magnets as described in the above embodiments . it will also be appreciated that one element which generates magnetic forces may be used in conjunction with another element which is magnetically attracted to the magnetic force generating element , but not necessarily a magnetic force generating element itself . for example , an electromagnet or permanent magnet may be positioned on one side of the tissue to be anchored , and another element formed from ferrous metal may be positioned on the opposite side of the tissue for magnetic coupling purposes while a fastener or anchor is driven into the tissue . fig1 illustrates a cs catheter 108 configured with multiple opposite pole magnetic pairs 110 , 112 along its length and a steerable lv catheter that may be directed to each discrete pair of magnets 110 , 112 to delivery anchors or fasteners ( not shown ), such as in one of the manners previously described . now referring to fig1 a , 11 a - 1 , 11 b and 11 b - 1 , a cs catheter 116 may be configured with multiple discrete magnets 118 along its length , wherein the poles of the magnets 118 are arranged such that they are magnetically attracted to each other , yet kept apart by a restraining force , such as pressurized air directed to a bladder - like structure 120 between the magnets 118 . in this case , the magnets 118 are being used as fasteners to fasten or trap tissue therebetween . a similar catheter 122 delivers magnets 124 on an opposite side of the tissue , such as within the lv 14 . when the restraining force is removed , such as by reducing the air pressure as shown in fig1 b and 11 b - 1 , the magnets 118 are attracted to each other and thereby modify the valve annulus 40 such that the posterior leaflet 24 is pulled toward the anterior leaflet 22 . as shown best in fig1 b and 11c , each strip of magnets 118 , 124 has opposing poles along its length and thereby plicates the tissue by removing a restraining force between the magnets 118 in the cs 46 , thereby allowing the attracted magnets 118 to move toward each other and plicate the annulus tissue therebetween . the magnets 124 in the lv catheter 122 may be configured in the same manner as magnets 118 . fig1 a and 12b illustrate respective strips of magnets 118 , 124 , as described in connection with fig1 a - 11c in the cs 46 and the la 12 instead of the lv 14 . the two strips of respective magnets 118 , 124 align with each other such that the magnets 118 , 124 are anchored to each other across the left atrial wall . in this case , once again , the stronger atrial wall is used as the anchoring tissue , as opposed to the cs tissue only . when the magnets 118 in the cs 46 are brought together , as discussed above , an annular reduction of the mitral annulus 40 is achieved similar to the manner discussed above . fig1 a and 13b illustrate strips of magnets 118 , 124 in the cs 46 and la 12 as discussed previously . however , cinching via the cs 46 alone may not have sufficiently precise pull on the mitral annulus 40 since these two anatomical structures typically do not lie at the same level . even the two strips of magnets 118 , 124 shown in fig1 b are only coupled across the left atrial wall , and this may not be in line with the annulus 40 at all locations . therefore , an additional magnet 126 shown in fig1 a and 13b , fixed to a metal or otherwise substantially rigid curved bar 128 , is placed under the mitral valve 20 in the lv 14 , such that magnet 126 locks up with the strip of magnets 118 in the cs 46 . this pulls the exterior annulus 40 toward the cs 46 and establishes a more coplanar relationship . fig1 a illustrates a modification of the strip of magnets 124 positioned in the la 12 such that there is an extension magnet 130 which is positioned at the midpoint of the strip of magnets 124 . this extension magnet 130 extends down to the mitral valve annulus 40 bridging the gap between the cs 46 and the valve annulus 40 . this may pull a magnet 132 and curved support bar 134 under the valve 20 tighter to the cs 46 , as shown in fig1 b . it will be appreciated that magnet 132 and support bar 134 are similar to magnet 126 and support bar 128 , except that bar 134 has a fabric covering 136 as may be desired for tissue ingrowth purposes . fig1 c - 14e illustrate the use of additional mechanical fasteners such as projections 138 on one or more of the magnets 132 used in the embodiments described above . this can apply additional traction or fastening to the tissue than could otherwise be supplied by the use of magnets alone . fig1 a - 15e comprise a series of illustrations showing another alternative catheter based fastener delivery system . in addition to showing the use of a fastener 140 to pull the cs 46 into a more coplanar relationship with the annulus 40 ( fig1 c ), this system utilizes magnets 142 , 144 which have orifices 142 a , 144 a through which the fastener 140 is delivered such that more precise placement of the fastener 140 may be obtained in certain instances while also using a magnetic lock up force for more positively driving the anchor or fastener 140 . it will be appreciated that magnet 144 will be coupled to a catheter ( not shown ) for positioning within the cs 46 . magnet 142 may be releasably coupled to a steerable catheter 146 . as shown in fig1 d and 15e , after a plurality of magnets 142 , 144 and fasteners 140 have been delivered such that tissue is trapped therebetween , a flexible tensile member 148 and crimps 150 may be used to cinch and lock the fasteners 140 together thereby pulling the posterior leaflet 24 toward the anterior leaflet 22 and closing a gap 32 in the valve 20 . fig1 a - 16e , as well as fig1 a - 1 and 16 a - 2 illustrate a system which is the same as the system shown in fig1 a - 15e , except that the magnets 142 ′, 144 ′ are formed of separable portions , such as halves 142 a , 142 b , 144 a , 144 b , so that the magnets 142 ′, 144 ′ may be removed after the fasteners 140 ′ have been properly delivered . thus , the anchors or fasteners 140 ′ themselves have portions 140 a , 140 b which retain the fasteners 140 ′ in place across the tissue proximate the annulus 40 , and portions 140 b accept a flexible tensile member 148 and crimps 150 for cinching and locking purposes as shown in fig1 d and 16e generally in the manner or manners described herein . the separable magnet portions 142 a , 142 b and 144 a , 144 b may be coupled to suitable catheter devices allowing their release from fasteners 140 ′ and withdrawal from the patient . fig1 a illustrates an alternative fastener delivery system 160 using magnetic guidance in which the fastener 140 ′ is not delivered through the magnets 162 , 164 , but is delivered adjacent to the magnets 162 , 164 in a fastener driving portion 166 of a catheter 168 . this is another manner of using magnetic guidance and temporary lock up without the necessity of leaving the magnets 162 , 164 in place after completion of the procedure . fig1 a - 18c illustrate a more conventional annuloplasty that may be accomplished using magnetic guidance and lock up in a temporary manner to facilitate fastener placement and driving . more specifically , a magnetic strip 170 is placed into the cs 46 using a catheter 172 . a second magnetic strip 174 with a fabric covering 176 is placed in the left atrium 12 also via a catheter 178 . fasteners 180 are placed into the fabric 176 on the strip 174 in the left atrium 12 from the undersurface of the mitral valve 20 again using a catheter 82 . likewise , fasteners 180 are driven through the cs 46 and left atrium wall into the fabric 176 in a manner similar to that described with respect to , for example , fig3 c and 3d through a catheter with a sideward firing fastener driving portion ( see also fig7 d - 7f ). the magnetic strips 170 , 174 are removed from the fabric covering 176 and from the cs 46 and the fabric 176 is then drawstringed or cinched with a suitable flexible tensile member 184 coupled therewith to produce annuloplasty or pulling of the posterior leaflet 24 toward the anterior leaflet 22 to eliminate or reduce a gap 32 in the mitral valve 20 . fig1 a - 19c illustrate one alternative to a t - bar configuration of fasteners as previously described . in this embodiment , fasteners 190 in the form of anchor buttons 190 a are placed below the mitral valve 20 along the annulus 40 using catheters 192 , 194 with magnetic guidance and lock up as previously described . although not shown , another catheter is used in the left atrium to deliver buttons 190 b which couple with buttons 190 a . buttons 190 a are further coupled to a flexible tensile member 196 which may be secured with crimps 200 ( one shown in fig1 c ) as previously described . this compresses the mitral tissue between respective tissue engaging portions of the buttons 190 a , 190 b . the buttons 190 a , 190 b are drawstringed or cinched from below using flexible tensile member 196 threaded through respective eyelet portions 198 of each button 190 a . fig2 a and 20b illustrate another way to plicate the annulus 40 by using memory alloy staples 202 driven into the tissue along the annulus 40 . when the memory alloy activates , the staples 202 shorten and plicate the tissue ( fig2 ) to shorten the annulus 40 of the mitral valve 20 to pull the posterior leaflet toward the anterior leaflet as generally described above . fig2 a - 21d illustrate the placement of fasteners 210 on the left atrial side of the mitral valve 20 , daisy chained to pledgets or fasteners 212 in the form of tissue trapping load spreading members underneath the annulus 40 . these fasteners 210 , 212 are coupled together by a flexible tensile member 214 or drawstring , in this case . fig2 a - 21c illustrate a catheter 216 which delivers fasteners 210 , 212 in a serial fashion along flexible tensile member 214 such that fasteners 210 are driven through the tissue and fasteners or pledgets 212 are released between each fastener 210 . the series of fasteners 210 , 212 is then drawn together using the drawstring or flexible tensile member 214 as shown in fig2 d . this shortens the distance between each of the fasteners 210 , 212 and the entire structure with elements above and below the annulus 40 . the tissue becomes trapped between the fasteners 210 , 212 spreading loads over larger areas and reducing tear out risks . fig2 illustrates a modified version of the system illustrated in fig2 a - 21d . in this embodiment , after the first drawstring 214 is pulled to tighten the various fasteners 210 , 212 ′ and plicate the annulus 40 as generally shown in fig2 d , a second drawstring 218 coupled to eyelets 220 each of the pledgets 212 ′ may be pulled for a secondary shortening operation which further reduces the annulus 40 , as necessary . fig2 a - 23e illustrate an alternative embodiment which is similar to fig2 a - 21d , except that the pledgets 212 ″ have a pair of holes 222 , 224 through which the flexible tensile member 214 or drawstring is threaded , as opposed to an eyelet structure . fig2 a - 24c illustrate another embodiment of a catheter based fastener system 230 which employs a series of connected magnets 232 , 234 with one series of magnets 232 lying in the cs 46 lying adjacent to the mitral valve annulus 40 and another series 234 lying in the lv 14 adjacent to the annulus 40 . the magnets 232 residing in the cs 46 are coupled together by coil springs 236 and by a flexible tensile member 238 , while the magnets 234 in the lv 14 are , in one embodiment , positioned individually in the lv adjacent to magnets in the cs 232 , after release from the lv magnet delivery catheter 240 , as shown in fig2 c . in another embodiment , the array of lv magnets 234 is shown in fig2 a adjacent to the cs magnets 232 and connected by a member consisting of a sheath 233 upon which the magnets 234 can slide . the array of magnets 234 and the sheath 233 are deposited in the lv 14 as the delivery catheter 240 is withdrawn . the connecting sheath 233 prevents the risk of an embolic accident resulting from a detachment of a single magnet 234 . in fig2 b , the withdrawal of the lv delivery catheter 240 is shown in more detail . the most distal magnet 234 is shown attached to the sheath 233 , whereas the next more proximal magnet 234 is still on the shaft of the delivery catheter 240 . each series of magnets 232 , 234 is introduced into the positions shown in fig2 a - 24c by respective catheters 242 , 240 . a coupling 244 is provided and is releasably coupled to a pull wire or cable 246 in the catheter 242 such that the series of magnets 232 may be cinched or drawn together to reduce the circumferential length of the valve annulus 40 . the lv magnets 234 , owing to their attraction to their cs counterparts 232 , are thus pulled together to accomplish plication of the dorsal cusp of the mitral valve 20 adjacent to the annulus 40 . plication may be better facilitated by features on the surface of the cs magnets 232 which grip the endocardial surface , and promote ultimate tissue ingrowth about the magnets 232 to strengthen the plication . once the reduction has taken place , the magnets 232 are locked in place , and the catheter 242 is removed . referring more specifically to fig2 a - 25d , the operation of the coupling 244 , and a release and locking mechanism 250 is shown . the initial position is shown in fig2 a in which the magnets 232 are spaced apart by the uncompressed coil springs 236 and the flexible tensile member 238 which is fixed to a coupling element 252 having at least a pair of arms 254 , 256 which releasably grip a complimentary coupling element 258 . the complimentary coupling element 258 is fixed to a pull wire or cable 260 extending within the delivery catheter 242 . the wire or cable 260 is pulled as shown in fig2 b to compress the coil springs 236 and reduce the distance between each adjacent pair of magnets 232 , thereby reducing the circumferential length of the annulus 40 ( fig2 c ) as the magnets 234 within the lv 14 passively follow the magnets 232 in the cs 46 . at this point , the delivery catheter 242 may be pushed to the left as viewed in fig2 b and 25c causing a crimping action of a tube 262 affixed to the most proximal magnet 232 . a crimped portion 262 a is then retained within a recessed portion of the coupling element 252 . at the same time , the gripping arms 254 , 256 release the complimentary coupling element 258 of the pull wire or cable 260 and the delivery catheter 242 and pull wire or cable 260 may then be removed leaving the locked fastener system 230 in place as shown in fig2 d . fig2 a and 26b illustrate a fastener system 270 which operates the same as that disclosed in fig2 a - 24c and 25 a - 25 d , except that an accordion or bellows type section 272 replaces each coil spring 236 , and internally and externally threaded coupling elements 274 , 276 replace the gripping arms 254 , 256 and coupling element 258 . it will be appreciated that the operation of the system shown in fig2 a and 26b is the same as that described in the previous embodiment , except that releasing the coupling element 276 will involve rotating the pull wire or cable 260 to decouple the threaded coupling elements 274 , 276 . it will be appreciated that the recessed portion 252 a of coupling element 252 can have an essentially square cross section . the crimped portion 262 a of tube 262 will thus engage the recessed portion and plastically deform about it to prevent rotation of coupling element 252 with respect to threaded coupling element 276 . the coupling element 276 and cable can thus be effectively unthreaded and released . fig2 a and 27b illustrate another alternative catheter based fastener system 280 which is the same as those described with respect to the two previous embodiments , except that the coil springs 236 and accordion shaped bellows sections 272 have been replaced by respective telescoping portions 282 , 284 which carry the magnets 232 fixed therein . also , a releasable coupling 286 is formed by a quarter turn bayonet type fastener as opposed to the gripping arms 254 , 256 and element 258 , or the threaded connection 274 , 276 of the two previous embodiments . in the present embodiment , an elastomeric pad 252 b is seated distal to the proximal component of the bayonet connector 286 . when the bayonet 286 is engaged in the delivery position , the pad 252 b creates a load on the proximal component which prevents inadvertent release of the system 280 . the recessed segment 252 a of the coupling element can have a square cross section to prevent rotation of the coupling during disengagement of the bayonet , in a manner similar to the previous embodiment . the telescoping portions 282 , 284 are flexible and also pivot so that they can conform to the curved shape of the cs 46 . when the pull wire or cable 260 is pulled to the right as illustrated in fig2 a and 27b , the telescoping portions 282 , 284 can move together such that detents 288 move from one recess 290 to an adjacent recess 292 of the respective telescoping portions . the assembly is then locked in place as previously described and the bayonet coupling 286 is released for purposes of withdrawing the delivery catheter 242 . fig2 a and 28b are illustrative of another embodiment which is the same as the system shown in fig2 a and 27b , except that the telescoping portions 282 ′, 284 ′ are fabricated of a flexible , elastomeric polymer material to allow the fastener system 280 ′ to conform to the curve of the cs 46 ( fig2 c ). this is to be contrasted with the fastener system 280 shown in fig2 a and 27b , in which the telescoping elements 284 are fabricated of a relatively more rigid material . in this previous embodiment , flexibility is gained primarily from the length of the detents 290 and 292 , which allow angled positioning of one telescoping element relative to an adjacent one . in the current embodiment , additional flexibility of the fastener is achieved with the length of the detents 290 and 292 . fig2 a and 29b illustrate another system 280 ″ which is similar to those described in the previous embodiment , except that the telescoping portions 282 ″, 284 ″ only have one recess location 290 ′ for initially retaining the relative positions of the telescoping portions 282 ″, 284 ″ as shown in fig2 a . also , each telescoping portion 282 ″, 284 ″ may have projections 296 which act as mechanical fasteners for engaging tissue within the cs 46 ( fig2 c ). when the telescoping portions 282 ″, 284 ″ are drawn together , as described above , the smaller diameter sections 282 ″ are retained in the telescoped position by a locking mechanism operating on the flexible tensile member 238 , such as previously described , thereby maintaining the shortened condition of the fastening system . fig3 , 31a and 31 b illustrate another catheter based system 300 for placing magnets adjacent the mitral annulus , such as within the lv 14 ( fig . a ). in this system , a delivery catheter 304 receives a plurality of annular magnets 306 . magnets 306 , for example , may have roughened outer surfaces 306 a for tissue engagement purposes . the catheter 304 has an outer diameter which is expandable to frictionally retain the magnets 306 at spaced apart locations . an internal tube 308 may be withdrawn , to the left as illustrated in fig3 , to release the magnets 306 from their frictional engagement with the outer surface of the delivery catheter 304 . as one example , the delivery catheter 304 is shown with a manipulator wire 310 for orienting the direction of the distal tip 312 , and also a core wire 314 for facilitating insertion and removal of the delivery catheter 304 . once the magnets 306 are magnetically coupled to additional magnets ( not shown ) across the annulus tissue , for example , the internal tube 308 may be withdrawn thereby releasing the delivery catheter 304 from magnets 306 and facilitating its removal by , for example , pulling on the core wire 314 . the magnets 306 may be coupled together by a thin flexible sheath 316 or other suitable structure . fig3 a - 32c illustrate another catheter based system of fasteners comprising a series of magnets 320 held for sliding movement along parallel wires 322 , 324 . additional parallel wires 326 , 328 are provided as guide wires to guide the assembly during insertion through a catheter ( now shown ) to a location adjacent the annulus . a suitable mechanism ( not shown ), is provided for pushing the magnets 320 together along wires 322 , 324 to reduce annulus tissue , for example , with respect to additional movable magnets ( not shown ) on the opposite side of the tissue . the series of magnets 320 is locked in the position shown in fig3 b , for example . in this embodiment , magnets 320 are coated with a soft polymer 320 a which frictional engages small stop members 322 a , 324 a on wires 322 , 324 to assist with retaining desired positions of the magnets 322 , 324 . fig3 , 33a and 33 b illustrate another system of fasteners placed via a delivery catheter 242 and including a coupling mechanism 244 and locking mechanism 250 as described above in connection with fig2 a - 25d . this system is similar to that described in fig2 a and 26b in that bellows or crumple zones 330 are provided between magnets 232 , as best illustrated in fig3 a and 33b to accommodate movement of adjacent magnets 232 together as they slide along the flexible tensile member 238 while flexible tensile member 238 , which is rigidly attached to the most distal magnet 232 , is pulled to the left as viewed in fig3 . the operation of this embodiment is otherwise the same as that described in connection with fig2 a and 26b . fig3 a - 34i comprise a series of illustrations of a catheter based system for applying a series of fasteners through tissue generally at the mitral valve annulus and using guidance magnets 102 a ′, 102 b ′ and 100 a ′ ( as previously described ) in the cs 46 and the lv 14 . in this embodiment , a left ventrical catheter 340 has a portion 342 which uses radio frequency ( rf ) to effectively drill an initial hole through the tissue and then insert a second larger diameter catheter portion 344 which is steerable , for example , as shown in fig3 b - 34d , to make a second hole in the annulus tissue 40 . it will be appreciated that the various catheters disclosed herein may have distal portions which are steerable in various manners for accurate positioning purposes . in this embodiment , tip 344 is movable into a desired hook - like position by a guiding cable 344 a which may be pulled to configure tip 344 into the hooked shape as shown . the catheters utilized herein can include unidirectional or bi - directional steering . a steering mechanism may be positioned within and / or on the devices . typically , the steering mechanism may include a pull wire 344 a terminating at a flat spring or collar . the steering system has a more flexible distal section compared to the proximal catheter tube body . when tension is placed on the pull wire 344 a , the catheter distal end 344 is deflected into a curve , which helps direct the device within a heart chamber , for example . the pull wire 344 a may be wound , crimped , spot welded or soldered to the flat spring or collar ( not shown ) placed in the catheter end 344 . this provides a stable point within the device for the pull wire 344 a to exert tensile force and thus steer the device . the more proximal portion of the catheter may be reinforced by incorporating a helically wound or braided wire therein to provide column support from which to better deflect the distal section 344 . alternatively , the steering mechanism may consist of a superelastic material having a desired three - dimensional geometric shape at its distal end and sufficient rigidity to impart this shape in the device . by retracting the preformed steering wire into the stiffer proximal section of the device , the distal end of the device straightens . extending the preformed steering wire into the more flexible distal section of the device causes the distal section to assume the shape of the steering wire . alternatively , a device with a curved section can incorporate a tube or rod that can be advanced through that section to straighten it . an additional feature that may be incorporated in the device is a preformed shape in the distal section of the device . the distal section may be preformed into a curve that biases the device to maximize tissue contact when the device is positioned into the appropriate heart chamber . this curve may consist of a single arc or a nonlinear geometry , such as an “ s ”. a pre - shaped rod , hypotube , wire or coil , created from a memory elastic material such as nickel titanium or spring steel may be thermally formed into the desired geometry , and inserted into the distal section ( including a separate lumen ) of the device during manufacturing or advanced through a dedicated lumen while the device is positioned in the heart . the shaped wire may be attached to the distal tip of the device for those non - removable pre - shaped rods and secured to the handle of the device at its proximal end to provide a reinforcing structure throughout the entire length of the device . the device body may also or alternatively be thermally formed into a desired geometry . as shown in fig3 a , the various systems of this invention may also include different manners of ensuring that the catheter device ( s ) is / are properly position adjacent to tissue prior to use . for example , an impedance measurement device 343 may be coupled to the perforating element itself , such as rf wire 342 , or electrodes on the perforating element or on any separate element carried by the system . such proximity determining devices may be used to confirm contact between the catheter device and the tissue surface by comparing the impedance between the electrode ( such as rf wire 342 ) and a return path ( indifferent patch electrode or second element electrode ). when the electrode ( s ) only contact blood , the impedance is substantially higher than when the electrode element is in contact with the tissue surface . each electrode is connected to a signal wire , with the signal wire connected to impedance measurement device 343 . the signal wire may be connected to the impedance measurement device 343 by way of a connector and cable system . the measurement device 343 may be a power supply , a simple electrical resistance meter , or any other suitable device and method of use . as further illustrated in fig3 c , a balloon portion 346 of the left ventricle catheter 340 may be inflated to stabilize the catheter 340 against the tissue 40 as the holes are being formed . as shown in fig3 e and 34f , a fastener 348 is delivered through the lumen of the steerable catheter portion 344 and is coupled with a flexible tensile member 350 and another fastener 352 . the first and second fasteners 348 , 352 are deployed on the same side of the tissue 40 at spaced apart locations with the flexible tensile member 350 coupled therebetween . these fasteners 348 , 352 may be formed essentially as torsion spring members which may have a portion which captures and locks against the flexible tensile member 350 in the deployed position as shown in fig3 f . once the first fastener 348 is deployed as shown in fig3 g , the flexible tensile member 350 may be pulled to plicate the tissue 40 between the first fastener 348 and the steerable catheter portion 344 . at this time , the second fastener 352 is delivered and captures and locks with the flexible tensile member 350 to lock the length of the flexible tensile member 350 between the two fasteners 348 , 350 with the tissue plicated as shown in fig3 h . this process may be repeated , as necessary , to plicate additional annulus tissue 40 for further annulus reduction . fig3 a - 35f illustrate another catheter device 360 for delivering multiple fasteners 362 attached with a flexible tensile member 364 , for example , in the lv 14 at the annulus 40 . as best shown in fig3 b , the catheter device 360 includes three fastener delivery portions 366 , 368 , 370 . one portion 368 is a central portion at the distal end of the catheter device 360 and deploys a first fastener 362 . two additional fastener delivery portions 366 , 370 are spaced on opposite sides of the central portion 368 and preferably may be actively moved to preferred positions relative to central portion 368 to deliver additional fasteners 362 . a flexible tensile member 364 couples each fastener 362 together as well as to a plurality of pledgets or tissue support members 372 . a fastener drive mechanism 374 is used to drive one or more of the fasteners 362 through the tissue and comprises a reciprocating rod 376 which is activated by spring force developed in a coil spring 378 . when a pair of magnets 380 , 382 are decoupled by pulling a wire or cable 384 , for example , the spring forces the reciprocating rod 376 upwardly as viewed in fig3 b to drive the fastener 362 through the tissue 40 . it will be appreciated that similar mechanisms may be used with flexible drive rods 386 , 388 in driving the outer fasteners 362 through the tissue , or this same mechanism 374 may be coupled with flexible drive rods 386 , 388 to simultaneously drive each of the fasteners 362 through the tissue 40 . all three fasteners 362 are thereby deployed , in addition to the pledgets 372 , as illustrated in fig3 e . then , the drawstring or flexible tensile member 364 are pulled tight to plicate the tissue 40 as shown in fig3 f and a crimp member 390 is applied to lock the flexible tensile member 364 in the tensioned position to retain the plicated tissue 40 in the desired state . fig3 illustrates an alternative embodiment of the catheter device 360 shown in fig3 a - 35f , in which the distal end of the catheter device 360 ′ includes a magnet 400 for locking up temporarily with one or more magnets ( not shown ) in the cs 46 ( fig . a ) as previously described . this allows the catheter device 360 ′ to be accurately positioned and temporarily locked in place proximate the annulus 40 while the anchors or fasteners 362 are being delivered , cinched and locked in place as previously described with respect to fig3 a - 35f . fig3 a - 37c illustrate another alternative catheter delivery device or system 410 , and valve support / fastener system 412 for plicating annulus tissue 40 and pulling a posterior leaflet 24 toward an anterior leaflet 22 . in this embodiment , a c - shaped support member 414 is initially retained within a catheter 416 in a nonactivated , compact state as shown in fig3 a . when the support member 414 is pushed from the distal end of the catheter 416 , it springs into a deployed or activated state as shown in fig3 b and 37c . the anchors or fasteners 418 are retained on the rod shaped support member 414 for sliding movement and are coupled together by one or more flexible tensile members 420 . an additional flexible tensile member 422 extends from another catheter portion 424 and provides for secondary cinching or drawstring action . a magnet 426 is rigidly coupled to a central fastener or anchor 418 at p 2 , as shown , or otherwise coupled to the support rod 414 and temporarily locks up with a magnet 428 in the cs 46 generally as previously described . fasteners or anchors 418 are then connected to the annulus tissue 40 such as by using additional fastening elements ( not shown ) which are delivered via another catheter ( not shown ) within the lv 14 , in one of the manner previously described . once the anchors or fasteners 418 are secured to the tissue 40 , the flexible tensile members 420 are pulled thereby pulling each of the fasteners or anchors 418 toward one another along the support member 414 . a final or secondary pulling action may be obtained by pulling the flexible tensile member ends 422 extending into the catheter portion 424 extending from the main catheter 416 . various manners may be used to retain the flexible tensile members 420 , 422 and anchors 418 at the new positions shown in fig3 c , such as by using crimp members ( not shown ), or integrated ratchet - type or frictional engagement structure ( not shown ) which automatically locks the flexible tensile members 420 , 422 in place as they are pulled . fig3 a - 38i illustrate another catheter based system and method for delivering , for example , three fasteners or anchors coupled to respective flexible tensile members and cinched together to reduce a mitral valve annulus 40 . in this embodiment , as shown in fig3 a , a cs catheter 430 and lv catheter 432 may temporarily lock up through magnetic coupling and an initial hole may be formed through the annulus tissue 40 using rf energy applied via a wire 434 . a first fastener or anchor 436 coupled with a flexible tensile member 438 may be deployed through the hole using a catheter 440 threaded over a guide tube 442 . the catheter 440 may be removed and another catheter 444 having bifurcated portions 444 a , 444 b may be used by threading one of the bifurcated portions 444 a over the flexible tensile member 438 . alternatively , once the first fastener 436 and flexible tensile member 438 are deployed as shown in fig3 f , the second portion 444 b of the catheter 440 may be activated and moved to a spaced apart location to form a hole using an rf wire 434 and then deploy a second fastener 446 and flexible tensile member 448 ( fig3 h ). then , the first catheter portion 444 a and second catheter portion 444 b are removed and the first catheter portion 444 a is threaded along the second flexible tensile member 448 . a third anchor 450 and attached flexible tensile member 452 are then deployed from the second catheter portion 444 b resulting in three deployed anchors 436 , 446 , 450 and flexible tensile members 438 , 448 , 452 as shown in fig3 h . a crimping and cutting device 460 is then used to pull the flexible tensile members 438 , 448 , 452 and fasteners or anchors 436 , 446 , 450 together to thereby pull the posterior leaflet 24 toward the anterior leaflet 22 and then a crimp member 462 is applied to the flexible tensile members 438 , 448 , 452 and cut to result in the system being fastened generally as shown in fig3 . as alternatives to rf energy , other manners and devices may be used for forming a hole through tissue prior to or while inserting an anchor or fastener . for example , these may include needles , blades , coring devices , etc . which can effectively create a starter hole in the tissue such that less force is required to drive an anchor into or through the tissue . as shown in fig3 a and 39b , the crimping and cutting device 460 includes a crimping portion 470 comprising jaws 472 a , 472 b with projections 472 for applying force to the crimp member 462 and a cutting portion 474 coupled with an rf energy source 476 . after the crimping portion 470 is actuated to crimp the crimp member 462 onto the flexible tensile members 438 , 448 , 452 , the rf energy source 476 is activated to cut the flexible tensile members 438 , 448 , 452 as shown in fig3 b using cutting element a 477 . to facilitate crimping , one threaded portion 478 of the device is rotated with respect to another portion 479 . this pulls jaws 472 a , 472 b proximally to bring them together against the crimp member 462 . fig4 illustrates the use of an additional magnet 480 in the left atrium 12 for supplying additional magnetic force at the junction of the annulus 40 and cs 46 . an arrangement of magnets 480 , 482 , 484 may be used for temporarily locking up the catheter system at the location that it is desired to deliver a fastener or anchor ( not shown ), such as in those manners previously described . fig4 b - 40d illustrate an alternative fastener delivery system and method for delivering fasteners 486 in the left atrium 12 as opposed to the left ventricle 14 as previously described . this system is otherwise similar in that magnetic guidance and lock up first temporarily occurs between the various magnets 480 , 482 , 484 in the system . once this magnetic lock up has taken place , a fastener 486 and flexible tensile member 488 may be delivered through a steerable portion 490 a of a catheter 490 in the left atrium 12 such that the fastener 486 is delivered into the left ventricle 14 . steering mechanisms , such as those described elsewhere herein may be used to accurately direct catheter portion 490 a . a number of fasteners 486 and attached flexible tensile member or members 488 may be deployed as shown in fig4 d and then cinched or drawn together using a crimping and cutting device 460 as previously described . fig4 a - 41c illustrate another embodiment of a catheter delivered fastening system . in this embodiment , it will be understood that a series of fasteners 500 , 502 , 504 and attached flexible tensile members 506 , 508 , 510 may be delivered as previously described and as shown in fig4 a and 41b . a delivery catheter 520 may include a balloon 522 for stabilizing against the tissue 40 and / or for positioning respective arms 520 a , 520 b , 520 c of the catheter device 520 while delivering the anchors or fasteners 500 , 502 , 504 and each of their attached flexible tensile members 506 , 508 , 510 . a valve support member 530 may then be delivered through a catheter ( not shown ) as shown in fig4 b . the support member 530 has eyelets 532 , 534 , 536 which are threaded over each of the respective flexible tensile members 506 , 508 , 510 . respective crimps 538 , 540 are applied to the outer eyelets 532 , 536 and the flexible tensile members 506 , 510 cut proximate to each crimp member 538 , 540 . the central flexible tensile member 508 is pulled to thereby pull the posterior leaflet 24 at p 2 toward the anterior leaflet 22 . when suitable tension and pulling action has taken place , a third crimp member 542 is applied proximate the central eyelet 534 at the apex of the v - shaped and the flexible tensile member 508 is cut proximate to the crimp member 542 . this results in approximation of the posterior and anterior leaflets 22 , 24 as shown in fig4 c . fig4 a and 42b illustrate one possible anchor or fastener 550 usable with the various systems of the present invention . such an anchor 550 may be rigidly coupled to a flexible tensile member 552 , or coupled such that the anchor or fastener 550 slides along the flexible tensile member 552 , as necessitated by the fastening system in which the fastener 550 is being used . fig4 is a side elevational view of an alternative fastener 560 which is similar to that shown in fig4 a and 42b , except that the fastener 560 has a curved outer profile . the convex surface 562 of the curved outer profile is adapted to engage tissue and cause less trauma to the tissue than the flat profile shown in fig4 a and 42b . fig4 a - 44c illustrate another alternative fastener 570 useful in the various systems and methods of this invention . this fastener 570 includes two radially expandable portions 572 , 574 which may be delivered through a catheter 576 in their nonexpanded state shown in fig4 a , and then expanded on opposite sides of the tissue 40 to be trapped therebetween , as shown in fig4 b and 44c . while the present invention has been illustrated by a description of various preferred embodiments and while these embodiments has been described in some detail , it is not the intention of the applicant to restrict or in any way limit the scope of the appended claims to such detail . additional advantages and modifications will readily appear to those skilled in the art . the various features of the invention may be used alone or in any combination depending on the needs and preferences of the user . this has been a description of the present invention , along with the preferred methods of practicing the present invention as currently known .
catheter based systems and methods for securing tissue including the annulus of a mitral valve . the systems and methods employ catheter based techniques and devices to plicate tissue and perform an annuloplasty .