Percutaneous Tether Locking

Abstract

An implant is provided that includes first and second tissue anchors, which include (a) first and second tissue-coupling elements, respectively, and (b) first and second heads, respectively, which include first and second tether interfaces; and one or more tethers, which are connected to the first tether interface, and coupled to the second tether interface. The first and second tissue anchors are removably positioned in a catheter shaft of a multiple-anchor delivery tool at first and second longitudinal locations, respectively, the first longitudinal location more distal than the second longitudinal location. First and second torque cables of the delivery tool (a) are removably coupled to the first and second heads, respectively, (b) extend within the catheter shaft proximally from the first and second heads, respectively, and (c) transmit torque when rotated. A portion of the first torque cable is removably positioned alongside the second tissue anchor in the catheter shaft.

Claims

1-127. (canceled)

128. An implant system comprising: (i) an implant, which comprises: at least first and second tissue anchors, which comprise (a) first and second tissue-coupling elements, respectively, and (b) first and second heads, respectively, which comprise first and second tether interfaces; and one or more tethers, which are connected to the first tether interface, and coupled to the second tether interface; and (ii) a multiple-anchor delivery tool, which comprises: a catheter shaft having proximal and distal ends, wherein the first and the second tissue anchors are removably positioned in the catheter shaft at first and second longitudinal locations, respectively, the first longitudinal location more distal than the second longitudinal location; and first and second torque cables, which (a) are removably coupled to the first and the second heads, respectively, (b) extend within the catheter shaft proximally from the first and the second heads, respectively, and (c) transmit torque when rotated, wherein a portion of the first torque cable is removably positioned alongside the second tissue anchor in the catheter shaft.

129. The implant system according to claim 128, wherein the implant further comprises a third tissue anchor, which comprises (a) a third tissue-coupling element and (b) a third head, which comprises a third tether interface, wherein the one or more tethers are coupled to the third tether interface, wherein the third tissue anchor is removably positioned in the catheter shaft at a third longitudinal location that is more proximal than the second longitudinal location, and wherein the multiple-anchor delivery tool further comprises a third torque cable, which (a) is removably coupled to the third head, (b) extends within the catheter shaft proximally from the third head, and (c) transmits torque when rotated, wherein a portion of the second torque cable is removably positioned alongside the third tissue anchor in the catheter shaft.

130. The implant system according to claim 128, wherein the first tether interface is rotatable with respect to the first tissue-coupling element.

131. The implant system according to claim 128, wherein the first torque cable is shaped so as to define a lumen therethrough, and wherein the multiple-anchor delivery tool further comprises a wire, which removably passes through the lumen.

132. The implant system according to claim 131, wherein the head is shaped so as to define a proximal coupling element, wherein the head, including the proximal coupling element, is shaped so as to define a first longitudinal channel at least partially therethrough, which channel is coaxial with the head, wherein a distal end of the first torque cable comprises a distal coupling element, which is shaped so as to define a second longitudinal channel therethrough, which channel is coaxial with the lumen of the first torque cable, wherein the proximal and the distal coupling elements are shaped so as to define corresponding interlocking surfaces, and wherein the wire, when disposed through the first and the second channels, prevents decoupling of the distal coupling element from the proximal coupling element.

133. The implant system according to claim 131, wherein the wire is shaped so as to define a sharp distal tip.

134. The implant system according to claim 131, wherein the first and the second tissue-coupling elements are configured to puncture tissue.

135. The implant system according to claim 131, wherein the first and the second anchor heads are coaxial when the first and the second tissue anchors are removably positioned in the catheter shaft.

136. The implant system according to claim 131, wherein the multiple-anchor delivery tool further comprises a control handle, which is configured to allow separate rotation of each of the first and the second torque cables.

137. A method comprising: advancing a distal end of a catheter shaft of a multiple-anchor delivery tool into a body of a subject, while (a) first and second tissue anchors are removably positioned in the catheter shaft at first and second longitudinal locations, respectively, the first longitudinal location more distal than the second longitudinal location, wherein the first and the second tissue anchors include (i) first and second tissue-coupling elements, respectively, and (ii) first and second heads, respectively, which include first and second tether interfaces, and (b) one or more tethers, which are connected to the first tether interface, and are coupled to the second tether interface, are removably positioned in the catheter shaft, wherein the multiple-anchor delivery tool includes first and second torque cables, which (A) are removably coupled to the first and the second heads, respectively, (B) extend within the catheter shaft proximally from the first and the second heads, respectively, and (C) transmit torque when rotated, wherein a portion of the first torque cable is removably positioned alongside the second tissue anchor in the catheter shaft; implanting the first tissue anchor in tissue of the subject; decoupling the first torque cable from the first tissue anchor; after implanting the first tissue anchor, distally advancing the second tissue anchor in the catheter shaft; implanting the second tissue anchor in tissue of the subject; and decoupling the second torque cable from the second tissue anchor.

138. The method according to claim 137, wherein implanting the first tissue anchor comprises rotating the first torque cable.

139. The method according to claim 137, wherein the first torque cable is shaped so as to define a lumen therethrough, wherein the multiple-anchor delivery tool further comprises a wire, which removably passes through the lumen, and which is initially positioned such that a distal end of the wire extends distally out of a distal end of the lumen, and wherein the method further comprises withdrawing the wire proximally.

140. The method according to claim 139, wherein the head is shaped so as to define a proximal coupling element, wherein the head, including the proximal coupling element, is shaped so as to define a first longitudinal channel at least partially therethrough, which channel is coaxial with the head, wherein a distal end of the first torque cable includes a distal coupling element, which is shaped so as to define a second longitudinal channel therethrough, which channel is coaxial with the lumen of the first torque cable, wherein the proximal and the distal coupling elements are shaped so as to define corresponding interlocking surfaces, wherein the wire, when disposed through the first and the second channels, prevents decoupling of the distal coupling element from the proximal coupling element, and wherein withdrawing the wire proximally comprises decoupling the distal coupling element from the proximal coupling element by withdrawing the wire proximally.

141. The method according to claim 140, wherein the wire is shaped so as to define a sharp distal tip.

142. The method according to claim 141, wherein implanting the first tissue anchor comprises inserting the sharp distal tip of the wire into the tissue.

143. The method according to claim 137, wherein advancing comprises advancing the distal end of the catheter shaft into the body while (a) a third tissue anchor is removably positioned in the catheter shaft at a third longitudinal location that is more proximal than the second longitudinal location, wherein the third tissue anchor includes (i) a third tissue-coupling element and (ii) a third head, which comprises a third tether interfaces, and (b) the one or more tethers are coupled to the third tether interface, wherein the multiple-anchor delivery tool further includes a third torque cable, which (a) is removably coupled to the third head, (b) extends within the catheter shaft proximally from the third head, and (c) transmits torque when rotated, wherein a portion of the second torque cable is removably positioned alongside the third tissue anchor in the catheter shaft, and wherein the method further comprises: after implanting the second tissue anchor, distally advancing the third tissue anchor in the catheter shaft; implanting the third tissue anchor in tissue of the subject; and decoupling the third torque cable from the third tissue anchor.

144. The method according to claim 137, wherein the first tether interface is rotatable with respect to the first tissue-coupling element.

145. The method according to claim 137, wherein the first and the second anchor heads are coaxial when the first and the second tissue anchors are removably positioned in the catheter shaft.

146. The method according to claim 137, wherein advancing the distal end of the catheter shaft comprises transvascularly advancing the distal end of the catheter shaft.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0223] FIG. 1 is a schematic illustration of a valve-tensioning implant system, in accordance with an application of the present invention;

[0224] FIG. 2 is a schematic illustration of a tether-securing device of the implant system of FIG. 1, in accordance with an application of the present invention;

[0225] FIG. 3 is a schematic illustration of another valve-tensioning implant system, in accordance with an application of the present invention;

[0226] FIGS. 4A-C are schematic illustrations of yet another valve-tensioning implant system, in accordance with an application of the present invention;

[0227] FIG. 5 is a schematic illustration of a tether-securing device of the implant system of FIGS. 4A-C fixed to second tissue anchor of the implant system, in accordance with an application of the present invention;

[0228] FIGS. 6A-C are schematic illustration of still another valve-tensioning implant system, in accordance with an application of the present invention;

[0229] FIGS. 7A and 7B are schematic illustration of a tether-securing device of the implant system of FIGS. 6A-C, in unlocked and one-way-locked configurations, respectively, in accordance with an application of the present invention;

[0230] FIGS. 8A-C are schematic illustrations of techniques for securing an excess portion of a tether of the implant system of FIGS. 6A-C and 7A-B, in accordance with respective applications of the present invention;

[0231] FIG. 9 is a schematic illustration of another valve-tensioning implant system, in accordance with an application of the present invention;

[0232] FIGS. 10A-D are schematic illustrations of friction-enhancing features of a tether, in accordance with respective applications of the present invention;

[0233] FIG. 11 is a schematic illustration of a delivery system comprising a multiple-anchor delivery tool, in accordance with an application of the present invention; and

[0234] FIGS. 12A-C are schematic illustrations of a deployment method using the multiple-anchor delivery tool of FIG. 11, in accordance with an application of the present invention.

DETAILED DESCRIPTION OF APPLICATIONS

[0235] FIG. 1 is a schematic illustration of a valve-tensioning implant system 20, in accordance with an application of the present invention. Valve-tensioning implant system 20 is configured to repair an atrioventricular valve of a subject (e.g., a tricuspid valve 22 or a mitral valve), using tension applied between multiple (e.g., two) anchors of the implant. Typically, repair of the atrioventricular valve facilitates a reduction in atrioventricular valve regurgitation by altering the geometry of the atrioventricular valve and/or by altering the geometry of the wall of the right or left atrium of a heart of the subject. Implant system 20 comprises a tether-securing device 30, at least one tether 50, and first and second tissue anchors 52A and 52B.

[0236] For some applications, first and second tissue anchors 52A and 52B are connected (e.g., permanently fixed) to first and second tether end portions 54A and 54B of the at least one tether 50, respectively (typically first and second tissue anchors 52A and 52B are connected to first and second tether ends of the at least one tether 50, respectively). The at least one tether 50 comprises an elongate flexible element, such as a cord, suture, or band. Typically, the at least one tether 50 has a high tensile strength, in order to enable the tether to apply tension, as described hereinbelow. It is noted that, although the tethers described herein are shown as ribbon-shaped sutures (i.e., having a generally rectangular cross-section), any suitable type of textile or suture, as is known in the art, may alternatively be used. For some applications, first and second tether end portions 54A and 54B are configured so as to define anchor-fixing loops 68A and 68B, respectively, which pass through corresponding interfaces on first and second tissue anchors 52A and 52B, respectively, so as to connect (e.g., permanently fix) the tether end portions to the tissue anchors.

[0237] Reference is still made to FIG. 1, and is additionally made to FIG. 2, which is a schematic illustration of tether-securing device 30, in accordance with an application of the present invention. Tether-securing device 30 comprises a tubular element 32, which is shaped so as define a lateral wall 34 that surrounds a securing-device lumen 36. Lateral wall 34 is shaped so as to define a one-way locking opening 38. For some applications, one-way locking opening is shaped as a slit, as shown. For some applications, the slit extends in a direction parallel to a longitudinal axis 39 of tubular element 32. Typically, lateral wall 34 is shaped so as to define at least two pawls 40A and 40B, which together define one-way locking opening 38. Typically, one-way locking opening has uneven edges, which, for example, may be jagged or serrated.

[0238] The at least one tether 50 passes through securing-device lumen 36 and one-way locking opening 38. One-way locking opening 38 is configured to (a) allow sliding of the at least one tether 50 in a first direction through one-way locking opening 38, and (b) inhibit (e.g., prevent or limit) sliding of the at least one tether 50 in a second direction opposite the first direction. The one-way locking opening thus allows the tightening of tissue anchors 52A and 52B together, and resists the loosening of the anchors away from one another. For some applications, the first direction is from inside the tubular element to outside the tubular element. For some applications, in order to provide such unidirectional movement of the at least one tether, pawls 40A and 40B are configured to open outwardly but not open inwardly.

[0239] For some applications, such as shown in FIG. 1, a single tether 50 of the at least one tether 50 has first and second tether end portions 54A and 54B. (The at least one tether 50 may or may not comprise additional tethers in addition to the single tether.) For these applications, single tether 50 typically comprises at least the following non-overlapping longitudinal portions disposed in sequence along the single tether: [0240] first tether end portion 54A, [0241] a first portion 59A that passes through securing-device lumen 36 and one-way locking opening 38, [0242] a looped middle portion 88 that extends out of and away from the one-way locking opening, and then loops back to the one-way locking opening (typically, such that a longitudinal center 61 of looped middle portion 88 is not in direct physical contact with any portion of tether-securing device 30), [0243] a second portion 59B that passes through securing-device lumen 36 and one-way locking opening 38, and [0244] second tether end portion 54B.
Typically, the single tether comprises additional longitudinal portions between the above-listed portions, i.e., the above-listed portions are in sequence, but not contiguous with one another. For example, the single tether typically comprises a longitudinal portion between first tether end portion 54A and first portion 59A, and a longitudinal portion between second portion 59B and second tether end portion 54B.

[0245] Tether-securing device 30 thus fixes first and second portions 59A and 59B to each other. Typically, the longitudinal location of tether-securing device 30 along the single tether is set during an implantation procedure, such that respective distances between tether-securing device 30 and first and second tissue anchors 52A and 52B are set during the procedure rather than preconfigured. For some applications, these distances are set using echocardiography and by measuring regurgitant flow, annulus dimensions, and/or with the aid of radiopaque markers on tethers between the two tissue anchors. For some applications, the at least one tether 50 comprises exactly one tether 50.

[0246] For some applications, lateral wall 34 is shaped so as to define at least one non-constraining opening 60, such as first and second non-constraining openings 60A and 60B, disposed at respective circumferential locations different from the circumferential location of one-way locking opening 38. First and second non-constraining openings 60A and 60B are sized and shaped to allow free sliding therethrough of first and second longitudinal portions 62A and 62B of single tether 50, respectively. Typically, first and second non-overlapping longitudinal portions 62A and 62B slidably pass through first and second non-constraining openings 60A and 60B, respectively. For some applications, non-constraining openings 60 are shaped as respective slits (as shown), circles (not shown), or other shapes. For some applications in which the non-constraining openings are shaped as slits, the slits extend in a direction parallel to longitudinal axis 39 of tubular element 32.

[0247] For some applications, as shown, tubular element 32 is cylindrical. Alternatively, the tubular element may have other hollow shapes such as rectangular, triangular, or hexagonal. For some applications, an axial length of tubular element 32 is at least 5 mm, no more than 20 mm, and/or between 5 and 20 mm.

[0248] For some applications, first and second tissue anchor 52A and 52B comprise respective atrial tissue anchors. Alternatively or additionally, for some applications, first and second tissue anchor 52A and 52B comprise respective helical tissue-coupling elements, which puncture and screw into cardiac muscle tissue. For some applications, first and second tissue anchor 52A and 52B implement techniques described in U.S. Provisional Application 61/750,427, filed Jan. 9, 2013. Alternatively, each of first and second tissue anchors 52A and 52B comprises a clip, jaws, or a clamp which grips and squeezes a portion of cardiac muscle tissue and does not puncture the cardiac muscle tissue.

[0249] Valve-tensioning implant system 20 is typically implanted transvascularly, using a delivery system comprising one or more catheters introduced with the aid of a guidewire, through vasculature of the subject, such as (a) via the femoral vein, through an inferior vena cava 74, and into a right atrium 81, (b) via the basilic vein, through the subclavian vein through a superior vena cava 76, and into right atrium 81, or (c) via the external jugular vein, through the subclavian vein through superior vena cava 76, and into right atrium 81. (Right atrium 81 includes a septal leaflet 82, a posterior leaflet 84, and an anterior leaflet 86.) The procedure is typically performed with the aid of imaging, such as fluoroscopy, transesophageal, transthoracic echocardiography, intravascular ultrasound (IVUS), and/or echocardiography. The procedure may be performed using techniques described in US Patent Application Publication 2012/0035712, which is assigned to the assignee of the present application and is incorporated herein by reference, with reference to FIGS. 1A-D thereof, mutatis mutandis, and/or using techniques described hereinbelow with reference to FIGS. 11-12C.

[0250] First and second tissue anchor 52A and 52B are implanted at respective different second atrial sites 70A and 70B, each of which sites is selected from the group of sites consisting of: an annulus of tricuspid valve 22, and a wall of the right atrium of the heart above the annulus. For applications in which first and second tissue anchors 52A and 52B comprise respective helical tissue-coupling elements, the helical tissue-coupling elements are rotated into tissue at the sites, respectively. For example, first and second tissue coupling elements may be implanted within 1 cm of a first site on the annulus and within 1 cm of a second site on the annulus around the valve, respectively. For example, as shown in FIG. 1, first tissue anchor 52A may be implanted within 1 cm of the site on the annulus that circumferentially corresponds to a septoposterior commissure 117 (i.e., is at the same angular location or o'clock as the septoposterior commissure), and second tissue anchor 52B may be implanted within 1 cm of a circumferential middle of the annulus 87 along anterior leaflet 86. The pairs of sites are typically diametrically opposed on the annulus of the valve. The direction of the 1 cm from the sites on the annulus described here and hereinbelow may be either circumferentially (i.e., clockwise or counterclockwise) around the annulus, up the wall of right atrium 81 above annulus 83, or a combination of circumferentially around the annulus and up the wall of the atrium.

[0251] The size of the tricuspid valve orifice is reduced by tensioning tether 50, so as to reduce regurgitation. Such tensioning may be performed by holding a catheter shaft (such as outer shaft 384, described hereinbelow with reference to FIGS. 6A-C) against a proximal side of tether-securing device 30 while proximally pulling on looped middle portion 88 of tether 50, such that portions of tether 50 are pulled through one-way locking opening 38. For example, a flexible longitudinal guide member 390 (as shown below in FIG. 6C) may be removably coupled to middle portion 88 by a loop 80, such as a ring, using techniques described in US Patent Application Publication 2013/0018459, which is assigned to the assignee of the present application and is incorporated herein by reference, with reference to FIGS. 23-26 thereof, mutatis mutandis (in which flexible longitudinal guide member 2616 corresponds to flexible longitudinal guide member 390 of the present application). Once the tension has been applied, one-way locking opening 38 maintains the tension.

[0252] After tether 50 has been tensioned, an excess portion 94 of tether 50 near looped middle portion 88 remains free in right atrium 81. It is generally undesirable to leave this excess portion free to move around in the atrium. For some applications, excess portion is secured in a desired disposition in the vasculature of right atrium 81, such as in inferior vena cava 74 (as shown in FIG. 1), superior vena cava 76 (such as shown in FIG. 8B, mutatis mutandis), or a coronary sinus 115 (such as shown in FIG. 8C, mutatis mutandis). Techniques described hereinbelow with reference to FIGS. 8A-C may be used for such securing, mutatis mutandis. It is noted that in this configuration, venous tissue anchor 400, described hereinbelow with reference to FIGS. 8A-C, is deployed such that only a moderate amount of tension is applied to fixation tether 404, which tension is insufficient to alter the geometry of the atrium annulus and ventricle. Fixation tether 404 is connected, typically during the implantation procedure, to looped middle portion 88, such as by loop 80, e.g., a ring. Alternatively, excess portion 394 is cut and removed from the atrium, such as using techniques described hereinbelow with reference to FIG. 9, mutatis mutandis.

[0253] Reference is now made to FIG. 3, which is a schematic illustration of a valve-tensioning implant system 120, in accordance with an application of the present invention. Except as described below, implant system 120 is the same as implant system 20, described hereinabove with reference to FIGS. 1 and 2, and may incorporate any of the features thereof. In this configuration, the at least one tether 50 of implant system 120 comprises first and second tethers 50A and 50B, which (a) have first tether end portion 54A and a second tether end portion 54B, respectively, and (b) pass through (i) the portion of securing-device lumen 36 and (ii) the one-way locking opening 38. Second tissue anchor 52B is connected (e.g., permanently fixed) to second tether end portion 54B. One-way locking opening 38 is configured to (a) allow the sliding of first and second tethers 50A and 50B in the first direction through one-way locking opening 38, and (b) inhibit (e.g., prevent or limit) the sliding of first and second tethers 50A and 50B in the second direction. Tether-securing device 30 thus fixes the tethers 50 to each other.

[0254] For some applications, lateral wall 34 is shaped so as to define at least two non-constraining openings 60, such as first and second non-constraining openings 60A and 60B, disposed at respective circumferential locations different from the circumferential location of one-way locking opening 38. First and second non-constraining openings 60A and 60B are sized and shaped to allow free sliding therethrough of first and second tethers 50A and 50B, respectively. First and second tethers 50A and 50B slidably pass through first and second non-constraining openings 60A and 60B, respectively. For some applications, non-constraining openings 60 are shaped as respective slits (as shown), circles (not shown), or other shapes. For some applications in which the non-constraining openings are shaped as slits, the slits extend in a direction parallel to longitudinal axis 39 of tubular element 32.

[0255] For some applications, free end portions 53 of first and second tethers 50A and 50B (opposite first and second tether end portions 54A and 54B) are connected, typically during the implantation procedure, to fixation tether 404, described hereinbelow with reference to FIGS. 8A-C, such as by respective rings 55. Alternatively, for some applications, any excess length of the free end portions is cut and removed from the atrium, using a cutting tool, such as thoracoscopic scissors, as known in the art.

[0256] Reference is made to FIGS. 1 and 3. For applications in which the at least one tether 50 comprises single tether 50, such as exactly one tether 50 (as shown in FIG. 1), the single tether typically has a length, measured between first tissue anchor 52A and second tissue anchor 52B, of at least 30 mm, no more than 160 mm, and/or between 30 and 160 mm. For some applications, looped middle portion 88 has a length, measured along tether 50 (i.e., if the looped middle portion were to be straightened), of at least 5 mm. For application in which the at least one tether 50 comprises two tethers 50A and 50B, such as shown in FIG. 3, each of tethers 50 typically has a length of at least 20 mm, no more than 80 mm, and/or between 20 and 80 mm. Because each tether 50 typically has a high tensile strength, the length thereof does not vary based on the particular disposition of the tether at any given point in time. In other words, the length of the tether does not depend on the amount of force applied to it.

[0257] Reference is now made to FIGS. 4A-C, which are schematic illustrations of a valve-tensioning implant system 220, in accordance with an application of the present invention. Valve-tensioning implant system 220 is configured to repair an atrioventricular valve of a subject (e.g., tricuspid valve 22 or a mitral valve), using tension applied between multiple (e.g., two) anchors of the implant. Typically, repair of the atrioventricular valve facilitates a reduction in atrioventricular valve regurgitation by altering the geometry of the atrioventricular valve and/or by altering the geometry of the wall of the right or left atrium of a heart of the subject. Implant system 220 comprises a tether-securing device 230, at least one tether 50, and first and second tissue anchors 252A and 252B. Except as described below, tether-securing device 230 is similar to tether-securing device 30, described hereinabove with reference to FIGS. 1 and 2, and may incorporate any of the features thereof.

[0258] Reference is still made to FIGS. 4A-C, and is additionally made to FIG. 5, which is a schematic illustration of tether-securing device 230 fixed to second tissue anchor 252B, in accordance with an application of the present invention. Second tissue anchor 252B comprises a head 253 and a tissue-coupling element 255, such as a helical tissue-coupling element. Tether-securing device 230 is fixed to head 253, typically such that the tether-securing device surrounds at least a portion of the head. Typically, tether-securing device 230 is configured to rotate with respect to head 253, such that the tether-securing device is mounted rotatably on the head.

[0259] Typically, first tissue anchor 252A is connected (e.g., permanently fixed) to first tether end portion 54A of tether 50. For some applications, first tether end portion 54A is configured so as to define anchor-fixing loop 68A, which passes through a corresponding interface on first tissue anchor 52A so as to connect (e.g., permanently fix) the tether end portion to the tissue anchor.

[0260] In this configuration, typically a single tether 50 of the at least one tether 50 has first and second tether end portions 54A and 54B. (The at least one tether 50 may or may not comprise additional tethers in addition to the single tether.) A longitudinal portion 257 of single tether 50 passes through (a) securing-device lumen 36 and (b) one-way locking opening 38 of tether-securing device 230. For some applications, the at least one tether 50 comprises exactly one tether 50.

[0261] For some applications, lateral wall 34 of tether-securing device 230 is shaped so as to define a non-constraining opening 60, such as exactly one non-constraining opening 60, as shown in FIG. 5 (which shows two different views of the same tether-securing device and anchor). Non-constraining opening 60 is disposed at a circumferential location different from the circumferential location of one-way locking opening 38, such as diametrically opposite the locking opening. Non-constraining opening 60 is sized and shaped to allow free sliding therethrough of longitudinal portion 257. Longitudinal portion 257 of tether 50 slidably passes through non-constraining opening 60. For some applications, non-constraining opening 60 is shaped as a slit (as shown), a circle (not shown), or another shape. For some applications in which the non-constraining opening is shaped as a slit, the slit extends in a direction parallel to longitudinal axis 39 of tubular element 32 of tether-securing device 230.

[0262] Valve-tensioning implant system 120 is typically implanted transcatheterly, using a delivery system comprising one or more catheters introduced with the aid of a guidewire, through vasculature of the subject, such as (a) via the femoral vein, through inferior vena cava 74, and into right atrium 81, (b) via the basilic vein, through the subclavian vein through superior vena cava 76, and into right atrium 81, or (c) via the external jugular vein, through the subclavian vein through superior vena cava 76, and into right atrium 81. The procedure is typically performed with the aid of imaging, such as fluoroscopy, transesophageal, transthoratic echocardiography, IVUS, and/or echocardiography. The procedure may be performed using techniques described in US Patent Application Publication 2012/0035712, which is assigned to the assignee of the present application and is incorporated herein by reference, with reference to FIGS. 1A-D thereof, mutatis mutandis, and/or using techniques described hereinbelow with reference to FIGS. 11-12C.

[0263] First and second tissue anchor 252A and 252B are implanted at respective different second atrial sites 270A and 270B, each of which sites is selected from the group of sites consisting of: an annulus of tricuspid valve 22, and a wall of the right atrium of the heart above the annulus. For applications in which first and second tissue anchors 252A and 252B comprise respective helical tissue-coupling elements, the helical tissue-coupling elements are rotated into tissue at the sites, respectively. For example, as shown in FIGS. 4A and 4C, first tissue anchor 252A may be implanted within 1 cm of the point on the annulus that circumferentially corresponds to septoposterior commissure 117, and second tissue anchor 352B may be implanted at any pair of locations around the annulus of the tricuspid valve, e.g. diametrically opposed, for instance, as shown in FIG. 4B, first tissue anchor 252A may be implanted within 1 cm of the point on the annulus that circumferentially corresponds to anteroposterior commissure 112, and second tissue anchor 252B may be implanted within 1 cm of the point on the annulus that circumferentially corresponds to a circumferential middle 93 of septal leaflet 82. The direction of the 1 cm from the described anatomical sites may be either circumferentially around the annulus, up the wall of right atrium 81 above annulus 83, or a combination of circumferentially around the annulus and up the wall of the atrium.

[0264] The size of the tricuspid valve orifice is reduced by tensioning tether 50, so as to reduce regurgitation. Such tensioning may be performed by proximally pulling on second tether end portion 54B of tether 50, such that a portion of tether 50 is pulled through one-way locking opening 38. For example, a flexible longitudinal guide member 390 (as shown below in FIG. 6C) may be removably coupled to second tether end portion 54B by a loop 180, such as a ring, using techniques described in US Patent Application Publication 2013/0018459, which is assigned to the assignee of the present application and is incorporated herein by reference, with reference to FIGS. 23-26 thereof, mutatis mutandis (in which flexible longitudinal guide member 2616 corresponds to flexible longitudinal guide member 390 of the present application). Once the tension has been applied, one-way locking opening 38 maintains the tension.

[0265] After tether 50 has been tensioned, an excess portion 294 of tether 50, including second tether end portion 54B, remains free in right atrium 81. It is generally undesirable to leave this excess portion free to move around in the atrium.

[0266] For some applications, excess portion is secured in a desired disposition in the vasculature of right atrium 81, such as in inferior vena cava 74 (as shown in FIG. 4A), superior vena cava 76 (such as shown in FIG. 8B, mutatis mutandis), or a coronary sinus 115 (such as shown in FIG. 4B). Techniques described hereinbelow with reference to FIGS. 8A-C may be used for such securing, mutatis mutandis. It is noted that in this configuration, venous tissue anchor 400, described hereinbelow with reference to FIGS. 8A-C, is deployed such that only a moderate amount of tension is applied to fixation tether 404, which tension is insufficient to alter the geometry of the atrium. Fixation tether 404 is connected, typically during the implantation procedure, to tether end portion 54B, such as by loop 180, e.g., a ring. Alternatively, excess portion 294 of tether 50 is cut and removed from the atrium, using a cutting tool 498, such as thoracoscopic scissors, as known in the art.

[0267] Reference is now made to FIGS. 6A-C, which are schematic illustration of a valve-tensioning implant system 320, in accordance with an application of the present invention. Valve-tensioning implant system 320 is configured to repair an atrioventricular valve of a subject (e.g., tricuspid valve 22 or a mitral valve), using tension applied between multiple (e.g., two) anchors of the implant. Typically, repair of the atrioventricular valve facilitates a reduction in atrioventricular valve regurgitation by altering the geometry of the atrioventricular valve and/or by altering the geometry of the wall of the right or left atrium of a heart of the subject. Implant system 320 comprises a tether-securing device 330, at least one tether 350, and first and second tissue anchors 352A and 352B. For some applications, first and second tissue anchors 352A and 352B are connected (e.g., permanently fixed) to first and second tether end portions 354A and 354B of the at least one tether 350, respectively (typically first and second tissue anchors 352A and 352B are connected to first and second ends of the at least one tether 350, respectively). For some applications, first and second tether end portions 354A and 354B are configured so as to define anchor-fixing loops 368A and 368B, respectively, which pass through corresponding interfaces on first and second tissue anchors 352A and 352B, respectively, so as to connect (e.g., permanently fix) the tether end portions to the tissue anchors.

[0268] Reference is now made to FIGS. 7A and 7B, which are schematic illustration of tether-securing device 330, in unlocked and one-way-locked configurations, respectively, in accordance with an application of the present invention. Tether-securing device 330 is configured to assume the unlocked and the one-way-locked configurations. Tether-securing device 330 comprises a tubular element 332, which is shaped so as define a securing-device lumen 336 through which the at least one tether 350 passes, and has proximal and distal tube ends 335 and 337. Tether-securing device 330 typically comprises an implantable alloy, typically superelastic, such as Nitinol.

[0269] Tether-securing device 330 further comprises three or more locking pieces 341 (which may be considered pawls), which extend proximally from proximal end 335 of tubular element 332. Tether-securing device 330 is configured: [0270] to assume the unlocked configuration when locking pieces 341 are in a constrained state, as shown in FIG. 7A, in which locking pieces 341 extend proximally and allow distal and proximal sliding of the at least one tether 350 through securing-device lumen 336, and [0271] to assume the one-way-locked configuration when locking pieces 341 are in a relaxed state, as shown in FIG. 7B, in which locking pieces 341 extend proximally and radially inward toward one another (and, typically, toward a central longitudinal axis of tubular element 332). When tether-securing device 330 is in the one-way-locked configuration, locking pieces 341 (a) inhibit (e.g., prevent) the distal sliding more than when in the constrained state and, optionally, (b) allow the proximal sliding. In this relaxed state, tether-securing device 330 may be bullet-shaped, such as shown in FIG. 7B, with the locking pieces collectively defining a round nose thereof.

[0272] For some applications, such as shown in FIG. 6A-C, a single tether 350 of the at least one tether 350 has first and second tether end portions 354A and 354B. (The at least one tether 350 may or may not comprise additional tethers in addition to the single tether.) For these applications, single tether 350 typically comprises at least the following non-overlapping longitudinal portions disposed in sequence along the single tether: [0273] first tether end portion 354A, [0274] a first portion 359A that passes through securing-device lumen 336, [0275] a looped middle portion 388 that extends out of and away from the lumen, and then loops back to the lumen (such that a longitudinal center 361 of looped middle portion 388 is not in direct physical contact with any portion of tether-securing device 330), [0276] a second portion 359B that passes through securing-device lumen 336, and [0277] second tether end portion 354B.
Typically, the single tether comprises additional longitudinal portions between the above-listed portions, i.e., the above-listed portions are in sequence, but not contiguous with one another. For example, the single tether typically comprises a longitudinal portion between first tether end portion 354A and first portion 359A, and a longitudinal portion between second portion 359B and second tether end portion 354B.

[0278] Tether-securing device 330 thus fixes first and second portions 359A and 359B to each other, either (a) directly, if the two portions touch one another between locking pieces 341, or (b) indirectly, via the tether-securing device, if the two portions do not touch one another in the one-way locking opening (such as if they are at different circumferential positions around the tether-securing device). For some applications, the at least one tether 350 comprises exactly one tether 350. For applications in which the at least one tether 350 comprises two tethers 350, such as described hereinbelow with reference to FIG. 9, tether-securing device 330 thus fixes the tethers 350 to each other, either (a) directly, if the two tethers touch one another between locking pieces 341, or (b) indirectly, via the tether-securing device, if the two tethers do not touch one another in the one-way locking opening (such as if they are at different circumferential positions around the tether-securing device).

[0279] For some applications, locking pieces 341 comprise exactly three locking pieces (as shown) or exactly four locking pieces (configuration not shown). Typically, locking pieces 341 are integral with tubular element 332, and the locking pieces and tubular element are manufactured from a single piece of material. For some applications, tubular element 332 has an inner diameter of at least 3 mm, no more than 12 mm, and/or between 3 and 12 mm, and/or an outer diameter of at least 3.1 mm, no more than 12.1 mm, and/or between 3.1 and 12.1 mm.

[0280] For some applications, each of locking pieces 341 is shaped so as to define two curved proximal edges 343A and 343B that meet at a proximal tip 345. For some applications, proximal edges 343A and 343B are shaped so as to define uneven edge surfaces, which, for example, may be jagged or serrated. The uneven edge surfaces of proximal edge 343A interconnect with the uneven edge surfaces of proximal edge 343B, thereby creating friction on the at least one tether 350 and inhibiting (e.g., preventing) sliding of the at least one tether through the tether-securing device, at least in the distal direction. For some applications, the uneven edge surfaces are shaped so as define teeth, such as shown in FIGS. 7A-B. Alternatively or additionally, for some applications, the uneven edge surfaces are rough. For some applications, locking pieces 341 are convex, as viewed from outside tether-securing device 330, at least when locking pieces 341 are in the relaxed state.

[0281] In the relaxed state, such as shown in FIG. 7B, proximal tips 345 of locking pieces may be in a vicinity of each other, e.g., within 2 mm of each other, if not held farther apart from each other by tether 350 (which is not shown in FIG. 7B). For example the tips may be within 0.1 mm of each other, or touching each other.

[0282] For some applications, as shown, tubular element 332 is cylindrical. Alternatively, the tubular element has another shape. For some applications, an axial length of tubular element 332 is at least 3 mm, no more than 50 mm, and/or between 3 and 50 mm; an axial length of tether-securing device 330 when in the unlocked configuration is between 3 and 50 mm; and/or an axial length of tether-securing device 330 when in the one-way-locked configuration is between 3 and 50 mm.

[0283] Reference is again made to FIGS. 6A-C. For some applications, a delivery tool 380 is provided, which comprises an inner catheter shaft 382, which is configured to apply a constraining force to tether-securing device 360 when inner shaft 382 is disposed in the securing-device lumen 336, as shown in FIG. 6A. The constraining force retains tether-securing device 360 in the unlocked configuration. Inner shaft 382 is shaped so as to define a shaft lumen, through which the at least one tether 350 removably slidably passes. Typically, an outer diameter of inner shaft 382 is between 80% and 99% of an inner diameter of tubular element 332 of tether-securing device 330. Typically, delivery tool 380 further comprises an outer shaft 384, which surrounds inner shaft 382. Typically, an inner diameter of outer shaft 384 is between 80% and 99% of an outer diameter of tubular element 332 of tether-securing device 330.

[0284] Valve-tensioning implant system 320 is typically implanted transvascularly, using a delivery system comprising one or more catheters introduced with the aid of a guidewire, through vasculature of the subject, such as (a) via the femoral vein, through inferior vena cava 74, and into right atrium 81, (b) via the basilic vein, through the subclavian vein through superior vena cava 76, and into right atrium 81, or (c) via the external jugular vein, through the subclavian vein through superior vena cava 76, and into right atrium 81. The procedure is typically performed with the aid of imaging, such as fluoroscopy, transesophageal, transthoratic echocardiography, IVUS, and/or echocardiography. The procedure may be performed using techniques described in US Patent Application Publication 2012/0035712, which is assigned to the assignee of the present application and is incorporated herein by reference, with reference to FIGS. 1A-D thereof, mutatis mutandis, and/or using techniques described hereinbelow with reference to FIGS. 11-12C.

[0285] At the beginning of the procedure, tether-securing device 330 resides on inner shaft 382, such that the inner shaft holds locking pieces 341 in the constrained state, and tether-securing device 330 in the unlocked configuration. A distal end 386 of outer shaft 384 is held by the surgeon proximal to a proximal end of tether-securing device 330. Typically, tether-securing device 330 is delivered to a vicinity of the target site (e.g., to right atrium 81) with the at least one tether 350 pre-threaded through securing-device lumen 336.

[0286] As shown in FIG. 6A, first and second tissue anchors 352A and 352B are implanted at respective different implantation sites 370A and 370B, each of which sites is selected from the group of sites consisting of: an annulus of tricuspid valve 22, and a wall of the right atrium of the heart above the annulus. For applications in which first and second tissue anchors 52A and 52B comprise respective helical tissue-coupling elements, the helical tissue-coupling elements are rotated into tissue at the sites, respectively. Implantation techniques described hereinbelow with reference to FIGS. 11-12C may optionally be used. For example, first and second tissue anchors 352A and 352B may be implanted at diametrically opposed sites on the annulus of the tricuspid valve, e.g., as shown in FIGS. 6A-C, first tissue anchor 352A may be implanted within 1 cm of the site on the annulus that circumferentially corresponds to an anteroposterior commissure 112, and second tissue anchor 352B may be implanted within 1 cm of the site on the annulus that circumferentially corresponds to a circumferential middle 93 of septal leaflet 82. Alternatively, for some applications, first and second tissue anchors 352A and 352B are implanted (a) within 1 cm of the site on the annulus that circumferentially corresponds to a septoanterior commissure 114, and within 1 cm of the site on the annulus that circumferentially corresponds to a circumferential middle of posterior leaflet 84, respectively, or (b) within 1 cm of the site on the annulus that circumferentially corresponds to a circumferential middle of the annulus 87 along anterior leaflet 86, and within 1 cm of the site on the annulus that circumferentially corresponds to septoposterior commissure 117, respectively. The direction of the 1 cm from the described anatomical sites may be either circumferentially around the annulus, up the wall of right atrium 81 above annulus 83, or a combination of circumferentially around the annulus and up the wall of the atrium.

[0287] A size of a tricuspid valve orifice is reduced by tensioning tether 350, so as to reduce regurgitation. Such tensioning may be performed by distally advancing inner shaft 382 while proximally pulling on looped middle portion 388 of tether 350 (shown and labeled in FIG. 6C), such that portions of tether 350 pass through inner shaft 382 and unlocked tether-securing device 330 mounted thereon. For example, a flexible longitudinal guide member 390 may be removably coupled to looped middle portion 388 by a loop 780, such as a ring, using techniques described in US Patent Application Publication 2013/0018459, which is assigned to the assignee of the present application and is incorporated herein by reference, with reference to FIGS. 23-26 thereof, mutatis mutandis (in which flexible longitudinal guide member 2616 corresponds to flexible longitudinal guide member 390 of the present application).

[0288] After tether 350 has been tensioned, tether-securing device 330 is transitioned to the one-way-locked configuration, by holding tether-securing device 330 in place by holding inner shaft 382 in place, and distally advancing outer shaft 384, as shown in FIG. 6B. Tether-securing device 330 is pushed distally by outer shaft 384 over inner shaft 382 until locking pieces 341 are no longer constrained by inner shaft 382, such that tether-securing device 330 automatically transitions to the one-way-locked configuration (in which locking pieces 341 are in a relaxed, resting state). Since tether-securing device 330 allows proximal sliding of tether 350 therethrough even when in the one-way-locked configuration, if necessary further tension can be applied to tether 350 by pushing tether-securing device 330 distally using outer shaft 384. Once the tension has been applied, tether-securing device 330 maintains the tension.

[0289] FIG. 6C shows valve-tensioning implant system 320 after tension has been applied and tether-securing device 330 has been fully deployed. The final disposition of an excess portion 394 of tether 350 near looped middle portion 388 is described hereinbelow with reference to FIGS. 8A-C.

[0290] Reference is now made to FIGS. 8A-C, which are schematic illustrations of techniques for securing excess portion 394 of tether 350, in accordance with respective applications of the present invention. As shown in FIG. 6C, after tether 350 has been tensioned, excess portion 394 of tether 350 near looped middle portion 388 remains free in right atrium 81. It is generally undesirable to leave this excess portion free to move around in the atrium.

[0291] In some applications of the present invention, valve-tensioning implant system 320 further comprises a venous tissue anchor 400, for holding excess portion 394 secured in a desired disposition in the vasculature of right atrium 81. Venous tissue anchor 400 is configured to be implanted at an implantation site upstream of the tricuspid valve. FIGS. 8A, 8B, and 8C show venous tissue anchor 400 disposed in inferior vena cava 74, superior vena cava 76, and coronary sinus 115, respectively. Venous tissue anchor 400 is connected to excess portion 394 by a fixation tether 404, which may be connected to excess portion 394 by a loop 780, such as a ring. Such connection is typically made after the tissue anchors have been implanted and tension has been applied to tether 350, as described hereinabove with reference to FIGS. 6A-C. For some applications, such connection is made using techniques described in above-mentioned US Patent Application Publication 2013/0018459, with reference to FIGS. 23-26 thereof, mutatis mutandis. It is noted that in this configuration, venous tissue anchor 400 is deployed such that only a moderate amount of tension is applied to fixation tether 404, which tension is insufficient to alter the geometry of the atrium.

[0292] By way of example and not limitation, in the deployment configuration shown in FIG. 8A, first tissue anchor 352A is implanted within 1 cm of the site on the annulus that circumferentially corresponds to septoanterior commissure 114, and second tissue anchor 352B is implanted within 1 cm of the site on the annulus that circumferentially corresponds to septoposterior commissure 117. By way of example and not limitation, in the deployment configuration shown in FIG. 8B, first tissue anchor 352A is implanted within 1 cm of the site on the annulus that circumferentially corresponds to anteroposterior commissure 112, and second tissue anchor 352B is implanted within 1 cm of the site on the annulus that circumferentially corresponds to circumferential middle 93 of septal leaflet 82. By way of example and not limitation, in the deployment configuration shown in FIG. 8C, first tissue anchor 352A is implanted within 1 cm of the site on the annulus that circumferentially corresponds to anteroposterior commissure 112, and second tissue anchor 352B is implanted within 1 cm of the site on the annulus that circumferentially corresponds to septoanterior commissure 114. The direction of the 1 cm from the described anatomical sites may be either circumferentially around the annulus, up the wall of right atrium 81 above annulus 83, or a combination of circumferentially around the annulus and up the wall of the atrium.

[0293] For some applications, venous tissue anchor 400 comprises an intraluminal stent 402. The stent is configured to be implanted in the vein by applying an outward radial force to the wall of the vein. Typically, the stent is configured to self-expand.

[0294] For example, the stent may comprise a shape-memory alloy, such as Nitinol. Alternatively, the stent comprises a deformable metal, and is expanded by a tool, such as a balloon. For some applications, stent 402 comprises a plurality of interconnected superelastic metallic struts, arranged so as to allow crimping the stent into a relatively small diameter (typically less than 8 mm) catheter, while allowing deployment to a much larger diameter (typically more than 20 mm) in the vein, while still maintaining radial force against the tissue of the wall of the vein, in order to anchor stent 402 to the wall of the vein by friction. Typically, the stent is configured to not penetrate tissue of the wall of the vein. For some applications, stent 402 implements techniques described in U.S. Provisional Application 61/783,224, filed Mar. 14, 2013, which is assigned to the assignee of the present application and is incorporated herein by reference.

[0295] For applications in which venous tissue anchor 400 is implanted in superior vena cava 76 or inferior vena cava 78, intraluminal stent 402 typically has a greatest outer diameter of at least 20 mm, no more than 50 mm, and/or between 20 and 50 mm, when unconstrained and fully radially expanded, i.e., no forces are applied to the stent by a delivery tool, walls of a blood vessel, or otherwise. For applications in which first venous tissue anchor 400 is implanted in coronary sinus 115, intraluminal stent 402 typically has a greatest outer diameter of at least 8 mm, no more than 15 mm, and/or between 8 and 15 mm, when unconstrained and fully radially expanded.

[0296] Alternatively, excess portion 394 is cut and removed from the atrium, such as using techniques described hereinbelow with reference to FIG. 9, mutatis mutandis.

[0297] Reference is now made to FIG. 9, which is a schematic illustration of a valve-tensioning implant system 420, in accordance with an application of the present invention. Except as described below, implant system 420 is the same as implant system 320, described hereinabove with reference to FIGS. 6A-C and 7A-B, and may incorporate any of the features thereof. In this configuration, the at least one tether 350 of implant system 420 comprises first and second tethers 350A and 350B, which (a) have first tether end portion 354A and a second tether end portion 354B, respectively, and (b) pass through the portion of securing-device lumen 336. Second tissue anchor 352B is connected (e.g., permanently fixed) to second tether end portion 354B.

[0298] For some applications, after tension is applied to first and second tethers 350A and 350B and tether-securing device 330 has been transitioned to the one-way-locked configuration, excess portions 494 of tethers 350A and 350B are cut and removed from the atrium, using cutting tool 498. Alternatively, excess portions 494 are held in a desired disposition, such as using techniques described hereinabove with reference to FIGS. 8A-C, mutatis mutandis.

[0299] Reference is made to FIGS. 6A-C and 9. For applications in which the at least one tether 350 comprises single tether 350, such as exactly one tether 350 (as shown in FIGS. 6A-C), the single tether typically has a length, measured between first tissue anchor 352A and second tissue anchor 352B, of at least 30 mm, no more than 160 mm, and/or between 30 and 160 mm. For some applications, looped middle portion 388 has a length, measured along tether 350 (i.e., if the looped middle portion were to be straightened), of at least 5 mm. For application in which the at least one tether 350 comprises two tethers 350A and 350B, such as shown in FIG. 9, each of tethers 350 typically has a length of at least 20 mm, no more than 80 mm, and/or between 20 and 80 mm. Because each tether 350 typically has a high tensile strength, the length thereof does not vary based on the particular disposition of the tether at any given point in time. In other words, the length of the tether does not depend on the amount of force applied to it.

[0300] Reference is now made to FIGS. 10A-D, which are schematic illustrations of friction-enhancing features of a tether 550, in accordance with respective applications of the present invention. These features may be used with tethers 50 or 350, in any of the configurations described herein with reference to FIGS. 1-2, 3, 4A-5, 6A-8C, and 9. The friction-enhancing features enhance friction between the tethers and one-way locking opening 38 of tether-securing device 30, or proximal edges 343A and 343B of locking pieces 341 of tether-securing device 330, as the case may be.

[0301] Typically, tether 550 defines a plurality of securement protrusions 560 spaced at intervals (I) along tether 550, which protrusions serve as the friction-enhancing features. The protrusions may also serve to ratchet the tether unidirectionally through one-way locking opening 38 of tether-securing device 30, or proximal edges 343A and 343B of locking pieces 341 of tether-securing device 330, as the case may be. For some applications, an average interval of securement protrusions 560 along tether 550 is at least 1 mm, no more than 5 mm, and/or between 1 and 5 mm.

[0302] For some applications, protrusions 560 are defined by respective knots 570 in tether 550, such as shown in FIG. 10A. For some applications, protrusions 560 comprise respective cones 572 on tether 550, such as shown in FIG. 10B. For some applications, protrusions 560 comprise respective scales 574 on tether 550, such as shown in FIG. 10C. For some applications, protrusions 560 comprise respective beads 576 on tether 550, such as shown in FIG. 10D.

[0303] Reference is now made to FIG. 11, which is a schematic illustration of a delivery system comprising a multiple-anchor delivery tool 600, in accordance with an application of the present invention. Multiple-anchor delivery tool 600 is used to sequentially deliver and implant two or more tissue anchors of an implant system, such as implant systems 20, 120, 220, 320, and 420, described hereinabove. Although multiple-anchor delivery tool 600 is illustrated and described below with reference to implant system 320 (and thus is one implementation of delivery tool 380), described hereinabove with reference to FIGS. 6A-7B, the delivery tool may be used for delivering the other implant systems described herein, mutatis mutandis.

[0304] For some applications, implant system 320 comprises a male coupling 680 of a first flexible-longitudinal-member-coupling element 682 of an intraluminal locking mechanism 684 which is connected to a female coupling during implantation, such as in order to allow implantation of the third tissue anchor with a separate catheter delivery system, such as described in above-mentioned US Patent Application Publication 2013/0018459, for example with reference to FIGS. 25-26 thereof.

[0305] Multiple-anchor delivery tool 600 comprises outer shaft 384 and inner shaft 382. Inner shaft 382 has proximal and distal ends 610 and 612. First and second tissue anchors 352A and 352B are initially removably positioned in inner shaft 382 at first and second longitudinal locations 614 and 616, respectively. First longitudinal location 614 is more distal than second longitudinal location 616. In other words, the tissue anchors are initially positioned in the desired sequence of deployment in inner shaft 382, with the first anchor to be deployed positioned more distally than the subsequent anchor(s) to be deployed. The tissue anchors are interconnected by tether 350.

[0306] Multiple-anchor delivery tool 600 further comprises first and second torque cables 620 and 622, which (a) are removably coupled to first and second heads 670A and 670B of first and second tissue anchors 352A and 352B, respectively, (b) extend within inner shaft 382 proximally from first and second heads 670A and 670B, respectively, and (c) transmit torque when rotated, for rotating tissue-coupling elements 648A and 648B of first and second tissue anchors 352A and 352B, respectively, into tissue. Typically, the torque cables additionally transmit axial force, to enable pushing of the tissue-coupling elements 648A and 648B into the tissue as they are rotated. A portion 630 of first torque cable 620 is initially removably positioned alongside second tissue anchor 352B in inner shaft 382. Thus each anchor is separately connected to a control handle 770 by its own torque cable, which allows full and separate control of deployment of each anchor by an operator of the multiple-anchor delivery tool.

[0307] For some applications, implant system 320 comprises one or more additional tissue anchors, and tool 600 correspondingly comprises one or more additional torque cables, removably coupled to the tissue coupling elements, as described herein. These additional tissue anchors are initially removably positioned in inner shaft 382 proximal to second longitudinal location 616. For example, implant system 320 may further comprise a third tissue anchor, which comprises (a) a third helical tissue coupling elements, and (b) a third head, which comprises a third tether interface; the tether is coupled to (e.g., slidably coupled to) the third tether interface; the third tissue anchor is removably positioned in inner shaft 382 at a third longitudinal location that is more proximal than second longitudinal location 616; and multiple-anchor delivery tool 600 further comprises a third torque cable, which (a) is removably coupled to the third head, (b) extends within the inner shaft proximally from the third head, and (c) transmits torque when rotated, wherein a portion of the second torque cable is removably positioned alongside the third tissue anchor in the inner shaft.

[0308] For some applications, first torque cable 620 is shaped so as to define a lumen 640 therethrough, and multiple-anchor delivery tool 600 further comprises a sharpened wire 642, which removably passes through lumen 640. A distal end of first torque cable 620 comprises a distal coupling element 650, which is configured to be removably coupled to a corresponding proximal coupling element 652 defined by a proximal portion of first head 670A. Distal and proximal coupling elements 650 and 652 are shaped so as to define corresponding interlocking surfaces, such that the coupling elements interlock, thereby mating the coupling elements to one another. First head 670A, including proximal coupling element 652, is shaped so as to define a first longitudinal channel 656 at least partially therethrough (typically entirely therethrough), which channel is coaxial with first head 670A. Distal coupling element 650 is shaped so as to define a second longitudinal channel 658 therethrough, which is coaxial with lumen 640 of first torque cable 620. First and second channels 656 and 658 are radially aligned with one another. When a portion of sharpened wire 642 is positioned in these channels, the sharpened wire prevents decoupling of distal coupling element 650 from proximal coupling element 652. Upon removal of sharpened wire 642 from channels 656 and 658 and the coupling elements 650 and 652, the coupling elements are free to be decoupled from one another.

[0309] For some applications, sharpened wire 642 is shaped so as to define a sharp distal tip 660. For these applications, first tissue anchor 352A typically is helical, and sharpened wire 642 is initially removably positioned within a channel defined by the helix. As tissue anchor 352A is screwed into tissue, sharpened wire 642 penetrates and advances into the tissue along with the anchor to a certain depth in the tissue. For some applications, when the shaft penetrates to the certain depth, the sharpened wire is withdrawn slightly. Typically, after tissue anchor 352A has been fully implanted, sharpened wire 642 is withdrawn entirely from the tissue, and removed from the patient's body. Optionally, the sharp distal tip of sharpened wire 642 is inserted into the tissue slightly, even before insertion of tissue anchor 352A, in order to prevent sliding of the tissue-coupling element on the surface of the tissue before commencement of insertion of the tissue-coupling element into the tissue.

[0310] After implantation of tissue anchor 352A, sharpened wire 642 is withdrawn proximally from the channel of tissue anchor 352A and from channels 656 and 658 of distal and proximal coupling elements 650 and 652, thereby decoupling the coupling elements from one another, and decoupling first torque cable 620 from first head 670A. After such proximal withdrawal, sharpened wire 642 typically remains within lumen 640 of first torque cable 620.

[0311] For some applications, the decoupling of first torque cable 620 and first head 670A is performed alternatively or additionally using techniques described in US Patent Application Publication 2012/0035712, which is assigned to the assignee of the present application and is incorporated herein by reference, such as with reference to FIGS. 12A-C thereof.

[0312] Second torque cable 622 and second tissue anchor 352B similarly comprise the above-mentioned elements (e.g., the sharpened wire and coupling elements), and are similarly configured, as do any additional torque cables and tissue anchors that may be provided, as described above.

[0313] Multiple-anchor delivery tool 600 further comprises control handle 770, which is configured to control the deployment of the tissue anchors, by rotating the torque cables, distally advancing the anchors through inner shaft 382, and proximally withdrawing the sharpened wires and torque cables. Control handle 770 may implement features of handle portion 1004, described with reference to FIG. 11C of above-mentioned US Patent Application Publication 2012/0035712, mutatis mutandis.

[0314] Reference is now made to FIGS. 12A-C, which are schematic illustrations of a deployment method using multiple-anchor delivery tool 600, in accordance with an application of the present invention. Although this method is described for deploying first and second tissue anchors 352A and 352B, the method may also be used to deploy first and second tissue anchors 52A and 52B, first and second tissue anchors 252A and 252B, or first and second tissue anchors 352A and 352B, described hereinabove, or other tissue anchors. Inner shaft 382 and outer shaft 384 are typically advanced transvascularly, using a delivery system comprising one or more catheters introduced with the aid of a guidewire, through vasculature of the subject, such as (a) via the femoral vein, through inferior vena cava 74, and into right atrium 81, (b) via the basilic vein, through the subclavian vein through superior vena cava 76, and into right atrium 81, or (c) via the external jugular vein, through the subclavian vein through superior vena cava 76, and into right atrium 81. The procedure is typically performed with the aid of imaging, such as fluoroscopy, transesophageal, transthoratic echocardiography, IVUS, and/or echocardiography. The procedure may be performed using techniques described in US Patent Application Publication 2012/0035712, which is assigned to the assignee of the present application and is incorporated herein by reference, with reference to FIGS. 1A-D thereof, mutatis mutandis.

[0315] Distal end 612 of inner shaft 382 of multiple-anchor delivery tool 600 is advanced into a body of a subject, while (a) first and second tissue anchors 352A and 352B are removably positioned in inner shaft 382 at first and second longitudinal locations 614 and 616, respectively, first longitudinal location 614 more distal than second longitudinal location 616. Portion 630 of first torque cable 620 is removably positioned alongside second tissue anchor 352B in inner shaft 382. Thus, inner shaft 382 does not need to be withdrawn and reintroduced from the body during the implantation procedure.

[0316] As shown in FIG. 12A, first tissue anchor 352A is implanted into tissue 700 of the subject (e.g., cardiac muscle tissue, such as atrial tissue) by rotating first torque cable 620, using control handle 770, and, typically pushing distally on the torque cable.

[0317] As shown in FIG. 12B, after first tissue anchor 352A has been fully implanted in tissue 700, first torque cable 620 is decoupled from first tissue anchor 352A, such as by proximally withdrawing sharpened wire 642, as described hereinabove with reference to FIG. 11. First torque cable 620 is typically further proximally withdrawn in inner shaft 382 (not shown), and optionally withdrawn out of the proximal end of the inner shaft.

[0318] As shown in FIG. 12C, after first tissue anchor 352A is implanted, second tissue anchor 352B is distally advanced in inner shaft 382, and implanted into tissue 700 by rotating second torque cable 622. The second torque cable is decoupled from second tissue anchor 352B (not shown). First and second tissue anchors 352A and 352B remain implanted in tissue 700, connected by tether 350.

[0319] Tether 350 may be tensioned so as to apply tension between the first and the second tissue anchors, such as described hereinabove with reference to FIGS. 6A-C. For example, flexible longitudinal guide member 390 may be removably coupled to looped middle portion 88 of tether 350 by loop 780, such as a ring, which is connected to first flexible-longitudinal-member-coupling element 682, which may be coupled to the female part of the locking mechanism using a separate catheter delivery system, such as described in above-mentioned US Patent Application Publication 2013/0018459, for example with reference to FIGS. 25-26 thereof. After tether 350 is tensioned, tether-securing device 330 is deployed to its one-way-locked configuration, in order to maintain the tension, using outer shaft 384, as described hereinabove with reference to FIG. 6C. Once the tension has been applied, tether-securing device 330 maintains the tension.

[0320] The scope of the present invention includes embodiments described in the following applications, which are assigned to the assignee of the present application and are incorporated herein by reference. In an embodiment, techniques and apparatus described in one or more of the following applications are combined with techniques and apparatus described herein: [0321] U.S. Pat. No. 8,475,525 to Maisano et al.; [0322] International Application PCT/IL2011/000064, filed Jan. 20, 2011, which published as PCT Publication WO 2011/089601, and U.S. application Ser. No. 13/574,088 in the national stage thereof, which published as US Patent Application Publication 2013/0046380; [0323] U.S. application Ser. No. 13/188,175, filed Jul. 21, 2011, which published as US Patent Application Publication 2012/0035712; [0324] U.S. application Ser. No. 13/485,145, filed May 31, 2012, which published as US Patent Application Publication 2013/0325115; [0325] U.S. application Ser. No. 13/553,081, filed Jul. 19, 2012, which published as US Patent Application Publication 2013/0018459; [0326] International Application PCT/IL2012/000282, filed Jul. 19, 2012, which published as PCT Publication WO 2013/011502; [0327] U.S. Provisional Application 61/750,427, filed Jan. 9, 2013; [0328] U.S. Provisional Application 61/783,224, filed Mar. 14, 2013; [0329] International Application PCT/IL2013/050470, filed May 30, 2013, which published as PCT Publication WO 2013/179295; [0330] U.S. Provisional Application 61/897,509, filed Oct. 30, 2013; [0331] U.S. application Ser. No. 14/143,355, filed Dec. 30, 2013, which published as US Patent Application Publication 2014/0114390; [0332] International Application PCT/IL2014/050027, filed Jan. 9, 2014, which published as PCT Publication WO 2014/108903; [0333] International Application PCT/IL2014/050233, filed Mar. 9, 2014, which published as PCT Publication WO 2014/141239; and [0334] U.S. Provisional Application 62/014,397, filed Jun. 19, 2014.

[0335] In particular, the stents described herein may be used as one or more of the stents described in the above-listed applications, in combination with the other techniques described therein.

[0336] It will be appreciated by persons skilled in the art that the present invention is not limited to what has been particularly shown and described hereinabove. Rather, the scope of the present invention includes both combinations and subcombinations of the various features described hereinabove, as well as variations and modifications thereof that are not in the prior art, which would occur to persons skilled in the art upon reading the foregoing description.