US20180344311A1 - Percutaneous Tether Locking - Google Patents
Percutaneous Tether Locking Download PDFInfo
- Publication number
- US20180344311A1 US20180344311A1 US16/035,654 US201816035654A US2018344311A1 US 20180344311 A1 US20180344311 A1 US 20180344311A1 US 201816035654 A US201816035654 A US 201816035654A US 2018344311 A1 US2018344311 A1 US 2018344311A1
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- United States
- Prior art keywords
- tether
- tissue
- anchor
- applications
- catheter shaft
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/04—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials
- A61B17/0401—Suture anchors, buttons or pledgets, i.e. means for attaching sutures to bone, cartilage or soft tissue; Instruments for applying or removing suture anchors
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/04—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials
- A61B17/0487—Suture clamps, clips or locks, e.g. for replacing suture knots; Instruments for applying or removing suture clamps, clips or locks
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/00234—Surgical instruments, devices or methods, e.g. tourniquets for minimally invasive surgery
- A61B2017/00238—Type of minimally invasive operation
- A61B2017/00243—Type of minimally invasive operation cardiac
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B2017/00743—Type of operation; Specification of treatment sites
- A61B2017/00778—Operations on blood vessels
- A61B2017/00783—Valvuloplasty
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/04—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials
- A61B17/0401—Suture anchors, buttons or pledgets, i.e. means for attaching sutures to bone, cartilage or soft tissue; Instruments for applying or removing suture anchors
- A61B2017/0409—Instruments for applying suture anchors
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/04—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials
- A61B17/0401—Suture anchors, buttons or pledgets, i.e. means for attaching sutures to bone, cartilage or soft tissue; Instruments for applying or removing suture anchors
- A61B2017/044—Suture anchors, buttons or pledgets, i.e. means for attaching sutures to bone, cartilage or soft tissue; Instruments for applying or removing suture anchors with a threaded shaft, e.g. screws
- A61B2017/0441—Suture anchors, buttons or pledgets, i.e. means for attaching sutures to bone, cartilage or soft tissue; Instruments for applying or removing suture anchors with a threaded shaft, e.g. screws the shaft being a rigid coil or spiral
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/04—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials
- A61B17/0401—Suture anchors, buttons or pledgets, i.e. means for attaching sutures to bone, cartilage or soft tissue; Instruments for applying or removing suture anchors
- A61B2017/0446—Means for attaching and blocking the suture in the suture anchor
- A61B2017/0461—Means for attaching and blocking the suture in the suture anchor with features cooperating with special features on the suture, e.g. protrusions on the suture
- A61B2017/0462—One way system, i.e. also tensioning the suture
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/04—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials
- A61B17/0401—Suture anchors, buttons or pledgets, i.e. means for attaching sutures to bone, cartilage or soft tissue; Instruments for applying or removing suture anchors
- A61B2017/0464—Suture anchors, buttons or pledgets, i.e. means for attaching sutures to bone, cartilage or soft tissue; Instruments for applying or removing suture anchors for soft tissue
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/04—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials
- A61B17/0487—Suture clamps, clips or locks, e.g. for replacing suture knots; Instruments for applying or removing suture clamps, clips or locks
- A61B2017/0488—Instruments for applying suture clamps, clips or locks
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/04—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials
- A61B2017/0496—Surgical instruments, devices or methods, e.g. tourniquets for suturing wounds; Holders or packages for needles or suture materials for tensioning sutures
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
Definitions
- Some applications of the present invention relate in general to valve repair. More specifically, some applications of the present invention relate to repair of an atrioventricular valve of a patient.
- Functional tricuspid regurgitation is governed by several pathophysiologic abnormalities such as tricuspid valve annular dilatation, annular shape abnormality, pulmonary hypertension, left or right ventricle dysfunction, right ventricle geometry, and leaflet tethering.
- pathophysiologic abnormalities such as tricuspid valve annular dilatation, annular shape abnormality, pulmonary hypertension, left or right ventricle dysfunction, right ventricle geometry, and leaflet tethering.
- Treatment options for FTR are primarily surgical.
- the current prevalence of moderate-to-severe tricuspid regurgitation is estimated to be 1.6 million in the United States. Of these, only 8,000 patients undergo tricuspid valve surgeries annually, most of them in conjunction with left heart valve surgeries.
- Some embodiments of the present invention provide techniques for tightening tethers of percutaneous implants transluminally, in order to enable percutaneous treatment of functional tricuspid regurgitation (FTR).
- FTR functional tricuspid regurgitation
- techniques are provided for fixing two or more tethers to each other, or two portions of a single tether to one another, in order to apply and maintain tension between two or more tissue anchors implanted in tissue of a subject.
- a tether-securing device comprises a serrated tubular element that allows passage of one or more tethers or longitudinal portions of tethers band in one direction, but inhibits (e.g., prevents) the return of the tether(s) in the opposite direction.
- a tether-securing device is configured to assume an unlocked configuration, in which one or more tethers are generally slidable through the device, and a one-way-locked configuration, in which the tether(s) are slidable only in one direction through the device.
- the tether-securing device is configured to be biased to assume the one-way-locked configuration thereof, and is retained in the unlocked configuration by a constraint.
- the devices automatically transition to the one-way-locked configuration when the constraint is removed.
- a delivery system for implanting the implant also comprises a tool for shearing off and retrieving the excess material, such as thoracoscopic scissors, as known in the art.
- excess portions of the tether(s) are held in place by a fixation device such as a stent, which is placed in the vasculature leading to the atrium, such as the superior vena cava (SVC), the inferior vena cava (IVC), or the coronary sinus (CS).
- a fixation device such as a stent, which is placed in the vasculature leading to the atrium, such as the superior vena cava (SVC), the inferior vena cava (IVC), or the coronary sinus (CS).
- the delivery system is configured to connect the excess material to the fixation device.
- tether-securing devices to repair a heart valve, by fixedly coupling together textile bands that are coupled to different parts of an annulus of a heart valve.
- apparatus including:
- At least one tether having first and second tether end portions
- first and second tissue anchors fixed to the first and the second tether end portions, respectively;
- a tether-securing device which includes:
- tether-securing device is configured:
- the locking pieces are configured to allow the proximal sliding when in the relaxed state.
- the locking pieces are convex, as viewed from outside the tether-securing device, at least when the locking pieces are in the relaxed state.
- the tubular element is cylindrical.
- the locking pieces are integral with the tubular element.
- the three or more locking pieces include exactly three locking pieces or exactly four locking pieces.
- the lumen is a securing-device lumen
- the apparatus further includes a delivery tool, which includes a catheter shaft, which (a) is configured to apply a constraining force to the locking pieces when the shaft is disposed in the securing-device lumen, which constraining force retains the tether-securing device in the unlocked configuration, and (b) is shaped so as to define a shaft lumen, through which the at least one tether removably slidably passes.
- a total axial length of the tether-securing device, when the locking pieces are in the relaxed state is between 3 and 50 mm.
- each of the locking pieces may be shaped so as to define two curved edges that meet at a proximal tip.
- the proximal edges are shaped so as to define uneven edge surfaces.
- the uneven edge surfaces are shaped so as define teeth.
- the uneven edge surfaces are rough.
- the at least one tether defines a plurality of securement protrusions spaced at intervals along the at least one tether.
- the protrusions are defined by respective knots in the at least one tether.
- the protrusions include respective elements selected from the group consisting of: cones, scales, and beads.
- an average interval of the securement protrusions is between 1 and 5 mm.
- the at least one tether may include first and second tethers, which have the first and the second tether end portions, respectively.
- a single tether of the at least one tether may have the first and the second tether end portions, and the single tether may include at least the following non-overlapping longitudinal portions disposed in sequence along the single tether:
- the apparatus further includes a fixation tether, which is connected to the looped middle portion of the single tether.
- the apparatus further includes a venous tissue anchor, which is configured to be implanted in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus, and which is connected to the fixation tether.
- the venous tissue anchor includes a stent.
- the apparatus further includes:
- a venous tissue anchor which is configured to be implanted in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus; and
- fixation tether which is connected to the venous tissue anchor and the at least one tether.
- the venous tissue anchor includes a stent.
- apparatus including:
- a tether-securing device which includes a tubular element, which is shaped so as define a lateral wall that surrounds a lumen, wherein the lateral wall is shaped so as to define a one-way locking opening;
- At least one tether which (a) has at least a first tether end portion, and (b) passes through the lumen and the one-way locking opening;
- first and second tissue anchors wherein the first tissue anchor is connected to the first tether end portion
- the one-way locking opening is configured to (a) allow sliding of the at least one tether in a first direction through the one-way locking opening, and (b) inhibit sliding of the at least one tether in a second direction opposite the first direction.
- the one-way locking opening is shaped as a slit.
- the first direction is from inside the tubular element to outside the tubular element.
- the tubular element is cylindrical.
- an axial length of the tubular element is between 5 and 20 mm.
- the one-way locking opening may have uneven edges.
- the uneven edges are jagged or serrated.
- the at least one tether may define a plurality of securement protrusions spaced at intervals along the at least one tether.
- the protrusions are defined by respective knots in the at least one tether.
- the protrusions include respective elements selected from the group consisting of: cones, scales, and beads.
- an average interval of the securement protrusions is between 1 and 5 mm.
- a single tether of the at least one tether may have the first tether end portion and a second tether end portion, which second tether end portion is connected to the second tissue anchor, and the single tether may include at least the following non-overlapping longitudinal portions disposed in sequence along the single tether:
- the lateral wall is shaped so as to define first and second non-constraining openings, which are sized and shaped to allow free sliding therethrough of two longitudinal portions, respectively, of the single tether.
- the non-constraining openings are shaped as respective slits.
- the apparatus further includes a fixation tether, which is connected to the looped middle portion of the single tether.
- the apparatus further includes a venous tissue anchor, which is configured to be implanted in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus, and which is connected to the fixation tether.
- the venous tissue anchor includes a stent.
- the second tissue anchor may include a head and a tissue-coupling element, and the tether-securing device is fixed to the head, such that the tether-securing device surrounds at least a portion of the head.
- the tether-securing device is configured to rotate with respect to the head.
- the lateral wall is shaped so as to define a non-constraining opening, which is sized and shaped to allow free sliding therethrough of the at least one tether.
- the non-constraining opening is shaped as a slit.
- the at least one tether may include first and second tethers, which (a) have the first tether end portion and a second tether end portion, respectively, and (b) pass through (i) the lumen and (ii) the one-way locking opening,
- the second tissue anchor may be connected to the second tether end portion
- the one-way locking opening may be configured to (a) allow the sliding of the first and the second tethers in the first direction through the one-way locking opening, and (b) inhibit the sliding of the first and the second tethers in the second direction.
- the lateral wall is shaped so as to define first and second non-constraining openings, which are sized and shaped to allow free sliding therethrough of the first and the second tethers, respectively.
- the non-constraining openings are shaped as respective slits.
- the apparatus may further include:
- a venous tissue anchor which is configured to be implanted in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus; and
- fixation tether which is connected to the venous tissue anchor and the at least one tether.
- the venous tissue anchor includes a stent.
- apparatus including:
- a tether having first and second tether end portions
- first and second tissue anchors fixed to the first and the second tether end portions, respectively;
- the tether includes at least the following non-overlapping longitudinal portions disposed in sequence along the tether:
- the looped middle portion extends out of and away from the tether-securing device such that a longitudinal center of the looped middle portion is not in direct physical contact with any portion of the tether-securing device.
- the tether-securing device is configured to assume:
- tether-securing device inhibits the distal sliding more than when in the unlocked configuration.
- the tether-securing device is configured to assume:
- the tether-securing device is configured to (a) allow sliding of the first and the second portions of the tether in a first direction through the tether-securing device, and (b) inhibit sliding of the first and the second portions of the tether in a second direction opposite the first direction.
- the apparatus may further include a fixation tether, which is connected to the looped middle portion of the tether.
- the apparatus further includes a venous tissue anchor, which is configured to be implanted in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus, and which is connected to the fixation tether.
- the venous tissue anchor includes a stent.
- apparatus including:
- an implant which includes:
- a multiple-anchor delivery tool which includes:
- the implant further includes a third tissue anchor, which includes (a) a third helical tissue coupling elements and (b) a third head, which includes a third tether interface,
- 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
- 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, and a portion of the second torque cable is removably positioned alongside the third tissue anchor in the catheter shaft.
- 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, and a portion of the second torque cable is removably positioned alongside the third tissue anchor in the catheter shaft.
- the first tether interface is rotatable with respect to the first tissue-coupling element.
- the first torque cable may be shaped so as to define a lumen therethrough, and the multiple-anchor delivery tool may further include a shaft, which removably passes through the lumen.
- the head is shaped so as to define a proximal coupling element
- 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,
- 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,
- proximal and the distal coupling elements are shaped so as to define corresponding interlocking surfaces
- the shaft when disposed through the first and the second channels, prevents decoupling of the distal coupling element from the proximal coupling element.
- the shaft is shaped so as to define a sharp distal tip.
- a tether-securing device which includes (i) a tubular element, which is shaped so as define a lumen through which the at least one tether passes, and has proximal and distal tube ends, and (ii) three or more locking pieces, which extend proximally from the proximal end of the tubular element;
- the locking pieces are configured to allow proximal sliding when in the relaxed state, and tensioning includes further tensioning the at least one tether by further proximally sliding the at least one tether through the lumen after transitioning the tether-securing device to the one-way-locked configuration.
- a single tether of the at least one tether has the first and the second tether end portions
- the single tether includes at least the following non-overlapping longitudinal portions disposed in sequence along the single tether:
- tensioning the tether includes proximally sliding the first and the second portions of the tether through the lumen by pulling on the looped middle portion.
- the method further includes connecting a fixation tether to the looped middle portion of the single tether.
- the method further includes implanting a venous tissue anchor, which is connected to the fixation tether, in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus.
- implanting the venous tissue anchor includes implanting a stent.
- the at least one tether includes first and second tethers, which have the first and the second tether end portions, respectively, and tensioning the at least one tether includes tensioning the first and the second tethers by proximally sliding the first and the second tethers through the lumen.
- each of the locking pieces is shaped so as to define two curved edges that meet at a proximal tip.
- the proximal edges are shaped so as to define uneven edge surfaces.
- the uneven edge surfaces are shaped so as define teeth.
- the uneven edge surfaces are rough.
- the locking pieces are convex, as viewed from outside the tether-securing device, at least when the locking pieces are in the relaxed state.
- the at least one tether defines a plurality of securement protrusions spaced at intervals along the at least one tether.
- the protrusions are defined by respective knots in the at least one tether.
- the protrusions include respective elements selected from the group consisting of: cones, scales, and beads.
- an average interval of the securement protrusions is between 1 and 5 mm.
- a total axial length of the tether-securing device, when the locking pieces are in the relaxed state is between 10 and 50 mm.
- the tubular element is cylindrical.
- the locking pieces are integral with the tubular element.
- the three or more locking pieces include exactly three locking pieces or exactly four locking pieces.
- the lumen is a securing-device lumen
- delivering the at least one tether and the tether-securing device includes delivering the at least one tether and the tether-securing device using a delivery tool, which includes a catheter shaft, which (a) applies a constraining force to the locking pieces when the shaft is disposed in the securing-device lumen, which constraining force retains the tether-securing device in the unlocked configuration, and (b) is shaped so as to define a shaft lumen, through which the at least one tether removably slidably passes, and
- transitioning the tether-securing device to a one-way-locked configuration includes removing the catheter shaft from the securing-device lumen.
- the method further includes:
- a venous tissue anchor in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus; and
- implanting the venous tissue anchor includes implanting a stent.
- a single tether of the at least one tether has the first tether end portion and a second tether end portion, which second tether end portion is connected to the second tissue anchor, and the single tether includes at least the following non-overlapping longitudinal portions disposed in sequence along the single tether:
- tensioning the tether includes proximally sliding the first and the second portions of the tether through the one-way locking opening in the first direction by pulling, in the first direction, on the looped middle portion.
- the lateral wall is shaped so as to define first and second non-constraining openings, which are sized and shaped to allow free sliding therethrough of two longitudinal portions, respectively, of the single tether, and
- sliding the tether through the one-way locking opening further includes sliding the two non-overlapping longitudinal portions of the tether through the first and the second non-constraining openings, respectively.
- the non-constraining openings are shaped as respective slits.
- the method further includes connecting a fixation tether to the looped middle portion of the single tether.
- the method further includes implanting a venous tissue anchor, which is connected to the fixation tether, in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus.
- implanting the venous tissue anchor includes implanting a stent.
- the second tissue anchor includes a head and a tissue-coupling element, and the tether-securing device is fixed to the head, such that the tether-securing device surrounds at least a portion of the head.
- the tether-securing device is configured to rotate with respect to the head.
- the lateral wall is shaped so as to define a non-constraining opening, which is sized and shaped to allow free sliding therethrough of the tether, and sliding the tether through the one-way locking opening further includes sliding the tether through the non-constraining opening.
- the non-constraining opening is shaped as a slit.
- the at least one tether includes first and second tethers, which (a) have the first tether end portion and a second tether end portion, respectively, and (b) pass through (i) the lumen and (ii) the one-way locking opening,
- the second tissue anchor is connected to the second tether end portion
- the one-way locking opening is configured to (a) allow the sliding of the first and the second tethers in the first direction through the one-way locking opening, and (b) inhibit the sliding of the first and the second tethers in the second direction, and
- tensioning the at least one tether includes tensioning the first and the second tethers by sliding the first and the second tethers in the first direction through the one-way locking opening.
- the lateral wall is shaped so as to define first and second non-constraining openings, which are sized and shaped to allow free sliding therethrough of the first and the second tethers, respectively,
- first and the second tethers slidably pass through the first and the second non-constraining openings, respectively
- sliding the first and the second tethers through the one-way locking opening further includes sliding the first and the second tethers through the first and the second non-constraining openings, respectively.
- the non-constraining openings are shaped as respective slits.
- the one-way locking opening is shaped as a slit.
- the first direction is from inside the tubular element to outside the tubular element.
- the one-way locking opening has uneven edges.
- the uneven edges are jagged or serrated.
- an axial length of the tubular element is between 5 and 20 mm.
- the tubular element is cylindrical.
- the at least one tether defines a plurality of securement protrusions spaced at intervals along the at least one tether.
- the protrusions are defined by respective knots in the at least one tether.
- the protrusions include respective elements selected from the group consisting of: cones, scales, and beads.
- an average interval of the securement protrusions is between 1 and 5 mm.
- the method further includes:
- a venous tissue anchor in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus; and
- implanting the venous tissue anchor includes implanting a stent.
- a tether having first and second tether end portions, (b) first and second tissue anchors, fixed to the first and the second tether end portions, respectively, and (c) a tether-securing device, wherein the tether includes at least the following non-overlapping longitudinal portions disposed in sequence along the tether: (i) the first tether end portion, (ii) a first portion that passes through the lumen, (iii) a looped middle portion that (1) extends out of and away from the tether-securing device and (2) then loops back to the tether-securing device, (iv) a second portion that passes through the tether-securing device, and (v) the second tether end portion;
- tensioning the tether by proximally sliding the first and the second portions of the tether through the tether-securing device by pulling on the looped middle portion.
- delivering the tether includes delivering the tether such that the looped middle portion extends out of and away from the tether-securing device, such that a longitudinal center of the looped middle portion is not in direct physical contact with any portion of the tether-securing device.
- the method further includes connecting a fixation tether to the looped middle portion of the tether.
- the method further includes implanting a venous tissue anchor, which is connected to the fixation tether, in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus.
- implanting the venous tissue anchor includes implanting a stent.
- the tether-securing device is configured to assume:
- tether-securing device inhibits the distal sliding more than when in the unlocked configuration.
- the tether-securing device is configured to assume:
- the tether-securing device is configured to (a) allow sliding of the first and the second portions of the tether in a first direction through the tether-securing device, and (b) inhibit sliding of the first and the second portions of the tether in a second direction opposite the first direction.
- 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
- first and the second tissue anchors include (i) first and second helical tissue coupling elements, respectively, and (ii) first and second heads, respectively, which include first and second tether interfaces, and (b) a tether, which is connected to the first tether interface, and is coupled to the second tether interface, is removably positioned in the catheter shaft
- 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
- the first torque cable is shaped so as to define a lumen therethrough
- the multiple-anchor delivery tool further includes a sharpened wire, which removably passes through the lumen, and which is initially positioned such that a distal end of the sharpened wire extends distally out of a distal end of the lumen, and
- the method further includes withdrawing the sharpened wire proximally.
- the head is shaped so as to define a proximal coupling element
- 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,
- 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,
- proximal and the distal coupling elements are shaped so as to define corresponding interlocking surfaces
- the sharpened wire when disposed through the first and the second channels, prevents decoupling of the distal coupling element from the proximal coupling element
- withdrawing the sharpened wire proximally includes decoupling the distal coupling element from the proximal coupling element by withdrawing the sharpened wire proximally.
- the sharpened wire is shaped so as to define a sharp distal tip.
- implanting the first tissue anchor includes inserting the sharp distal tip of the sharpened wire into the tissue.
- advancing includes 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, and the third tissue anchor includes (i) a third helical tissue coupling elements and (ii) a third head, which includes a third tether interfaces, (b) the tether is coupled to the third tether interface,
- 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, and a portion of the second torque cable is removably positioned alongside the third tissue anchor in the catheter shaft, and
- the method further includes:
- the first tether interface is rotatable with respect to the first tissue-coupling element.
- FIG. 1 is a schematic illustration of a valve-tensioning implant system, in accordance with an application of the present invention
- 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
- FIG. 3 is a schematic illustration of another valve-tensioning implant system, in accordance with an application of the present invention.
- FIGS. 4A-C are schematic illustrations of yet another valve-tensioning implant system, in accordance with an application of the present invention.
- 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
- FIGS. 6A-C are schematic illustration of still another valve-tensioning implant system, in accordance with an application of the present invention.
- 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
- 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 7 A-B, in accordance with respective applications of the present invention
- FIG. 9 is a schematic illustration of another valve-tensioning implant system, in accordance with an application of the present invention.
- FIGS. 10A-D are schematic illustrations of friction-enhancing features of a tether, in accordance with respective applications of the present invention.
- 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.
- 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.
- 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.
- 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 52 A and 52 B.
- first and second tissue anchors 52 A and 52 B are connected (e.g., permanently fixed) to first and second tether end portions 54 A and 54 B of the at least one tether 50 , respectively (typically first and second tissue anchors 52 A and 52 B 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.
- the at least one tether 50 has a high tensile strength, in order to enable the tether to apply tension, as described hereinbelow.
- first and second tether end portions 54 A and 54 B are configured so as to define anchor-fixing loops 68 A and 68 B, respectively, which pass through corresponding interfaces on first and second tissue anchors 52 A and 52 B, respectively, so as to connect (e.g., permanently fix) the tether end portions to the tissue anchors.
- 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 .
- one-way locking opening is shaped as a slit, as shown.
- the slit extends in a direction parallel to a longitudinal axis 39 of tubular element 32 .
- lateral wall 34 is shaped so as to define at least two pawls 40 A and 40 B, which together define one-way locking opening 38 .
- one-way locking opening has uneven edges, which, for example, may be jagged or serrated.
- 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 52 A and 52 B together, and resists the loosening of the anchors away from one another.
- the first direction is from inside the tubular element to outside the tubular element.
- pawls 40 A and 40 B are configured to open outwardly but not open inwardly.
- a single tether 50 of the at least one tether 50 has first and second tether end portions 54 A and 54 B.
- the at least one tether 50 may or may not comprise additional tethers in addition to the single tether.
- single tether 50 typically comprises at least the following non-overlapping longitudinal portions disposed in sequence along the single tether:
- Tether-securing device 30 thus fixes first and second portions 59 A and 59 B to each other.
- 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 52 A and 52 B are set during the procedure rather than preconfigured.
- 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.
- the at least one tether 50 comprises exactly one tether 50 .
- lateral wall 34 is shaped so as to define at least one non-constraining opening 60 , such as first and second non-constraining openings 60 A and 60 B, disposed at respective circumferential locations different from the circumferential location of one-way locking opening 38 .
- First and second non-constraining openings 60 A and 60 B are sized and shaped to allow free sliding therethrough of first and second longitudinal portions 62 A and 62 B of single tether 50 , respectively.
- first and second non-overlapping longitudinal portions 62 A and 62 B slidably pass through first and second non-constraining openings 60 A and 60 B, respectively.
- non-constraining openings 60 are shaped as respective slits (as shown), circles (not shown), or other shapes.
- the slits extend in a direction parallel to longitudinal axis 39 of tubular element 32 .
- tubular element 32 is cylindrical.
- the tubular element may have other hollow shapes such as rectangular, triangular, or hexagonal.
- an axial length of tubular element 32 is at least 5 mm, no more than 20 mm, and/or between 5 and 20 mm.
- first and second tissue anchor 52 A and 52 B comprise respective atrial tissue anchors.
- first and second tissue anchor 52 A and 52 B comprise respective helical tissue-coupling elements, which puncture and screw into cardiac muscle tissue.
- first and second tissue anchor 52 A and 52 B implement techniques described in U.S. Provisional Application 61/750,427, filed Jan. 9, 2013.
- each of first and second tissue anchors 52 A and 52 B 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.
- 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 .
- 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 ven
- 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 .
- First and second tissue anchor 52 A and 52 B are implanted at respective different second atrial sites 70 A and 70 B, 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.
- first and second tissue anchors 52 A and 52 B comprise respective helical tissue-coupling elements
- the helical tissue-coupling elements are rotated into tissue at the sites, respectively.
- 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.
- first tissue anchor 52 A 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 52 B 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.
- the size of the tricuspid valve orifice is reduced by tensioning tether 50 , so as to reduce regurgitation.
- 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 .
- a catheter shaft such as outer shaft 384 , described hereinbelow with reference to FIGS. 6A-C
- looped middle portion 88 of tether 50 such that portions of tether 50 are pulled through one-way locking opening 38 .
- a flexible longitudinal guide member 390 (as shown below in FIG.
- a loop 80 such as a ring
- a loop 80 such as a ring
- 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.
- 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 ).
- 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.
- excess portion 394 is cut and removed from the atrium, such as using techniques described hereinbelow with reference to FIG. 9 , mutatis mutandis.
- FIG. 3 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.
- the at least one tether 50 of implant system 120 comprises first and second tethers 50 A and 50 B, which (a) have first tether end portion 54 A and a second tether end portion 54 B, respectively, and (b) pass through (i) the portion of securing-device lumen 36 and (ii) the one-way locking opening 38 .
- Second tissue anchor 52 B is connected (e.g., permanently fixed) to second tether end portion 54 B.
- One-way locking opening 38 is configured to (a) allow the sliding of first and second tethers 50 A and 50 B 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 50 A and 50 B in the second direction.
- Tether-securing device 30 thus fixes the tethers 50 to each other.
- lateral wall 34 is shaped so as to define at least two non-constraining openings 60 , such as first and second non-constraining openings 60 A and 60 B, disposed at respective circumferential locations different from the circumferential location of one-way locking opening 38 .
- First and second non-constraining openings 60 A and 60 B are sized and shaped to allow free sliding therethrough of first and second tethers 50 A and 50 B, respectively.
- First and second tethers 50 A and 50 B slidably pass through first and second non-constraining openings 60 A and 60 B, respectively.
- non-constraining openings 60 are shaped as respective slits (as shown), circles (not shown), or other shapes.
- the slits extend in a direction parallel to longitudinal axis 39 of tubular element 32 .
- first and second tethers 50 A and 50 B 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 .
- 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.
- 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 52 A and second tissue anchor 52 B, of at least 30 mm, no more than 160 mm, and/or between 30 and 160 mm.
- 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.
- the at least one tether 50 comprises two tethers 50 A and 50 B, such as shown in FIG.
- 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.
- FIGS. 4A-C 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.
- 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 252 A and 252 B. 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.
- FIG. 5 is a schematic illustration of tether-securing device 230 fixed to second tissue anchor 252 B, in accordance with an application of the present invention.
- Second tissue anchor 252 B 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.
- 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.
- first tissue anchor 252 A is connected (e.g., permanently fixed) to first tether end portion 54 A of tether 50 .
- first tether end portion 54 A is configured so as to define anchor-fixing loop 68 A, which passes through a corresponding interface on first tissue anchor 52 A so as to connect (e.g., permanently fix) the tether end portion to the tissue anchor.
- a single tether 50 of the at least one tether 50 has first and second tether end portions 54 A and 54 B.
- 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 .
- the at least one tether 50 comprises exactly one tether 50 .
- 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 .
- non-constraining opening 60 is shaped as a slit (as shown), a circle (not shown), or another shape.
- the slit extends in a direction parallel to longitudinal axis 39 of tubular element 32 of tether-securing device 230 .
- 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 .
- 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
- 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 .
- First and second tissue anchor 252 A and 252 B are implanted at respective different second atrial sites 270 A and 270 B, 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.
- first and second tissue anchors 252 A and 252 B 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.
- first tissue anchor 252 A may be implanted within 1 cm of the point on the annulus that circumferentially corresponds to septoposterior commissure 117
- second tissue anchor 352 B 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 252 A may be implanted within 1 cm of the point on the annulus that circumferentially corresponds to anteroposterior commissure 112
- second tissue anchor 252 B 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.
- the size of the tricuspid valve orifice is reduced by tensioning tether 50 , so as to reduce regurgitation.
- tensioning may be performed by proximally pulling on second tether end portion 54 B of tether 50 , such that a portion of tether 50 is pulled through one-way locking opening 38 .
- a flexible longitudinal guide member 390 (as shown below in FIG. 6C ) may be removably coupled to second tether end portion 54 B 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).
- an excess portion 294 of tether 50 remains free in right atrium 81 . It is generally undesirable to leave this excess portion free to move around in the atrium.
- 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 ).
- 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.
- Fixation tether 404 is connected, typically during the implantation procedure, to tether end portion 54 B, such as by loop 180 , e.g., a ring.
- loop 180 e.g., a ring.
- 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.
- FIGS. 6A-C 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.
- 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 352 A and 352 B.
- first and second tissue anchors 352 A and 352 B are connected (e.g., permanently fixed) to first and second tether end portions 354 A and 354 B of the at least one tether 350 , respectively (typically first and second tissue anchors 352 A and 352 B are connected to first and second ends of the at least one tether 350 , respectively).
- first and second tether end portions 354 A and 354 B are configured so as to define anchor-fixing loops 368 A and 368 B, respectively, which pass through corresponding interfaces on first and second tissue anchors 352 A and 352 B, respectively, so as to connect (e.g., permanently fix) the tether end portions to the tissue anchors.
- FIGS. 7A and 7B 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.
- 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:
- a single tether 350 of the at least one tether 350 has first and second tether end portions 354 A and 354 B.
- the at least one tether 350 may or may not comprise additional tethers in addition to the single tether.
- single tether 350 typically comprises at least the following non-overlapping longitudinal portions disposed in sequence along the single tether:
- Tether-securing device 330 thus fixes first and second portions 359 A and 359 B 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).
- the at least one tether 350 comprises exactly one tether 350 .
- the at least one tether 350 comprises two tethers 350 , such as described hereinbelow with reference to FIG.
- 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).
- locking pieces 341 comprise exactly three locking pieces (as shown) or exactly four locking pieces (configuration not shown).
- locking pieces 341 are integral with tubular element 332 , and the locking pieces and tubular element are manufactured from a single piece of material.
- 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.
- each of locking pieces 341 is shaped so as to define two curved proximal edges 343 A and 343 B that meet at a proximal tip 345 .
- proximal edges 343 A and 343 B are shaped so as to define uneven edge surfaces, which, for example, may be jagged or serrated.
- the uneven edge surfaces of proximal edge 343 A interconnect with the uneven edge surfaces of proximal edge 343 B, 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.
- the uneven edge surfaces are shaped so as define teeth, such as shown in FIGS.
- locking pieces 341 are convex, as viewed from outside tether-securing device 330 , at least when locking pieces 341 are in the relaxed state.
- 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 ).
- the tips may be within 0.1 mm of each other, or touching each other.
- tubular element 332 is cylindrical. Alternatively, the tubular element has another shape.
- 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.
- a delivery tool 380 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.
- 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 .
- delivery tool 380 further comprises an outer shaft 384 , which surrounds inner shaft 382 .
- 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 .
- 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 .
- 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
- 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 .
- 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 .
- 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 .
- first and second tissue anchors 352 A and 352 B are implanted at respective different implantation sites 370 A and 370 B, 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.
- first and second tissue anchors 52 A and 52 B 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.
- first and second tissue anchors 352 A and 352 B 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 352 A may be implanted within 1 cm of the site on the annulus that circumferentially corresponds to an anteroposterior commissure 112 , and second tissue anchor 352 B may be implanted within 1 cm of the site on the annulus that circumferentially corresponds to a circumferential middle 93 of septal leaflet 82 .
- first and second tissue anchors 352 A and 352 B 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.
- a size of a tricuspid valve orifice is reduced by tensioning tether 350 , so as to reduce regurgitation.
- 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.
- 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).
- 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).
- 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.
- 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 .
- FIGS. 8A-C are schematic illustrations of techniques for securing excess portion 394 of tether 350 , in accordance with respective applications of the present invention.
- 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.
- 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.
- 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 .
- 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.
- first tissue anchor 352 A is implanted within 1 cm of the site on the annulus that circumferentially corresponds to septoanterior commissure 114
- second tissue anchor 352 B is implanted within 1 cm of the site on the annulus that circumferentially corresponds to septoposterior commissure 117 .
- first tissue anchor 352 A is implanted within 1 cm of the site on the annulus that circumferentially corresponds to septoposterior commissure 117 .
- first tissue anchor 352 A is implanted within 1 cm of the site on the annulus that circumferentially corresponds to anteroposterior commissure 112
- second tissue anchor 352 B is implanted within 1 cm of the site on the annulus that circumferentially corresponds to circumferential middle 93 of septal leaflet 82
- first tissue anchor 352 A is implanted within 1 cm of the site on the annulus that circumferentially corresponds to anteroposterior commissure 112
- second tissue anchor 352 B 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.
- 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.
- the stent is configured to self-expand.
- the stent may comprise a shape-memory alloy, such as Nitinol.
- the stent comprises a deformable metal, and is expanded by a tool, such as a balloon.
- 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.
- the stent is configured to not penetrate tissue of the wall of the vein.
- 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.
- 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.
- 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.
- excess portion 394 is cut and removed from the atrium, such as using techniques described hereinbelow with reference to FIG. 9 , mutatis mutandis.
- FIG. 9 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 7 A-B, and may incorporate any of the features thereof.
- the at least one tether 350 of implant system 420 comprises first and second tethers 350 A and 350 B, which (a) have first tether end portion 354 A and a second tether end portion 354 B, respectively, and (b) pass through the portion of securing-device lumen 336 .
- Second tissue anchor 352 B is connected (e.g., permanently fixed) to second tether end portion 354 B.
- excess portions 494 of tethers 350 A and 350 B are cut and removed from the atrium, using cutting tool 498 .
- excess portions 494 are held in a desired disposition, such as using techniques described hereinabove with reference to FIGS. 8A-C , mutatis mutandis.
- 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 352 A and second tissue anchor 352 B, of at least 30 mm, no more than 160 mm, and/or between 30 and 160 mm.
- 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.
- the at least one tether 350 comprises two tethers 350 A and 350 B, such as shown in FIG.
- 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.
- FIGS. 10A-D 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 343 A and 343 B of locking pieces 341 of tether-securing device 330 , as the case may be.
- 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 343 A and 343 B of locking pieces 341 of tether-securing device 330 , as the case may be.
- 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.
- protrusions 560 are defined by respective knots 570 in tether 550 , such as shown in FIG. 10A .
- protrusions 560 comprise respective cones 572 on tether 550 , such as shown in FIG. 10B .
- protrusions 560 comprise respective scales 574 on tether 550 , such as shown in FIG. 10C .
- protrusions 560 comprise respective beads 576 on tether 550 , such as shown in FIG. 10D .
- FIG. 11 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.
- implant system 320 and thus is one implementation of delivery tool 380
- the delivery tool may be used for delivering the other implant systems described herein, mutatis mutandis.
- 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.
- 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 352 A and 352 B 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 .
- 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 .
- 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 670 A and 670 B of first and second tissue anchors 352 A and 352 B, respectively, (b) extend within inner shaft 382 proximally from first and second heads 670 A and 670 B, respectively, and (c) transmit torque when rotated, for rotating tissue-coupling elements 648 A and 648 B of first and second tissue anchors 352 A and 352 B, respectively, into tissue.
- the torque cables additionally transmit axial force, to enable pushing of the tissue-coupling elements 648 A and 648 B into the tissue as they are rotated.
- a portion 630 of first torque cable 620 is initially removably positioned alongside second tissue anchor 352 B in inner shaft 382 .
- 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.
- 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.
- additional tissue anchors are initially removably positioned in inner shaft 382 proximal to second longitudinal location 616 .
- 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.
- 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.,
- 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 670 A.
- 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 670 A 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 670 A.
- 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.
- sharpened wire 642 is shaped so as to define a sharp distal tip 660 .
- first tissue anchor 352 A typically is helical, and sharpened wire 642 is initially removably positioned within a channel defined by the helix. As tissue anchor 352 A 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 352 A has been fully implanted, sharpened wire 642 is withdrawn entirely from the tissue, and removed from the patient's body.
- the sharp distal tip of sharpened wire 642 is inserted into the tissue slightly, even before insertion of tissue anchor 352 A, 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.
- sharpened wire 642 is withdrawn proximally from the channel of tissue anchor 352 A 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 670 A. After such proximal withdrawal, sharpened wire 642 typically remains within lumen 640 of first torque cable 620 .
- first torque cable 620 and first head 670 A are decoupling of first torque cable 620 and first head 670 A 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.
- Second torque cable 622 and second tissue anchor 352 B 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.
- 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.
- FIGS. 12A-C 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 352 A and 352 B, the method may also be used to deploy first and second tissue anchors 52 A and 52 B, first and second tissue anchors 252 A and 252 B, or first and second tissue anchors 352 A and 352 B, 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 .
- 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 at
- the procedure is typically performed with the aid of imaging, such as fluoroscopy, transesophageal, transthoratic echocardiography, IVUS, and/or echocardiography.
- 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.
- 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 352 A and 352 B 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 352 B in inner shaft 382 .
- first tissue anchor 352 A 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.
- tissue 700 of the subject e.g., cardiac muscle tissue, such as atrial tissue
- first torque cable 620 is decoupled from first tissue anchor 352 A, 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.
- second tissue anchor 352 B 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 352 B (not shown).
- First and second tissue anchors 352 A and 352 B remain implanted in tissue 700 , connected by tether 350 .
- 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 .
- 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.
- tether-securing device 330 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.
- 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.
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Abstract
Description
- The present application is a continuation of U.S. application Ser. No. 14/525,668, filed Oct. 28, 2014, which claims priority from U.S.
Provisional Application 61/897,491, filed Oct. 30, 2013, which is assigned to the assignee of the present application and is incorporated herein by reference. - Some applications of the present invention relate in general to valve repair. More specifically, some applications of the present invention relate to repair of an atrioventricular valve of a patient.
- Functional tricuspid regurgitation (FTR) is governed by several pathophysiologic abnormalities such as tricuspid valve annular dilatation, annular shape abnormality, pulmonary hypertension, left or right ventricle dysfunction, right ventricle geometry, and leaflet tethering. Treatment options for FTR are primarily surgical. The current prevalence of moderate-to-severe tricuspid regurgitation is estimated to be 1.6 million in the United States. Of these, only 8,000 patients undergo tricuspid valve surgeries annually, most of them in conjunction with left heart valve surgeries.
- Some embodiments of the present invention provide techniques for tightening tethers of percutaneous implants transluminally, in order to enable percutaneous treatment of functional tricuspid regurgitation (FTR). In some applications of the invention, techniques are provided for fixing two or more tethers to each other, or two portions of a single tether to one another, in order to apply and maintain tension between two or more tissue anchors implanted in tissue of a subject.
- In some applications of the present invention, a tether-securing device comprises a serrated tubular element that allows passage of one or more tethers or longitudinal portions of tethers band in one direction, but inhibits (e.g., prevents) the return of the tether(s) in the opposite direction.
- In other applications of the present invention, a tether-securing device is configured to assume an unlocked configuration, in which one or more tethers are generally slidable through the device, and a one-way-locked configuration, in which the tether(s) are slidable only in one direction through the device. For some applications, the tether-securing device is configured to be biased to assume the one-way-locked configuration thereof, and is retained in the unlocked configuration by a constraint. For such applications, the devices automatically transition to the one-way-locked configuration when the constraint is removed.
- In some applications of the present invention, excess portions of the tether(s) are cut off proximal to the tether-securing device after it is locked in place. For such applications, a delivery system for implanting the implant also comprises a tool for shearing off and retrieving the excess material, such as thoracoscopic scissors, as known in the art.
- In other applications of the present invention, excess portions of the tether(s) are held in place by a fixation device such as a stent, which is placed in the vasculature leading to the atrium, such as the superior vena cava (SVC), the inferior vena cava (IVC), or the coronary sinus (CS). For such applications, the delivery system is configured to connect the excess material to the fixation device.
- In some applications of the present invention, techniques are provided for using tether-securing devices to repair a heart valve, by fixedly coupling together textile bands that are coupled to different parts of an annulus of a heart valve.
- There is therefore provided, in accordance with an application of the present invention, apparatus including:
- at least one tether, having first and second tether end portions;
- first and second tissue anchors, fixed to the first and the second tether end portions, respectively; and
- a tether-securing device, which includes:
-
- a tubular element, which is shaped so as define a lumen through which the at least one tether passes, and has proximal and distal tube ends; and
- three or more locking pieces, which extend proximally from the proximal end of the tubular element,
- wherein the tether-securing device is configured:
-
- to assume an unlocked configuration when the locking pieces are in a constrained state, in which the locking pieces extend proximally and allow distal and proximal sliding of the at least one tether through the lumen, and
- to assume a one-way-locked configuration when the locking pieces are in a relaxed state, in which the locking pieces extend proximally and radially inward toward one another and inhibit the distal sliding more than when in the constrained state.
- For some applications, the locking pieces are configured to allow the proximal sliding when in the relaxed state.
- For some applications, the locking pieces are convex, as viewed from outside the tether-securing device, at least when the locking pieces are in the relaxed state.
- For some applications, the tubular element is cylindrical.
- For some applications, the locking pieces are integral with the tubular element.
- For some applications, the three or more locking pieces include exactly three locking pieces or exactly four locking pieces.
- For some applications, the lumen is a securing-device lumen, and the apparatus further includes a delivery tool, which includes a catheter shaft, which (a) is configured to apply a constraining force to the locking pieces when the shaft is disposed in the securing-device lumen, which constraining force retains the tether-securing device in the unlocked configuration, and (b) is shaped so as to define a shaft lumen, through which the at least one tether removably slidably passes.
- For some applications, a total axial length of the tether-securing device, when the locking pieces are in the relaxed state, is between 3 and 50 mm.
- For any of the applications described above, each of the locking pieces may be shaped so as to define two curved edges that meet at a proximal tip. For some applications, the proximal edges are shaped so as to define uneven edge surfaces. For some applications, the uneven edge surfaces are shaped so as define teeth. For some applications, the uneven edge surfaces are rough.
- For any of the applications described above, the at least one tether defines a plurality of securement protrusions spaced at intervals along the at least one tether. For some applications, the protrusions are defined by respective knots in the at least one tether. For some applications, the protrusions include respective elements selected from the group consisting of: cones, scales, and beads. For some applications, an average interval of the securement protrusions is between 1 and 5 mm.
- For any of the applications described above, the at least one tether may include first and second tethers, which have the first and the second tether end portions, respectively.
- For any of the applications described above, a single tether of the at least one tether may have the first and the second tether end portions, and the single tether may include at least the following non-overlapping longitudinal portions disposed in sequence along the single tether:
- the first tether end portion,
- a first portion that passes through the lumen,
- a looped middle portion that extends out of and away from the lumen, and then loops back to the lumen,
- a second portion that passes through the lumen, and
- the second tether end portion.
- For some applications, the apparatus further includes a fixation tether, which is connected to the looped middle portion of the single tether. For some applications, the apparatus further includes a venous tissue anchor, which is configured to be implanted in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus, and which is connected to the fixation tether. For some applications, the venous tissue anchor includes a stent.
- For any of the applications described above, the apparatus further includes:
- a venous tissue anchor, which is configured to be implanted in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus; and
- a fixation tether, which is connected to the venous tissue anchor and the at least one tether.
- For some applications, the venous tissue anchor includes a stent.
- There is further provided, in accordance with an application of the present invention, apparatus including:
- a tether-securing device, which includes a tubular element, which is shaped so as define a lateral wall that surrounds a lumen, wherein the lateral wall is shaped so as to define a one-way locking opening;
- at least one tether, which (a) has at least a first tether end portion, and (b) passes through the lumen and the one-way locking opening; and
- first and second tissue anchors, wherein the first tissue anchor is connected to the first tether end portion,
- wherein the one-way locking opening is configured to (a) allow sliding of the at least one tether in a first direction through the one-way locking opening, and (b) inhibit sliding of the at least one tether in a second direction opposite the first direction.
- For some applications, the one-way locking opening is shaped as a slit.
- For some applications, the first direction is from inside the tubular element to outside the tubular element.
- For some applications, the tubular element is cylindrical.
- For some applications, an axial length of the tubular element is between 5 and 20 mm.
- For any of the applications described above, the one-way locking opening may have uneven edges. For some applications, the uneven edges are jagged or serrated.
- For any of the applications described above, the at least one tether may define a plurality of securement protrusions spaced at intervals along the at least one tether. For some applications, the protrusions are defined by respective knots in the at least one tether. For some applications, the protrusions include respective elements selected from the group consisting of: cones, scales, and beads. For some applications, an average interval of the securement protrusions is between 1 and 5 mm.
- For any of the applications described above, a single tether of the at least one tether may have the first tether end portion and a second tether end portion, which second tether end portion is connected to the second tissue anchor, and the single tether may include at least the following non-overlapping longitudinal portions disposed in sequence along the single tether:
- the first tether end portion,
- a first portion that passes through the securing-device lumen and the one-way locking opening,
- a looped middle portion that extends out of and away from the one-way locking opening, and then loops back to the one-way locking opening,
- a second portion that passes through the securing-device lumen and the one-way locking opening, and
- the second tether end portion.
- For some applications, the lateral wall is shaped so as to define first and second non-constraining openings, which are sized and shaped to allow free sliding therethrough of two longitudinal portions, respectively, of the single tether. For some applications, the non-constraining openings are shaped as respective slits. For some applications, the apparatus further includes a fixation tether, which is connected to the looped middle portion of the single tether. For some applications, the apparatus further includes a venous tissue anchor, which is configured to be implanted in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus, and which is connected to the fixation tether. For some applications, the venous tissue anchor includes a stent.
- For any of the applications described above, the second tissue anchor may include a head and a tissue-coupling element, and the tether-securing device is fixed to the head, such that the tether-securing device surrounds at least a portion of the head. For some applications, the tether-securing device is configured to rotate with respect to the head. For some applications, the lateral wall is shaped so as to define a non-constraining opening, which is sized and shaped to allow free sliding therethrough of the at least one tether. For some applications, the non-constraining opening is shaped as a slit.
- For any of the applications described above:
- the at least one tether may include first and second tethers, which (a) have the first tether end portion and a second tether end portion, respectively, and (b) pass through (i) the lumen and (ii) the one-way locking opening,
- the second tissue anchor may be connected to the second tether end portion, and
- the one-way locking opening may be configured to (a) allow the sliding of the first and the second tethers in the first direction through the one-way locking opening, and (b) inhibit the sliding of the first and the second tethers in the second direction.
- For some applications, the lateral wall is shaped so as to define first and second non-constraining openings, which are sized and shaped to allow free sliding therethrough of the first and the second tethers, respectively. For some applications, the non-constraining openings are shaped as respective slits.
- For any of the applications described above, the apparatus may further include:
- a venous tissue anchor, which is configured to be implanted in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus; and
- a fixation tether, which is connected to the venous tissue anchor and the at least one tether.
- For some applications, the venous tissue anchor includes a stent.
- There is still further provided, in accordance with an application of the present invention, apparatus including:
- a tether, having first and second tether end portions;
- first and second tissue anchors, fixed to the first and the second tether end portions, respectively; and
- a tether-securing device,
- the tether includes at least the following non-overlapping longitudinal portions disposed in sequence along the tether:
-
- the first tether end portion,
- a first portion that passes through the lumen,
- a looped middle portion that (a) extends out of and away from the tether-securing device and (b) then loops back to the tether-securing device,
- a second portion that passes through the tether-securing device, and
- the second tether end portion.
- For some applications, the looped middle portion extends out of and away from the tether-securing device such that a longitudinal center of the looped middle portion is not in direct physical contact with any portion of the tether-securing device.
- For some applications, the tether-securing device is configured to assume:
- an unlocked configuration, in which the tether-securing device allows distal and proximal sliding of the first and the second portions of the tether therethrough, and
- a one-way-locked configuration, in which the tether-securing device inhibits the distal sliding more than when in the unlocked configuration.
- For some applications, the tether-securing device is configured to assume:
- an unlocked configuration, in which the tether-securing device allows distal and proximal sliding of the first and the second portions of the tether therethrough, and
- a locked configuration, in which the tether-securing device inhibits the distal and proximal sliding.
- For some applications, the tether-securing device is configured to (a) allow sliding of the first and the second portions of the tether in a first direction through the tether-securing device, and (b) inhibit sliding of the first and the second portions of the tether in a second direction opposite the first direction.
- For any of the applications described above, the apparatus may further include a fixation tether, which is connected to the looped middle portion of the tether. For some applications, the apparatus further includes a venous tissue anchor, which is configured to be implanted in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus, and which is connected to the fixation tether. For some applications, the venous tissue anchor includes a stent.
- There is additionally provided, in accordance with an application of the present invention, apparatus including:
- an implant, which includes:
-
- at least first and second tissue anchors, which include (a) first and second helical tissue coupling elements, respectively, and (b) first and second heads, respectively, which include first and second tether interfaces; and
- a tether, which is connected to the first tether interface, and coupled to the second tether interface; and
- a multiple-anchor delivery tool, which includes:
-
- 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.
- For some applications:
- the implant further includes a third tissue anchor, which includes (a) a third helical tissue coupling elements and (b) a third head, which includes a third tether interface,
- the tether, which is coupled to the third tether interface,
- 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
- 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, and a portion of the second torque cable is removably positioned alongside the third tissue anchor in the catheter shaft.
- For some applications, the first tether interface is rotatable with respect to the first tissue-coupling element.
- For any of the applications described above, the first torque cable may be shaped so as to define a lumen therethrough, and the multiple-anchor delivery tool may further include a shaft, which removably passes through the lumen. For some applications:
- the head is shaped so as to define a proximal coupling element,
- 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,
- 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,
- the proximal and the distal coupling elements are shaped so as to define corresponding interlocking surfaces, and
- the shaft, when disposed through the first and the second channels, prevents decoupling of the distal coupling element from the proximal coupling element.
- For some applications, the shaft is shaped so as to define a sharp distal tip.
- There is yet additionally provided, in accordance with an application of the present invention, a method including:
- delivering, to a vicinity of an anatomical site of a subject, (a) at least one tether, having first and second tether end portions, (b) first and second tissue anchors, fixed to the first and the second tether end portions, respectively, and (c) a tether-securing device, which includes (i) a tubular element, which is shaped so as define a lumen through which the at least one tether passes, and has proximal and distal tube ends, and (ii) three or more locking pieces, which extend proximally from the proximal end of the tubular element;
- implanting the first and the second tissue anchors in tissue of the subject;
- tensioning the at least one tether by proximally sliding the at least one tether through the lumen while the tether-securing device is in an unlocked configuration in which the locking pieces are in a constrained state, in which state the locking pieces extend proximally and allow distal and proximal sliding of the at least one tether through the lumen; and
- transitioning the tether-securing device to a one-way-locked configuration in which the locking pieces are in a relaxed state, in which state the locking pieces extend proximally and radially inward toward one another and inhibit the distal sliding more than when in the constrained state.
- For some applications, the locking pieces are configured to allow proximal sliding when in the relaxed state, and tensioning includes further tensioning the at least one tether by further proximally sliding the at least one tether through the lumen after transitioning the tether-securing device to the one-way-locked configuration.
- For some applications:
- a single tether of the at least one tether has the first and the second tether end portions,
- the single tether includes at least the following non-overlapping longitudinal portions disposed in sequence along the single tether:
-
- the first tether end portion,
- a first portion that passes through the lumen,
- a looped middle portion that extends out of and away from the lumen, and then loops back to the lumen,
- a second portion that passes through the lumen, and
- the second tether end portion, and
- tensioning the tether includes proximally sliding the first and the second portions of the tether through the lumen by pulling on the looped middle portion.
- For some applications, the method further includes connecting a fixation tether to the looped middle portion of the single tether.
- For some applications, the method further includes implanting a venous tissue anchor, which is connected to the fixation tether, in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus. For some applications, implanting the venous tissue anchor includes implanting a stent.
- For some applications, the at least one tether includes first and second tethers, which have the first and the second tether end portions, respectively, and tensioning the at least one tether includes tensioning the first and the second tethers by proximally sliding the first and the second tethers through the lumen.
- For some applications, each of the locking pieces is shaped so as to define two curved edges that meet at a proximal tip. For some applications, the proximal edges are shaped so as to define uneven edge surfaces. For some applications, the uneven edge surfaces are shaped so as define teeth. For some applications, the uneven edge surfaces are rough.
- For some applications, the locking pieces are convex, as viewed from outside the tether-securing device, at least when the locking pieces are in the relaxed state.
- For some applications, the at least one tether defines a plurality of securement protrusions spaced at intervals along the at least one tether. For some applications, the protrusions are defined by respective knots in the at least one tether. For some applications, the protrusions include respective elements selected from the group consisting of: cones, scales, and beads. For some applications, an average interval of the securement protrusions is between 1 and 5 mm.
- For some applications, a total axial length of the tether-securing device, when the locking pieces are in the relaxed state, is between 10 and 50 mm.
- For some applications, the tubular element is cylindrical.
- For some applications, the locking pieces are integral with the tubular element.
- For some applications, the three or more locking pieces include exactly three locking pieces or exactly four locking pieces.
- For some applications:
- the lumen is a securing-device lumen,
- delivering the at least one tether and the tether-securing device includes delivering the at least one tether and the tether-securing device using a delivery tool, which includes a catheter shaft, which (a) applies a constraining force to the locking pieces when the shaft is disposed in the securing-device lumen, which constraining force retains the tether-securing device in the unlocked configuration, and (b) is shaped so as to define a shaft lumen, through which the at least one tether removably slidably passes, and
- transitioning the tether-securing device to a one-way-locked configuration includes removing the catheter shaft from the securing-device lumen.
- For some applications, the method further includes:
- implanting a venous tissue anchor in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus; and
- connecting, to the at least one tether, a fixation tether which is connected to the venous tissue anchor.
- For some applications, implanting the venous tissue anchor includes implanting a stent.
- There is also provided, in accordance with an application of the present invention, a method including:
- delivering, to a vicinity of an anatomical site of a subject:
-
- (a) a tether-securing device, which includes a tubular element, which is shaped so as define a lateral wall that surrounds a lumen, wherein the lateral wall is shaped so as to define a one-way locking opening, which is configured to (i) allow sliding of the at least one tether in a first direction through the one-way locking opening, and (ii) inhibit sliding of the at least one tether in a second direction opposite the first direction,
- (b) at least one tether, which (i) has at least a first tether end portion, and (ii) passes through the lumen and the one-way locking opening, and
- (c) first and second tissue anchors, wherein the first tissue anchor is connected to the first tether end portion;
- implanting the first and the second tissue anchors in tissue of the subject; and
- tensioning the at least one tether by sliding the at least one tether in the first direction through the one-way locking opening.
- For some applications, a single tether of the at least one tether has the first tether end portion and a second tether end portion, which second tether end portion is connected to the second tissue anchor, and the single tether includes at least the following non-overlapping longitudinal portions disposed in sequence along the single tether:
- the first tether end portion,
- a first portion that passes through the securing-device lumen and the one-way locking opening,
- a looped middle portion that extends out of and away from the one-way locking opening, and then loops back to the one-way locking opening,
- a second portion that passes through the securing-device lumen and the one-way locking opening, and
- the second tether end portion, and
- tensioning the tether includes proximally sliding the first and the second portions of the tether through the one-way locking opening in the first direction by pulling, in the first direction, on the looped middle portion.
- For some applications:
- the lateral wall is shaped so as to define first and second non-constraining openings, which are sized and shaped to allow free sliding therethrough of two longitudinal portions, respectively, of the single tether, and
- sliding the tether through the one-way locking opening further includes sliding the two non-overlapping longitudinal portions of the tether through the first and the second non-constraining openings, respectively.
- For some applications, the non-constraining openings are shaped as respective slits. For some applications, the method further includes connecting a fixation tether to the looped middle portion of the single tether. For some applications, the method further includes implanting a venous tissue anchor, which is connected to the fixation tether, in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus. For some applications, implanting the venous tissue anchor includes implanting a stent.
- For some applications, the second tissue anchor includes a head and a tissue-coupling element, and the tether-securing device is fixed to the head, such that the tether-securing device surrounds at least a portion of the head. For some applications, the tether-securing device is configured to rotate with respect to the head.
- For some applications, the lateral wall is shaped so as to define a non-constraining opening, which is sized and shaped to allow free sliding therethrough of the tether, and sliding the tether through the one-way locking opening further includes sliding the tether through the non-constraining opening.
- For some applications, the non-constraining opening is shaped as a slit.
- For some applications:
- the at least one tether includes first and second tethers, which (a) have the first tether end portion and a second tether end portion, respectively, and (b) pass through (i) the lumen and (ii) the one-way locking opening,
- the second tissue anchor is connected to the second tether end portion,
- the one-way locking opening is configured to (a) allow the sliding of the first and the second tethers in the first direction through the one-way locking opening, and (b) inhibit the sliding of the first and the second tethers in the second direction, and
- tensioning the at least one tether includes tensioning the first and the second tethers by sliding the first and the second tethers in the first direction through the one-way locking opening.
- For some applications:
- the lateral wall is shaped so as to define first and second non-constraining openings, which are sized and shaped to allow free sliding therethrough of the first and the second tethers, respectively,
- the first and the second tethers slidably pass through the first and the second non-constraining openings, respectively, and
- sliding the first and the second tethers through the one-way locking opening further includes sliding the first and the second tethers through the first and the second non-constraining openings, respectively.
- For some applications, the non-constraining openings are shaped as respective slits.
- For some applications, the one-way locking opening is shaped as a slit.
- For some applications, the first direction is from inside the tubular element to outside the tubular element.
- For some applications, the one-way locking opening has uneven edges. For some applications, the uneven edges are jagged or serrated.
- For some applications, an axial length of the tubular element is between 5 and 20 mm.
- For some applications, the tubular element is cylindrical.
- For some applications, the at least one tether defines a plurality of securement protrusions spaced at intervals along the at least one tether. For some applications, the protrusions are defined by respective knots in the at least one tether. For some applications, the protrusions include respective elements selected from the group consisting of: cones, scales, and beads.
- For some applications, an average interval of the securement protrusions is between 1 and 5 mm.
- For some applications, the method further includes:
- implanting a venous tissue anchor in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus; and
- connecting, to the at least one tether, a fixation tether which is connected to the venous tissue anchor.
- For some applications, implanting the venous tissue anchor includes implanting a stent.
- There is further provided, in accordance with an application of the present invention, a method including:
- delivering, to a vicinity of an anatomical site of a subject, (a) a tether, having first and second tether end portions, (b) first and second tissue anchors, fixed to the first and the second tether end portions, respectively, and (c) a tether-securing device, wherein the tether includes at least the following non-overlapping longitudinal portions disposed in sequence along the tether: (i) the first tether end portion, (ii) a first portion that passes through the lumen, (iii) a looped middle portion that (1) extends out of and away from the tether-securing device and (2) then loops back to the tether-securing device, (iv) a second portion that passes through the tether-securing device, and (v) the second tether end portion;
- implanting the first and the second tissue anchors in tissue of the subject; and
- tensioning the tether by proximally sliding the first and the second portions of the tether through the tether-securing device by pulling on the looped middle portion.
- For some applications, delivering the tether includes delivering the tether such that the looped middle portion extends out of and away from the tether-securing device, such that a longitudinal center of the looped middle portion is not in direct physical contact with any portion of the tether-securing device.
- For some applications, the method further includes connecting a fixation tether to the looped middle portion of the tether. For some applications, the method further includes implanting a venous tissue anchor, which is connected to the fixation tether, in a vein selected from the group of veins consisting of: an inferior vena cava, a superior vena cava, and a coronary sinus. For some applications, implanting the venous tissue anchor includes implanting a stent.
- For some applications, the tether-securing device is configured to assume:
- an unlocked configuration, in which the tether-securing device allows distal and proximal sliding of the first and the second portions of the tether therethrough, and
- a one-way-locked configuration, in which the tether-securing device inhibits the distal sliding more than when in the unlocked configuration.
- For some applications, the tether-securing device is configured to assume:
- an unlocked configuration, in which the tether-securing device allows distal and proximal sliding of the first and the second portions of the tether therethrough, and
- a locked configuration, in which the tether-securing device inhibits the distal and proximal sliding.
- For some applications, the tether-securing device is configured to (a) allow sliding of the first and the second portions of the tether in a first direction through the tether-securing device, and (b) inhibit sliding of the first and the second portions of the tether in a second direction opposite the first direction.
- There is still further provided, in accordance with an application of the present invention, a method including:
- 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 helical tissue coupling elements, respectively, and (ii) first and second heads, respectively, which include first and second tether interfaces, and (b) a tether, which is connected to the first tether interface, and is coupled to the second tether interface, is 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 into tissue of the subject by rotating the first torque cable;
- 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 into tissue of the subject by rotating the second torque cable; and
- decoupling the second torque cable from the second tissue anchor.
- For some applications:
- the first torque cable is shaped so as to define a lumen therethrough,
- the multiple-anchor delivery tool further includes a sharpened wire, which removably passes through the lumen, and which is initially positioned such that a distal end of the sharpened wire extends distally out of a distal end of the lumen, and
- the method further includes withdrawing the sharpened wire proximally.
- For some applications:
- the head is shaped so as to define a proximal coupling element,
- 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,
- 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,
- the proximal and the distal coupling elements are shaped so as to define corresponding interlocking surfaces,
- the sharpened wire, when disposed through the first and the second channels, prevents decoupling of the distal coupling element from the proximal coupling element, and
- withdrawing the sharpened wire proximally includes decoupling the distal coupling element from the proximal coupling element by withdrawing the sharpened wire proximally.
- For some applications, the sharpened wire is shaped so as to define a sharp distal tip. For some applications, implanting the first tissue anchor includes inserting the sharp distal tip of the sharpened wire into the tissue.
- For some applications:
- advancing includes 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, and the third tissue anchor includes (i) a third helical tissue coupling elements and (ii) a third head, which includes a third tether interfaces, (b) the tether is coupled to the third tether interface,
- 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, and a portion of the second torque cable is removably positioned alongside the third tissue anchor in the catheter shaft, and
- the method further includes:
-
- after implanting the second tissue anchor, distally advancing the third tissue anchor in the catheter shaft;
- implanting the third tissue anchor into tissue of the subject by rotating the third torque cable; and
- decoupling the third torque cable from the third tissue anchor.
- For some applications, the first tether interface is rotatable with respect to the first tissue-coupling element.
- The present invention will be more fully understood from the following detailed description of applications thereof, taken together with the drawings, in which:
-
FIG. 1 is a schematic illustration of a valve-tensioning implant system, in accordance with an application of the present invention; -
FIG. 2 is a schematic illustration of a tether-securing device of the implant system ofFIG. 1 , in accordance with an application of the present invention; -
FIG. 3 is a schematic illustration of another valve-tensioning implant system, in accordance with an application of the present invention; -
FIGS. 4A-C are schematic illustrations of yet another valve-tensioning implant system, in accordance with an application of the present invention; -
FIG. 5 is a schematic illustration of a tether-securing device of the implant system ofFIGS. 4A-C fixed to second tissue anchor of the implant system, in accordance with an application of the present invention; -
FIGS. 6A-C are schematic illustration of still another valve-tensioning implant system, in accordance with an application of the present invention; -
FIGS. 7A and 7B are schematic illustration of a tether-securing device of the implant system ofFIGS. 6A-C , in unlocked and one-way-locked configurations, respectively, in accordance with an application of the present invention; -
FIGS. 8A-C are schematic illustrations of techniques for securing an excess portion of a tether of the implant system ofFIGS. 6A-C and 7A-B, in accordance with respective applications of the present invention; -
FIG. 9 is a schematic illustration of another valve-tensioning implant system, in accordance with an application of the present invention; -
FIGS. 10A-D are schematic illustrations of friction-enhancing features of a tether, in accordance with respective applications of the present invention; -
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 -
FIGS. 12A-C are schematic illustrations of a deployment method using the multiple-anchor delivery tool ofFIG. 11 , in accordance with an application of the present invention. -
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., atricuspid 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-securingdevice 30, at least onetether 50, and first and second tissue anchors 52A and 52B. - For some applications, first and second tissue anchors 52A and 52B are connected (e.g., permanently fixed) to first and second
tether end portions tether 50, respectively (typically first and second tissue anchors 52A and 52B are connected to first and second tether ends of the at least onetether 50, respectively). The at least onetether 50 comprises an elongate flexible element, such as a cord, suture, or band. Typically, the at least onetether 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 secondtether end portions loops - Reference is still made to
FIG. 1 , and is additionally made toFIG. 2 , which is a schematic illustration of tether-securingdevice 30, in accordance with an application of the present invention. Tether-securingdevice 30 comprises atubular element 32, which is shaped so as define alateral 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 alongitudinal axis 39 oftubular element 32. Typically,lateral wall 34 is shaped so as to define at least twopawls way locking opening 38. Typically, one-way locking opening has uneven edges, which, for example, may be jagged or serrated. - 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 onetether 50 in a first direction through one-way locking opening 38, and (b) inhibit (e.g., prevent or limit) sliding of the at least onetether 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. - For some applications, such as shown in
FIG. 1 , asingle tether 50 of the at least onetether 50 has first and secondtether end portions 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: -
- first
tether end portion 54A, - a
first portion 59A that passes through securing-device lumen 36 and one-way locking opening 38, - 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 alongitudinal center 61 of loopedmiddle portion 88 is not in direct physical contact with any portion of tether-securing device 30), - a
second portion 59B that passes through securing-device lumen 36 and one-way locking opening 38, and - 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 firsttether end portion 54A andfirst portion 59A, and a longitudinal portion betweensecond portion 59B and secondtether end portion 54B.
- first
- Tether-securing
device 30 thus fixes first andsecond portions device 30 along the single tether is set during an implantation procedure, such that respective distances between tether-securingdevice 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 onetether 50 comprises exactly onetether 50. - For some applications,
lateral wall 34 is shaped so as to define at least onenon-constraining opening 60, such as first and secondnon-constraining openings way locking opening 38. First and secondnon-constraining openings longitudinal portions single tether 50, respectively. Typically, first and second non-overlappinglongitudinal portions non-constraining openings 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 tolongitudinal axis 39 oftubular element 32. - 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 oftubular element 32 is at least 5 mm, no more than 20 mm, and/or between 5 and 20 mm. - For some applications, first and
second tissue anchor second tissue anchor second tissue anchor 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. - 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 aninferior vena cava 74, and into aright atrium 81, (b) via the basilic vein, through the subclavian vein through asuperior vena cava 76, and intoright atrium 81, or (c) via the external jugular vein, through the subclavian vein throughsuperior vena cava 76, and intoright atrium 81. (Right atrium 81 includes aseptal leaflet 82, aposterior leaflet 84, and ananterior 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 toFIGS. 11-12C . - First and
second tissue anchor atrial sites 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 inFIG. 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), andsecond tissue anchor 52B may be implanted within 1 cm of a circumferential middle of theannulus 87 alonganterior 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 ofright atrium 81 above annulus 83, or a combination of circumferentially around the annulus and up the wall of the atrium. - 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 asouter shaft 384, described hereinbelow with reference toFIGS. 6A-C ) against a proximal side of tether-securingdevice 30 while proximally pulling on loopedmiddle portion 88 oftether 50, such that portions oftether 50 are pulled through one-way locking opening 38. For example, a flexible longitudinal guide member 390 (as shown below inFIG. 6C ) may be removably coupled tomiddle 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 flexiblelongitudinal guide member 390 of the present application). Once the tension has been applied, one-way locking opening 38 maintains the tension. - After
tether 50 has been tensioned, anexcess portion 94 oftether 50 near loopedmiddle portion 88 remains free inright 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 ofright atrium 81, such as in inferior vena cava 74 (as shown inFIG. 1 ), superior vena cava 76 (such as shown inFIG. 8B , mutatis mutandis), or a coronary sinus 115 (such as shown inFIG. 8C , mutatis mutandis). Techniques described hereinbelow with reference toFIGS. 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 toFIGS. 8A-C , is deployed such that only a moderate amount of tension is applied tofixation 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 loopedmiddle 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 toFIG. 9 , mutatis mutandis. - 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 asimplant system 20, described hereinabove with reference toFIGS. 1 and 2 , and may incorporate any of the features thereof. In this configuration, the at least onetether 50 ofimplant system 120 comprises first andsecond tethers tether end portion 54A and a secondtether 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 secondtether end portion 54B. One-way locking opening 38 is configured to (a) allow the sliding of first andsecond tethers way locking opening 38, and (b) inhibit (e.g., prevent or limit) the sliding of first andsecond tethers device 30 thus fixes thetethers 50 to each other. - For some applications,
lateral wall 34 is shaped so as to define at least twonon-constraining openings 60, such as first and secondnon-constraining openings way locking opening 38. First and secondnon-constraining openings second tethers second tethers non-constraining openings 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 tolongitudinal axis 39 oftubular element 32. - For some applications,
free end portions 53 of first andsecond tethers tether end portions fixation tether 404, described hereinbelow with reference toFIGS. 8A-C , such as byrespective 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. - Reference is made to
FIGS. 1 and 3 . For applications in which the at least onetether 50 comprisessingle tether 50, such as exactly one tether 50 (as shown inFIG. 1 ), the single tether typically has a length, measured betweenfirst tissue anchor 52A andsecond tissue anchor 52B, of at least 30 mm, no more than 160 mm, and/or between 30 and 160 mm. For some applications, loopedmiddle 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 onetether 50 comprises twotethers FIG. 3 , each oftethers 50 typically has a length of at least 20 mm, no more than 80 mm, and/or between 20 and 80 mm. Because eachtether 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. - 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-securingdevice 230, at least onetether 50, and first and second tissue anchors 252A and 252B. Except as described below, tether-securingdevice 230 is similar to tether-securingdevice 30, described hereinabove with reference toFIGS. 1 and 2 , and may incorporate any of the features thereof. - Reference is still made to
FIGS. 4A-C , and is additionally made toFIG. 5 , which is a schematic illustration of tether-securingdevice 230 fixed tosecond tissue anchor 252B, in accordance with an application of the present invention.Second tissue anchor 252B comprises ahead 253 and a tissue-coupling element 255, such as a helical tissue-coupling element. Tether-securingdevice 230 is fixed to head 253, typically such that the tether-securing device surrounds at least a portion of the head. Typically, tether-securingdevice 230 is configured to rotate with respect tohead 253, such that the tether-securing device is mounted rotatably on the head. - Typically,
first tissue anchor 252A is connected (e.g., permanently fixed) to firsttether end portion 54A oftether 50. For some applications, firsttether end portion 54A is configured so as to define anchor-fixingloop 68A, which passes through a corresponding interface onfirst tissue anchor 52A so as to connect (e.g., permanently fix) the tether end portion to the tissue anchor. - In this configuration, typically a
single tether 50 of the at least onetether 50 has first and secondtether end portions tether 50 may or may not comprise additional tethers in addition to the single tether.) Alongitudinal portion 257 ofsingle tether 50 passes through (a) securing-device lumen 36 and (b) one-way locking opening 38 of tether-securingdevice 230. For some applications, the at least onetether 50 comprises exactly onetether 50. - For some applications,
lateral wall 34 of tether-securingdevice 230 is shaped so as to define anon-constraining opening 60, such as exactly onenon-constraining opening 60, as shown inFIG. 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 oflongitudinal portion 257.Longitudinal portion 257 oftether 50 slidably passes throughnon-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 tolongitudinal axis 39 oftubular element 32 of tether-securingdevice 230. - 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, throughinferior vena cava 74, and intoright atrium 81, (b) via the basilic vein, through the subclavian vein throughsuperior vena cava 76, and intoright atrium 81, or (c) via the external jugular vein, through the subclavian vein throughsuperior vena cava 76, and intoright 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 toFIGS. 11-12C . - First and
second tissue anchor atrial sites 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 inFIGS. 4A and 4C ,first tissue anchor 252A may be implanted within 1 cm of the point on the annulus that circumferentially corresponds toseptoposterior commissure 117, andsecond 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 inFIG. 4B ,first tissue anchor 252A may be implanted within 1 cm of the point on the annulus that circumferentially corresponds toanteroposterior commissure 112, andsecond tissue anchor 252B may be implanted within 1 cm of the point on the annulus that circumferentially corresponds to a circumferential middle 93 ofseptal leaflet 82. The direction of the 1 cm from the described anatomical sites may be either circumferentially around the annulus, up the wall ofright atrium 81 above annulus 83, or a combination of circumferentially around the annulus and up the wall of the atrium. - 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 secondtether end portion 54B oftether 50, such that a portion oftether 50 is pulled through one-way locking opening 38. For example, a flexible longitudinal guide member 390 (as shown below inFIG. 6C ) may be removably coupled to secondtether end portion 54B by aloop 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 flexiblelongitudinal guide member 390 of the present application). Once the tension has been applied, one-way locking opening 38 maintains the tension. - After
tether 50 has been tensioned, anexcess portion 294 oftether 50, including secondtether end portion 54B, remains free inright 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 inFIG. 4A ), superior vena cava 76 (such as shown inFIG. 8B , mutatis mutandis), or a coronary sinus 115 (such as shown inFIG. 4B ). Techniques described hereinbelow with reference toFIGS. 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 toFIGS. 8A-C , is deployed such that only a moderate amount of tension is applied tofixation tether 404, which tension is insufficient to alter the geometry of the atrium.Fixation tether 404 is connected, typically during the implantation procedure, to tetherend portion 54B, such as byloop 180, e.g., a ring. Alternatively,excess portion 294 oftether 50 is cut and removed from the atrium, using acutting tool 498, such as thoracoscopic scissors, as known in the art. - 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-securingdevice 330, at least onetether 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 secondtether end portions tether 350, respectively (typically first and second tissue anchors 352A and 352B are connected to first and second ends of the at least onetether 350, respectively). For some applications, first and secondtether end portions loops - Reference is now made to
FIGS. 7A and 7B , which are schematic illustration of tether-securingdevice 330, in unlocked and one-way-locked configurations, respectively, in accordance with an application of the present invention. Tether-securingdevice 330 is configured to assume the unlocked and the one-way-locked configurations. Tether-securingdevice 330 comprises atubular element 332, which is shaped so as define a securing-device lumen 336 through which the at least onetether 350 passes, and has proximal and distal tube ends 335 and 337. Tether-securingdevice 330 typically comprises an implantable alloy, typically superelastic, such as Nitinol. - Tether-securing
device 330 further comprises three or more locking pieces 341 (which may be considered pawls), which extend proximally fromproximal end 335 oftubular element 332. Tether-securingdevice 330 is configured: -
- to assume the unlocked configuration when locking
pieces 341 are in a constrained state, as shown inFIG. 7A , in which lockingpieces 341 extend proximally and allow distal and proximal sliding of the at least onetether 350 through securing-device lumen 336, and - to assume the one-way-locked configuration when locking
pieces 341 are in a relaxed state, as shown inFIG. 7B , in which lockingpieces 341 extend proximally and radially inward toward one another (and, typically, toward a central longitudinal axis of tubular element 332). When tether-securingdevice 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-securingdevice 330 may be bullet-shaped, such as shown in FIG. 7B, with the locking pieces collectively defining a round nose thereof.
- to assume the unlocked configuration when locking
- For some applications, such as shown in
FIG. 6A-C , asingle tether 350 of the at least onetether 350 has first and secondtether end portions 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: -
- first
tether end portion 354A, - a
first portion 359A that passes through securing-device lumen 336, - a looped
middle portion 388 that extends out of and away from the lumen, and then loops back to the lumen (such that alongitudinal center 361 of loopedmiddle portion 388 is not in direct physical contact with any portion of tether-securing device 330), - a
second portion 359B that passes through securing-device lumen 336, and - 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 firsttether end portion 354A andfirst portion 359A, and a longitudinal portion betweensecond portion 359B and secondtether end portion 354B.
- first
- Tether-securing
device 330 thus fixes first andsecond portions 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 onetether 350 comprises exactly onetether 350. For applications in which the at least onetether 350 comprises twotethers 350, such as described hereinbelow with reference toFIG. 9 , tether-securingdevice 330 thus fixes thetethers 350 to each other, either (a) directly, if the two tethers touch one another between lockingpieces 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). - For some applications, locking
pieces 341 comprise exactly three locking pieces (as shown) or exactly four locking pieces (configuration not shown). Typically, lockingpieces 341 are integral withtubular 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. - For some applications, each of locking
pieces 341 is shaped so as to define two curvedproximal edges proximal tip 345. For some applications,proximal edges proximal edge 343A interconnect with the uneven edge surfaces ofproximal edge 343B, thereby creating friction on the at least onetether 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 inFIGS. 7A-B . Alternatively or additionally, for some applications, the uneven edge surfaces are rough. For some applications, lockingpieces 341 are convex, as viewed from outside tether-securingdevice 330, at least when lockingpieces 341 are in the relaxed state. - 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 inFIG. 7B ). For example the tips may be within 0.1 mm of each other, or touching each other. - For some applications, as shown,
tubular element 332 is cylindrical. Alternatively, the tubular element has another shape. For some applications, an axial length oftubular element 332 is at least 3 mm, no more than 50 mm, and/or between 3 and 50 mm; an axial length of tether-securingdevice 330 when in the unlocked configuration is between 3 and 50 mm; and/or an axial length of tether-securingdevice 330 when in the one-way-locked configuration is between 3 and 50 mm. - Reference is again made to
FIGS. 6A-C . For some applications, adelivery tool 380 is provided, which comprises aninner catheter shaft 382, which is configured to apply a constraining force to tether-securing device 360 wheninner shaft 382 is disposed in the securing-device lumen 336, as shown inFIG. 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 onetether 350 removably slidably passes. Typically, an outer diameter ofinner shaft 382 is between 80% and 99% of an inner diameter oftubular element 332 of tether-securingdevice 330. Typically,delivery tool 380 further comprises anouter shaft 384, which surroundsinner shaft 382. Typically, an inner diameter ofouter shaft 384 is between 80% and 99% of an outer diameter oftubular element 332 of tether-securingdevice 330. - 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, throughinferior vena cava 74, and intoright atrium 81, (b) via the basilic vein, through the subclavian vein throughsuperior vena cava 76, and intoright atrium 81, or (c) via the external jugular vein, through the subclavian vein throughsuperior vena cava 76, and intoright 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 toFIGS. 11-12C . - At the beginning of the procedure, tether-securing
device 330 resides oninner shaft 382, such that the inner shaft holds lockingpieces 341 in the constrained state, and tether-securingdevice 330 in the unlocked configuration. Adistal end 386 ofouter shaft 384 is held by the surgeon proximal to a proximal end of tether-securingdevice 330. Typically, tether-securingdevice 330 is delivered to a vicinity of the target site (e.g., to right atrium 81) with the at least onetether 350 pre-threaded through securing-device lumen 336. - As shown in
FIG. 6A , first and second tissue anchors 352A and 352B are implanted at respectivedifferent implantation sites 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 toFIGS. 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 inFIGS. 6A-C ,first tissue anchor 352A may be implanted within 1 cm of the site on the annulus that circumferentially corresponds to ananteroposterior commissure 112, andsecond tissue anchor 352B may be implanted within 1 cm of the site on the annulus that circumferentially corresponds to a circumferential middle 93 ofseptal 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 aseptoanterior commissure 114, and within 1 cm of the site on the annulus that circumferentially corresponds to a circumferential middle ofposterior leaflet 84, respectively, or (b) within 1 cm of the site on the annulus that circumferentially corresponds to a circumferential middle of theannulus 87 alonganterior leaflet 86, and within 1 cm of the site on the annulus that circumferentially corresponds toseptoposterior commissure 117, respectively. The direction of the 1 cm from the described anatomical sites may be either circumferentially around the annulus, up the wall ofright atrium 81 above annulus 83, or a combination of circumferentially around the annulus and up the wall of the atrium. - 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 advancinginner shaft 382 while proximally pulling on loopedmiddle portion 388 of tether 350 (shown and labeled inFIG. 6C ), such that portions oftether 350 pass throughinner shaft 382 and unlocked tether-securingdevice 330 mounted thereon. For example, a flexiblelongitudinal guide member 390 may be removably coupled to loopedmiddle portion 388 by aloop 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 flexiblelongitudinal guide member 390 of the present application). - After
tether 350 has been tensioned, tether-securingdevice 330 is transitioned to the one-way-locked configuration, by holding tether-securingdevice 330 in place by holdinginner shaft 382 in place, and distally advancingouter shaft 384, as shown inFIG. 6B . Tether-securingdevice 330 is pushed distally byouter shaft 384 overinner shaft 382 until lockingpieces 341 are no longer constrained byinner shaft 382, such that tether-securingdevice 330 automatically transitions to the one-way-locked configuration (in which lockingpieces 341 are in a relaxed, resting state). Since tether-securingdevice 330 allows proximal sliding oftether 350 therethrough even when in the one-way-locked configuration, if necessary further tension can be applied totether 350 by pushing tether-securingdevice 330 distally usingouter shaft 384. Once the tension has been applied, tether-securingdevice 330 maintains the tension. -
FIG. 6C shows valve-tensioning implant system 320 after tension has been applied and tether-securingdevice 330 has been fully deployed. The final disposition of anexcess portion 394 oftether 350 near loopedmiddle portion 388 is described hereinbelow with reference toFIGS. 8A-C . - Reference is now made to
FIGS. 8A-C , which are schematic illustrations of techniques for securingexcess portion 394 oftether 350, in accordance with respective applications of the present invention. As shown inFIG. 6C , aftertether 350 has been tensioned,excess portion 394 oftether 350 near loopedmiddle portion 388 remains free inright atrium 81. It is generally undesirable to leave this excess portion free to move around in the atrium. - In some applications of the present invention, valve-
tensioning implant system 320 further comprises avenous tissue anchor 400, for holdingexcess portion 394 secured in a desired disposition in the vasculature ofright 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 showvenous tissue anchor 400 disposed ininferior vena cava 74,superior vena cava 76, andcoronary sinus 115, respectively.Venous tissue anchor 400 is connected toexcess portion 394 by afixation tether 404, which may be connected toexcess portion 394 by aloop 780, such as a ring. Such connection is typically made after the tissue anchors have been implanted and tension has been applied totether 350, as described hereinabove with reference toFIGS. 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 tofixation tether 404, which tension is insufficient to alter the geometry of the atrium. - 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 toseptoanterior commissure 114, andsecond tissue anchor 352B is implanted within 1 cm of the site on the annulus that circumferentially corresponds toseptoposterior commissure 117. By way of example and not limitation, in the deployment configuration shown inFIG. 8B ,first tissue anchor 352A is implanted within 1 cm of the site on the annulus that circumferentially corresponds toanteroposterior commissure 112, andsecond tissue anchor 352B is implanted within 1 cm of the site on the annulus that circumferentially corresponds to circumferential middle 93 ofseptal leaflet 82. By way of example and not limitation, in the deployment configuration shown inFIG. 8C ,first tissue anchor 352A is implanted within 1 cm of the site on the annulus that circumferentially corresponds toanteroposterior commissure 112, andsecond tissue anchor 352B is implanted within 1 cm of the site on the annulus that circumferentially corresponds toseptoanterior commissure 114. The direction of the 1 cm from the described anatomical sites may be either circumferentially around the annulus, up the wall ofright atrium 81 above annulus 83, or a combination of circumferentially around the annulus and up the wall of the atrium. - For some applications,
venous tissue anchor 400 comprises anintraluminal 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. - 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 anchorstent 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 inU.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. - For applications in which
venous tissue anchor 400 is implanted insuperior 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 firstvenous tissue anchor 400 is implanted incoronary 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. - Alternatively,
excess portion 394 is cut and removed from the atrium, such as using techniques described hereinbelow with reference toFIG. 9 , mutatis mutandis. - 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 asimplant system 320, described hereinabove with reference toFIGS. 6A-C and 7A-B, and may incorporate any of the features thereof. In this configuration, the at least onetether 350 ofimplant system 420 comprises first andsecond tethers tether end portion 354A and a secondtether 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 secondtether end portion 354B. - For some applications, after tension is applied to first and
second tethers device 330 has been transitioned to the one-way-locked configuration,excess portions 494 oftethers cutting tool 498. Alternatively,excess portions 494 are held in a desired disposition, such as using techniques described hereinabove with reference toFIGS. 8A-C , mutatis mutandis. - Reference is made to
FIGS. 6A-C and 9. For applications in which the at least onetether 350 comprisessingle tether 350, such as exactly one tether 350 (as shown inFIGS. 6A-C ), the single tether typically has a length, measured betweenfirst tissue anchor 352A andsecond tissue anchor 352B, of at least 30 mm, no more than 160 mm, and/or between 30 and 160 mm. For some applications, loopedmiddle 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 onetether 350 comprises twotethers FIG. 9 , each oftethers 350 typically has a length of at least 20 mm, no more than 80 mm, and/or between 20 and 80 mm. Because eachtether 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. - Reference is now made to
FIGS. 10A-D , which are schematic illustrations of friction-enhancing features of atether 550, in accordance with respective applications of the present invention. These features may be used withtethers 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-securingdevice 30, orproximal edges pieces 341 of tether-securingdevice 330, as the case may be. - Typically,
tether 550 defines a plurality ofsecurement protrusions 560 spaced at intervals (I) alongtether 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-securingdevice 30, orproximal edges pieces 341 of tether-securingdevice 330, as the case may be. For some applications, an average interval ofsecurement protrusions 560 alongtether 550 is at least 1 mm, no more than 5 mm, and/or between 1 and 5 mm. - For some applications,
protrusions 560 are defined byrespective knots 570 intether 550, such as shown inFIG. 10A . For some applications,protrusions 560 compriserespective cones 572 ontether 550, such as shown inFIG. 10B . For some applications,protrusions 560 compriserespective scales 574 ontether 550, such as shown inFIG. 10C . For some applications,protrusions 560 compriserespective beads 576 ontether 550, such as shown inFIG. 10D . - 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 asimplant systems 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 toFIGS. 6A-7B , the delivery tool may be used for delivering the other implant systems described herein, mutatis mutandis. - For some applications,
implant system 320 comprises amale coupling 680 of a first flexible-longitudinal-member-coupling element 682 of anintraluminal 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. - Multiple-
anchor delivery tool 600 comprisesouter shaft 384 andinner shaft 382.Inner shaft 382 has proximal anddistal ends inner shaft 382 at first and secondlongitudinal locations longitudinal location 614 is more distal than secondlongitudinal location 616. In other words, the tissue anchors are initially positioned in the desired sequence of deployment ininner 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 bytether 350. - Multiple-
anchor delivery tool 600 further comprises first andsecond torque cables second heads inner shaft 382 proximally from first andsecond heads coupling elements coupling elements portion 630 offirst torque cable 620 is initially removably positioned alongsidesecond tissue anchor 352B ininner shaft 382. Thus each anchor is separately connected to acontrol 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. - For some applications,
implant system 320 comprises one or more additional tissue anchors, andtool 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 ininner shaft 382 proximal to secondlongitudinal 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 ininner shaft 382 at a third longitudinal location that is more proximal than secondlongitudinal 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. - For some applications,
first torque cable 620 is shaped so as to define alumen 640 therethrough, and multiple-anchor delivery tool 600 further comprises a sharpenedwire 642, which removably passes throughlumen 640. A distal end offirst torque cable 620 comprises adistal coupling element 650, which is configured to be removably coupled to a correspondingproximal coupling element 652 defined by a proximal portion offirst head 670A. Distal andproximal coupling elements First head 670A, includingproximal coupling element 652, is shaped so as to define a firstlongitudinal channel 656 at least partially therethrough (typically entirely therethrough), which channel is coaxial withfirst head 670A.Distal coupling element 650 is shaped so as to define a secondlongitudinal channel 658 therethrough, which is coaxial withlumen 640 offirst torque cable 620. First andsecond channels wire 642 is positioned in these channels, the sharpened wire prevents decoupling ofdistal coupling element 650 fromproximal coupling element 652. Upon removal of sharpenedwire 642 fromchannels coupling elements - For some applications, sharpened
wire 642 is shaped so as to define a sharpdistal tip 660. For these applications,first tissue anchor 352A typically is helical, and sharpenedwire 642 is initially removably positioned within a channel defined by the helix. Astissue anchor 352A is screwed into tissue, sharpenedwire 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, aftertissue anchor 352A has been fully implanted, sharpenedwire 642 is withdrawn entirely from the tissue, and removed from the patient's body. Optionally, the sharp distal tip of sharpenedwire 642 is inserted into the tissue slightly, even before insertion oftissue 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. - After implantation of
tissue anchor 352A, sharpenedwire 642 is withdrawn proximally from the channel oftissue anchor 352A and fromchannels proximal coupling elements first torque cable 620 fromfirst head 670A. After such proximal withdrawal, sharpenedwire 642 typically remains withinlumen 640 offirst torque cable 620. - For some applications, the decoupling of
first torque cable 620 andfirst 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. -
Second torque cable 622 andsecond 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. - 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 throughinner 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. - 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 andouter 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, throughinferior vena cava 74, and intoright atrium 81, (b) via the basilic vein, through the subclavian vein throughsuperior vena cava 76, and intoright atrium 81, or (c) via the external jugular vein, through the subclavian vein throughsuperior vena cava 76, and intoright 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. -
Distal end 612 ofinner 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 ininner shaft 382 at first and secondlongitudinal locations longitudinal location 614 more distal than secondlongitudinal location 616.Portion 630 offirst torque cable 620 is removably positioned alongsidesecond tissue anchor 352B ininner shaft 382. Thus,inner shaft 382 does not need to be withdrawn and reintroduced from the body during the implantation procedure. - As shown in
FIG. 12A ,first tissue anchor 352A is implanted intotissue 700 of the subject (e.g., cardiac muscle tissue, such as atrial tissue) by rotatingfirst torque cable 620, using control handle 770, and, typically pushing distally on the torque cable. - As shown in
FIG. 12B , afterfirst tissue anchor 352A has been fully implanted intissue 700,first torque cable 620 is decoupled fromfirst tissue anchor 352A, such as by proximally withdrawing sharpenedwire 642, as described hereinabove with reference toFIG. 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. - As shown in
FIG. 12C , afterfirst tissue anchor 352A is implanted,second tissue anchor 352B is distally advanced ininner shaft 382, and implanted intotissue 700 by rotatingsecond torque cable 622. The second torque cable is decoupled fromsecond tissue anchor 352B (not shown). First and second tissue anchors 352A and 352B remain implanted intissue 700, connected bytether 350. - 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, flexiblelongitudinal guide member 390 may be removably coupled to loopedmiddle portion 88 oftether 350 byloop 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. Aftertether 350 is tensioned, tether-securingdevice 330 is deployed to its one-way-locked configuration, in order to maintain the tension, usingouter shaft 384, as described hereinabove with reference toFIG. 6C . Once the tension has been applied, tether-securingdevice 330 maintains the tension. - 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:
-
- U.S. Pat. No. 8,475,525 to Maisano et al.;
- 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;
- U.S. application Ser. No. 13/188,175, filed Jul. 21, 2011, which published as US Patent Application Publication 2012/0035712;
- U.S. application Ser. No. 13/485,145, filed May 31, 2012, which published as US Patent Application Publication 2013/0325115;
- U.S. application Ser. No. 13/553,081, filed Jul. 19, 2012, which published as US Patent Application Publication 2013/0018459;
- International Application PCT/IL2012/000282, filed Jul. 19, 2012, which published as PCT Publication WO 2013/011502;
-
U.S. Provisional Application 61/750,427, filed Jan. 9, 2013; -
U.S. Provisional Application 61/783,224, filed Mar. 14, 2013; - International Application PCT/IL2013/050470, filed May 30, 2013, which published as PCT Publication WO 2013/179295;
-
U.S. Provisional Application 61/897,509, filed Oct. 30, 2013; - U.S. application Ser. No. 14/143,355, filed Dec. 30, 2013, which published as US Patent Application Publication 2014/0114390;
- International Application PCT/IL2014/050027, filed Jan. 9, 2014, which published as PCT Publication WO 2014/108903;
- International Application PCT/IL2014/050233, filed Mar. 9, 2014, which published as PCT Publication WO 2014/141239; and
- U.S. Provisional Application 62/014,397, filed Jun. 19, 2014.
- 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.
- 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.
Claims (20)
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US14/525,668 US10022114B2 (en) | 2013-10-30 | 2014-10-28 | Percutaneous tether locking |
US16/035,654 US20180344311A1 (en) | 2013-10-30 | 2018-07-15 | Percutaneous Tether Locking |
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Cited By (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US10925731B2 (en) | 2016-12-30 | 2021-02-23 | Pipeline Medical Technologies, Inc. | Method and apparatus for transvascular implantation of neo chordae tendinae |
US11083580B2 (en) | 2016-12-30 | 2021-08-10 | Pipeline Medical Technologies, Inc. | Method of securing a leaflet anchor to a mitral valve leaflet |
US11684475B2 (en) | 2016-12-30 | 2023-06-27 | Pipeline Medical Technologies, Inc. | Method and apparatus for transvascular implantation of neo chordae tendinae |
US11696828B2 (en) | 2016-12-30 | 2023-07-11 | Pipeline Medical Technologies, Inc. | Method and apparatus for mitral valve chord repair |
US11766331B2 (en) | 2020-05-27 | 2023-09-26 | Politecnico Di Milano | Device and assembly to repair a heart valve |
Families Citing this family (68)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE102007043830A1 (en) | 2007-09-13 | 2009-04-02 | Lozonschi, Lucian, Madison | Heart valve stent |
WO2011072084A2 (en) | 2009-12-08 | 2011-06-16 | Avalon Medical Ltd. | Device and system for transcatheter mitral valve replacement |
US9307980B2 (en) | 2010-01-22 | 2016-04-12 | 4Tech Inc. | Tricuspid valve repair using tension |
US10058323B2 (en) | 2010-01-22 | 2018-08-28 | 4 Tech Inc. | Tricuspid valve repair using tension |
US8475525B2 (en) | 2010-01-22 | 2013-07-02 | 4Tech Inc. | Tricuspid valve repair using tension |
CA2957442C (en) | 2011-08-11 | 2019-06-04 | Tendyne Holdings, Inc. | Improvements for prosthetic valves and related inventions |
US9827092B2 (en) | 2011-12-16 | 2017-11-28 | Tendyne Holdings, Inc. | Tethers for prosthetic mitral valve |
US8961594B2 (en) | 2012-05-31 | 2015-02-24 | 4Tech Inc. | Heart valve repair system |
WO2014022124A1 (en) | 2012-07-28 | 2014-02-06 | Tendyne Holdings, Inc. | Improved multi-component designs for heart valve retrieval device, sealing structures and stent assembly |
US9675454B2 (en) | 2012-07-30 | 2017-06-13 | Tendyne Holdings, Inc. | Delivery systems and methods for transcatheter prosthetic valves |
EP2943132B1 (en) | 2013-01-09 | 2018-03-28 | 4Tech Inc. | Soft tissue anchors |
WO2014134183A1 (en) | 2013-02-26 | 2014-09-04 | Mitralign, Inc. | Devices and methods for percutaneous tricuspid valve repair |
JP6329570B2 (en) * | 2013-03-14 | 2018-05-23 | 4テック インコーポレイテッド | Stent with tether interface |
US10463489B2 (en) | 2013-04-02 | 2019-11-05 | Tendyne Holdings, Inc. | Prosthetic heart valve and systems and methods for delivering the same |
US11224510B2 (en) | 2013-04-02 | 2022-01-18 | Tendyne Holdings, Inc. | Prosthetic heart valve and systems and methods for delivering the same |
US10478293B2 (en) | 2013-04-04 | 2019-11-19 | Tendyne Holdings, Inc. | Retrieval and repositioning system for prosthetic heart valve |
US9610159B2 (en) | 2013-05-30 | 2017-04-04 | Tendyne Holdings, Inc. | Structural members for prosthetic mitral valves |
EP3013250A4 (en) | 2013-06-25 | 2017-05-31 | Mitralign, Inc. | Percutaneous valve repair by reshaping and resizing right ventricle |
CA2914856C (en) | 2013-06-25 | 2021-03-09 | Chad Perrin | Thrombus management and structural compliance features for prosthetic heart valves |
CA2919379C (en) | 2013-08-01 | 2021-03-30 | Tendyne Holdings, Inc. | Epicardial anchor devices and methods |
WO2015058039A1 (en) | 2013-10-17 | 2015-04-23 | Robert Vidlund | Apparatus and methods for alignment and deployment of intracardiac devices |
JP6554094B2 (en) | 2013-10-28 | 2019-07-31 | テンダイン ホールディングス,インコーポレイテッド | Prosthetic heart valve and system and method for delivering an artificial heart valve |
US9526611B2 (en) | 2013-10-29 | 2016-12-27 | Tendyne Holdings, Inc. | Apparatus and methods for delivery of transcatheter prosthetic valves |
EP3062709A2 (en) | 2013-10-30 | 2016-09-07 | 4Tech Inc. | Multiple anchoring-point tension system |
US10052095B2 (en) | 2013-10-30 | 2018-08-21 | 4Tech Inc. | Multiple anchoring-point tension system |
WO2015120122A2 (en) | 2014-02-05 | 2015-08-13 | Robert Vidlund | Apparatus and methods for transfemoral delivery of prosthetic mitral valve |
US9986993B2 (en) | 2014-02-11 | 2018-06-05 | Tendyne Holdings, Inc. | Adjustable tether and epicardial pad system for prosthetic heart valve |
CA2937566C (en) | 2014-03-10 | 2023-09-05 | Tendyne Holdings, Inc. | Devices and methods for positioning and monitoring tether load for prosthetic mitral valve |
US9801720B2 (en) | 2014-06-19 | 2017-10-31 | 4Tech Inc. | Cardiac tissue cinching |
GB2530487B (en) * | 2014-09-17 | 2016-12-28 | Cardiomech As | Device for heart repair |
WO2016087934A1 (en) | 2014-12-02 | 2016-06-09 | 4Tech Inc. | Off-center tissue anchors |
AU2016205371B2 (en) | 2015-01-07 | 2019-10-10 | Tendyne Holdings, Inc. | Prosthetic mitral valves and apparatus and methods for delivery of same |
ES2877699T3 (en) | 2015-02-05 | 2021-11-17 | Tendyne Holdings Inc | Prosthetic Heart Valve with Ligation and Expandable Epicardial Pad |
US10010315B2 (en) | 2015-03-18 | 2018-07-03 | Mitralign, Inc. | Tissue anchors and percutaneous tricuspid valve repair using a tissue anchor |
EP4070763A1 (en) | 2015-04-16 | 2022-10-12 | Tendyne Holdings, Inc. | Apparatus for retrieval of transcathter prosthetic valves |
JP6816889B2 (en) | 2015-05-28 | 2021-01-20 | 4テック インコーポレイテッド | Eccentric tissue anchor with tension member |
US10327894B2 (en) | 2015-09-18 | 2019-06-25 | Tendyne Holdings, Inc. | Methods for delivery of prosthetic mitral valves |
JP2018535754A (en) | 2015-12-03 | 2018-12-06 | テンダイン ホールディングス,インコーポレイテッド | Frame features for artificial mitral valves |
WO2017117109A1 (en) | 2015-12-28 | 2017-07-06 | Tendyne Holdings, Inc. | Atrial pocket closures for prosthetic heart valves |
US10751182B2 (en) | 2015-12-30 | 2020-08-25 | Edwards Lifesciences Corporation | System and method for reshaping right heart |
US10828160B2 (en) | 2015-12-30 | 2020-11-10 | Edwards Lifesciences Corporation | System and method for reducing tricuspid regurgitation |
US10470877B2 (en) | 2016-05-03 | 2019-11-12 | Tendyne Holdings, Inc. | Apparatus and methods for anterior valve leaflet management |
US20200146854A1 (en) | 2016-05-16 | 2020-05-14 | Elixir Medical Corporation | Methods and devices for heart valve repair |
WO2017218375A1 (en) | 2016-06-13 | 2017-12-21 | Tendyne Holdings, Inc. | Sequential delivery of two-part prosthetic mitral valve |
CN109640887B (en) | 2016-06-30 | 2021-03-16 | 坦迪尼控股股份有限公司 | Prosthetic heart valve and apparatus and method for delivering same |
EP3484411A1 (en) | 2016-07-12 | 2019-05-22 | Tendyne Holdings, Inc. | Apparatus and methods for trans-septal retrieval of prosthetic heart valves |
WO2018035378A1 (en) | 2016-08-18 | 2018-02-22 | 4Tech Inc. | Tissue anchors with flexible tips for insertion into the pericardial cavity |
WO2018148324A1 (en) | 2017-02-08 | 2018-08-16 | 4 Tech Inc. | Implantable force gauges |
US10682229B2 (en) | 2017-02-08 | 2020-06-16 | 4Tech Inc. | Post-implantation tensioning in cardiac implants |
WO2018160456A1 (en) | 2017-03-01 | 2018-09-07 | 4Tech Inc. | Post-implantation tension adjustment in cardiac implants |
US11045627B2 (en) | 2017-04-18 | 2021-06-29 | Edwards Lifesciences Corporation | Catheter system with linear actuation control mechanism |
JP6736193B2 (en) | 2017-06-08 | 2020-08-05 | 4テック インコーポレイテッド | Tissue anchor with tether stop |
WO2019013994A1 (en) | 2017-07-10 | 2019-01-17 | 4Tech Inc. | Tissue anchors with load-bearing features |
US11154399B2 (en) | 2017-07-13 | 2021-10-26 | Tendyne Holdings, Inc. | Prosthetic heart valves and apparatus and methods for delivery of same |
CN111031967B (en) | 2017-08-28 | 2022-08-09 | 坦迪尼控股股份有限公司 | Prosthetic heart valve with tether connection features |
WO2019074815A1 (en) | 2017-10-10 | 2019-04-18 | 4Tech Inc. | Force-distributing anchor system |
EP3661428B1 (en) | 2017-10-31 | 2021-07-21 | 4Tech Inc. | Tissue anchors with hemostasis features |
US20200360001A1 (en) | 2018-02-09 | 2020-11-19 | 4Tech Inc. | Frustoconical Hemostatic Sealing Elements |
JP2022502095A (en) | 2018-08-07 | 2022-01-11 | 4テック インコーポレイテッド | Post-embedding tension in cardiac implants |
EP3902484A1 (en) | 2018-12-24 | 2021-11-03 | 4 Tech Inc. | Self-locking tissue anchors |
WO2020214818A1 (en) * | 2019-04-16 | 2020-10-22 | Neochord, Inc. | Transverse helical cardiac anchor for minimally invasive heart valve repair |
CA3221458A1 (en) * | 2019-05-09 | 2020-11-12 | W. L. Gore & Associates, Inc. | Continuous tethered tissue anchor and associated systems and methods |
US20210015475A1 (en) * | 2019-07-16 | 2021-01-21 | Jan R. Lau | Tissue remodeling systems and methods |
US11648110B2 (en) | 2019-12-05 | 2023-05-16 | Tendyne Holdings, Inc. | Braided anchor for mitral valve |
US11648114B2 (en) | 2019-12-20 | 2023-05-16 | Tendyne Holdings, Inc. | Distally loaded sheath and loading funnel |
US11951002B2 (en) | 2020-03-30 | 2024-04-09 | Tendyne Holdings, Inc. | Apparatus and methods for valve and tether fixation |
EP4199860A1 (en) | 2020-08-19 | 2023-06-28 | Tendyne Holdings, Inc. | Fully-transseptal apical pad with pulley for tensioning |
EP4329634A1 (en) * | 2021-04-30 | 2024-03-06 | Davol Inc. | Tissue aperture closure device |
Family Cites Families (528)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3874388A (en) | 1973-02-12 | 1975-04-01 | Ochsner Med Found Alton | Shunt defect closure system |
US4214349A (en) | 1978-11-30 | 1980-07-29 | Midland-Ross Corporation | Tie wrap |
GB2084468B (en) | 1980-09-25 | 1984-06-06 | South African Inventions | Surgical implant |
IT1144379B (en) | 1981-07-14 | 1986-10-29 | Sorin Biomedica Spa | CARDIAC VALVE PROSTHESIS |
US4493329A (en) | 1982-08-19 | 1985-01-15 | Lynn Crawford | Implantable electrode having different stiffening and curvature maintaining characteristics along its length |
DE3230858C2 (en) | 1982-08-19 | 1985-01-24 | Ahmadi, Ali, Dr. med., 7809 Denzlingen | Ring prosthesis |
US4532926A (en) | 1983-06-20 | 1985-08-06 | Ethicon, Inc. | Two-piece tissue fastener with ratchet leg staple and sealable latching receiver |
US4625727A (en) | 1985-01-24 | 1986-12-02 | Leiboff Arnold R | Anastomosis device with excisable frame |
US4853986A (en) | 1986-01-02 | 1989-08-08 | The Awareness Marketing Corporation | Water level control |
FI85223C (en) | 1988-11-10 | 1992-03-25 | Biocon Oy | BIODEGRADERANDE SURGICAL IMPLANT OCH MEDEL. |
SE467459B (en) | 1990-09-25 | 1992-07-20 | Allset Marine Lashing Ab | WIRELESS BEFORE HEARING CHARGES TO CONTAINERS |
US5108420A (en) | 1991-02-01 | 1992-04-28 | Temple University | Aperture occlusion device |
US5330521A (en) | 1992-06-29 | 1994-07-19 | Cohen Donald M | Low resistance implantable electrical leads |
ES2049653B1 (en) | 1992-10-05 | 1994-12-16 | Velazquez Francisco Farrer | CORRECTIVE DEVICE FOR FEMALE URINARY INCONTINENCE. |
US5374286A (en) | 1993-03-31 | 1994-12-20 | Medtronic, Inc. | Torque indicator for fixed screw leads |
US6776754B1 (en) | 2000-10-04 | 2004-08-17 | Wilk Patent Development Corporation | Method for closing off lower portion of heart ventricle |
US5450860A (en) | 1993-08-31 | 1995-09-19 | W. L. Gore & Associates, Inc. | Device for tissue repair and method for employing same |
CA2141911C (en) | 1994-02-24 | 2002-04-23 | Jude S. Sauer | Surgical crimping device and method of use |
US5843120A (en) | 1994-03-17 | 1998-12-01 | Medinol Ltd. | Flexible-expandable stent |
AU3783195A (en) | 1994-11-15 | 1996-05-23 | Advanced Cardiovascular Systems Inc. | Intraluminal stent for attaching a graft |
US6743198B1 (en) | 1995-03-20 | 2004-06-01 | Conticare Medical, Inc. | Self-cleansing bladder drainage device |
US5662683A (en) | 1995-08-22 | 1997-09-02 | Ortho Helix Limited | Open helical organic tissue anchor and method of facilitating healing |
EP0775471B1 (en) | 1995-11-27 | 2002-05-29 | Schneider (Europe) GmbH | A stent for use in a body passage way |
US5957953A (en) | 1996-02-16 | 1999-09-28 | Smith & Nephew, Inc. | Expandable suture anchor |
US5776178A (en) | 1996-02-21 | 1998-07-07 | Medtronic, Inc. | Medical electrical lead with surface treatment for enhanced fixation |
US6402780B2 (en) | 1996-02-23 | 2002-06-11 | Cardiovascular Technologies, L.L.C. | Means and method of replacing a heart valve in a minimally invasive manner |
US5853422A (en) | 1996-03-22 | 1998-12-29 | Scimed Life Systems, Inc. | Apparatus and method for closing a septal defect |
US6702846B2 (en) | 1996-04-09 | 2004-03-09 | Endocare, Inc. | Urological stent therapy system and method |
US5948000A (en) | 1996-10-03 | 1999-09-07 | United States Surgical Corporation | System for suture anchor placement |
US5961440A (en) | 1997-01-02 | 1999-10-05 | Myocor, Inc. | Heart wall tension reduction apparatus and method |
US6077214A (en) | 1998-07-29 | 2000-06-20 | Myocor, Inc. | Stress reduction apparatus and method |
US6406420B1 (en) | 1997-01-02 | 2002-06-18 | Myocor, Inc. | Methods and devices for improving cardiac function in hearts |
US6050936A (en) | 1997-01-02 | 2000-04-18 | Myocor, Inc. | Heart wall tension reduction apparatus |
US7883539B2 (en) | 1997-01-02 | 2011-02-08 | Edwards Lifesciences Llc | Heart wall tension reduction apparatus and method |
US6045497A (en) | 1997-01-02 | 2000-04-04 | Myocor, Inc. | Heart wall tension reduction apparatus and method |
US5928281A (en) | 1997-03-27 | 1999-07-27 | Baxter International Inc. | Tissue heart valves |
US6251109B1 (en) | 1997-06-27 | 2001-06-26 | Daig Corporation | Process and device for the treatment of atrial arrhythmia |
US6042606A (en) | 1997-09-29 | 2000-03-28 | Cook Incorporated | Radially expandable non-axially contracting surgical stent |
US6027523A (en) | 1997-10-06 | 2000-02-22 | Arthrex, Inc. | Suture anchor with attached disk |
US6332893B1 (en) | 1997-12-17 | 2001-12-25 | Myocor, Inc. | Valve to myocardium tension members device and method |
US6193734B1 (en) | 1998-01-23 | 2001-02-27 | Heartport, Inc. | System for performing vascular anastomoses |
US6533807B2 (en) | 1998-02-05 | 2003-03-18 | Medtronic, Inc. | Radially-expandable stent and delivery system |
EP1079740B1 (en) | 1998-05-21 | 2007-08-29 | Christopher J. Walshe | A tissue anchor system |
US7063711B1 (en) | 1998-05-29 | 2006-06-20 | By-Pass, Inc. | Vascular surgery |
US6260552B1 (en) | 1998-07-29 | 2001-07-17 | Myocor, Inc. | Transventricular implant tools and devices |
US6129713A (en) | 1998-08-11 | 2000-10-10 | Embol-X, Inc. | Slidable cannula and method of use |
CN2398971Y (en) | 1998-09-19 | 2000-10-04 | 周沛林 | Length detectable sacculus catheter |
EP1073385A2 (en) | 1999-01-22 | 2001-02-07 | Gore Enterprise Holdings, Inc. | A biliary stent-graft |
US8137364B2 (en) | 2003-09-11 | 2012-03-20 | Abbott Laboratories | Articulating suturing device and method |
US7842048B2 (en) | 2006-08-18 | 2010-11-30 | Abbott Laboratories | Articulating suture device and method |
US6298272B1 (en) | 1999-03-29 | 2001-10-02 | Cardiac Pacemakers, Inc. | High impedance electrode tip with internal drug delivery capability |
US7666204B2 (en) | 1999-04-09 | 2010-02-23 | Evalve, Inc. | Multi-catheter steerable guiding system and methods of use |
US6752813B2 (en) | 1999-04-09 | 2004-06-22 | Evalve, Inc. | Methods and devices for capturing and fixing leaflets in valve repair |
EP2078498B1 (en) | 1999-04-09 | 2010-12-22 | Evalve, Inc. | Apparatus for cardiac valve repair |
US6183512B1 (en) | 1999-04-16 | 2001-02-06 | Edwards Lifesciences Corporation | Flexible annuloplasty system |
US6273911B1 (en) | 1999-04-22 | 2001-08-14 | Advanced Cardiovascular Systems, Inc. | Variable strength stent |
US20050222665A1 (en) | 1999-04-23 | 2005-10-06 | Ernest Aranyi | Endovascular fastener applicator |
US6626899B2 (en) | 1999-06-25 | 2003-09-30 | Nidus Medical, Llc | Apparatus and methods for treating tissue |
SE514718C2 (en) | 1999-06-29 | 2001-04-09 | Jan Otto Solem | Apparatus for treating defective closure of the mitral valve apparatus |
US6997951B2 (en) | 1999-06-30 | 2006-02-14 | Edwards Lifesciences Ag | Method and device for treatment of mitral insufficiency |
US7192442B2 (en) | 1999-06-30 | 2007-03-20 | Edwards Lifesciences Ag | Method and device for treatment of mitral insufficiency |
US6592609B1 (en) | 1999-08-09 | 2003-07-15 | Bonutti 2003 Trust-A | Method and apparatus for securing tissue |
US6338738B1 (en) | 1999-08-31 | 2002-01-15 | Edwards Lifesciences Corp. | Device and method for stabilizing cardiac tissue |
DE60033827T2 (en) | 1999-09-13 | 2007-12-20 | Rex Medical, L.P. | VASCULAR WOUND CLOSURE |
US6231561B1 (en) | 1999-09-20 | 2001-05-15 | Appriva Medical, Inc. | Method and apparatus for closing a body lumen |
US6626930B1 (en) | 1999-10-21 | 2003-09-30 | Edwards Lifesciences Corporation | Minimally invasive mitral valve repair method and apparatus |
AUPQ366099A0 (en) | 1999-10-26 | 1999-11-18 | Queensland University Of Technology | Ortho paedic screw |
US7169187B2 (en) | 1999-12-22 | 2007-01-30 | Ethicon, Inc. | Biodegradable stent |
US6494908B1 (en) | 1999-12-22 | 2002-12-17 | Ethicon, Inc. | Removable stent for body lumens |
US6989028B2 (en) | 2000-01-31 | 2006-01-24 | Edwards Lifesciences Ag | Medical system and method for remodeling an extravascular tissue structure |
US6402781B1 (en) | 2000-01-31 | 2002-06-11 | Mitralife | Percutaneous mitral annuloplasty and cardiac reinforcement |
US7011682B2 (en) | 2000-01-31 | 2006-03-14 | Edwards Lifesciences Ag | Methods and apparatus for remodeling an extravascular tissue structure |
US6797002B2 (en) | 2000-02-02 | 2004-09-28 | Paul A. Spence | Heart valve repair apparatus and methods |
US7993368B2 (en) | 2003-03-13 | 2011-08-09 | C.R. Bard, Inc. | Suture clips, delivery devices and methods |
US6537198B1 (en) | 2000-03-21 | 2003-03-25 | Myocor, Inc. | Splint assembly for improving cardiac function in hearts, and method for implanting the splint assembly |
US7083628B2 (en) | 2002-09-03 | 2006-08-01 | Edwards Lifesciences Corporation | Single catheter mitral valve repair device and method for use |
WO2001089426A1 (en) | 2000-05-25 | 2001-11-29 | Bioring S.A. | Device for shrinking or reinforcing the heart valvular orifices |
US7632303B1 (en) | 2000-06-07 | 2009-12-15 | Advanced Cardiovascular Systems, Inc. | Variable stiffness medical devices |
US6575976B2 (en) | 2000-06-12 | 2003-06-10 | Arthrex, Inc. | Expandable tissue anchor |
US7077861B2 (en) | 2000-07-06 | 2006-07-18 | Medtentia Ab | Annuloplasty instrument |
US6613078B1 (en) | 2000-08-02 | 2003-09-02 | Hector Daniel Barone | Multi-component endoluminal graft assembly, use thereof and method of implanting |
SE0002878D0 (en) | 2000-08-11 | 2000-08-11 | Kimblad Ola | Device and method of treatment of atrioventricular regurgitation |
US7510572B2 (en) | 2000-09-12 | 2009-03-31 | Shlomo Gabbay | Implantation system for delivery of a heart valve prosthesis |
US8956407B2 (en) | 2000-09-20 | 2015-02-17 | Mvrx, Inc. | Methods for reshaping a heart valve annulus using a tensioning implant |
WO2004030570A2 (en) | 2002-10-01 | 2004-04-15 | Ample Medical, Inc. | Devices for retaining native heart valve leaflet |
US20080091264A1 (en) | 2002-11-26 | 2008-04-17 | Ample Medical, Inc. | Devices, systems, and methods for reshaping a heart valve annulus, including the use of magnetic tools |
US6893459B1 (en) | 2000-09-20 | 2005-05-17 | Ample Medical, Inc. | Heart valve annulus device and method of using same |
US20050228422A1 (en) | 2002-11-26 | 2005-10-13 | Ample Medical, Inc. | Devices, systems, and methods for reshaping a heart valve annulus, including the use of magnetic tools |
US8784482B2 (en) | 2000-09-20 | 2014-07-22 | Mvrx, Inc. | Method of reshaping a heart valve annulus using an intravascular device |
US7691144B2 (en) | 2003-10-01 | 2010-04-06 | Mvrx, Inc. | Devices, systems, and methods for reshaping a heart valve annulus |
US20060106278A1 (en) | 2004-05-14 | 2006-05-18 | Ample Medical, Inc. | Devices, systems, and methods for reshaping a heart valve annulus, including the use of an adjustable bridge implant system |
US20060106279A1 (en) | 2004-05-14 | 2006-05-18 | Ample Medical, Inc. | Devices, systems, and methods for reshaping a heart valve annulus, including the use of a bridge implant having an adjustable bridge stop |
US6602288B1 (en) | 2000-10-05 | 2003-08-05 | Edwards Lifesciences Corporation | Minimally-invasive annuloplasty repair segment delivery template, system and method of use |
US6616684B1 (en) | 2000-10-06 | 2003-09-09 | Myocor, Inc. | Endovascular splinting devices and methods |
US6723038B1 (en) | 2000-10-06 | 2004-04-20 | Myocor, Inc. | Methods and devices for improving mitral valve function |
US7041097B1 (en) | 2000-12-21 | 2006-05-09 | Cardiac Pacemakers, Inc. | System and method for accessing the coronary sinus |
US6929660B1 (en) | 2000-12-22 | 2005-08-16 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US6810882B2 (en) | 2001-01-30 | 2004-11-02 | Ev3 Santa Rosa, Inc. | Transluminal mitral annuloplasty |
US20020107531A1 (en) | 2001-02-06 | 2002-08-08 | Schreck Stefan G. | Method and system for tissue repair using dual catheters |
IL157732A0 (en) | 2001-03-08 | 2004-03-28 | Atritech Inc | Atrial filter implants |
US6622730B2 (en) | 2001-03-30 | 2003-09-23 | Myocor, Inc. | Device for marking and aligning positions on the heart |
US6619291B2 (en) | 2001-04-24 | 2003-09-16 | Edwin J. Hlavka | Method and apparatus for catheter-based annuloplasty |
US20090143808A1 (en) | 2001-04-24 | 2009-06-04 | Houser Russell A | Guided Tissue Cutting Device, Method of Use and Kits Therefor |
US8202315B2 (en) | 2001-04-24 | 2012-06-19 | Mitralign, Inc. | Catheter-based annuloplasty using ventricularly positioned catheter |
ITMI20011012A1 (en) | 2001-05-17 | 2002-11-17 | Ottavio Alfieri | ANNULAR PROSTHESIS FOR MITRAL VALVE |
US6641597B2 (en) | 2001-05-25 | 2003-11-04 | Arthrex, Inc. | Interference fit knotless suture anchor fixation |
JP4908737B2 (en) | 2001-06-21 | 2012-04-04 | アボット ラボラトリーズ バスキュラー エンタープライズ リミテッド | Method and apparatus for traversing a heart valve |
FR2826863B1 (en) | 2001-07-04 | 2003-09-26 | Jacques Seguin | ASSEMBLY FOR PLACING A PROSTHETIC VALVE IN A BODY CONDUIT |
WO2003009773A2 (en) | 2001-07-26 | 2003-02-06 | Alveolus Inc. | Removable stent and method of using the same |
US6997944B2 (en) | 2001-08-13 | 2006-02-14 | Advanced Cardiovascular Systems, Inc. | Apparatus and method for decreasing stent gap size |
US7125421B2 (en) | 2001-08-31 | 2006-10-24 | Mitral Interventions, Inc. | Method and apparatus for valve repair |
US7338506B2 (en) | 2001-09-05 | 2008-03-04 | Caro Nicholas C | Scleral clip and procedures for using same |
US20060052821A1 (en) | 2001-09-06 | 2006-03-09 | Ovalis, Inc. | Systems and methods for treating septal defects |
JP4458845B2 (en) | 2001-10-01 | 2010-04-28 | アンプル メディカル,インコーポレイテッド | Medical device |
US6893460B2 (en) | 2001-10-11 | 2005-05-17 | Percutaneous Valve Technologies Inc. | Implantable prosthetic valve |
US7144363B2 (en) | 2001-10-16 | 2006-12-05 | Extensia Medical, Inc. | Systems for heart treatment |
US6949122B2 (en) | 2001-11-01 | 2005-09-27 | Cardiac Dimensions, Inc. | Focused compression mitral valve device and method |
US8231639B2 (en) | 2001-11-28 | 2012-07-31 | Aptus Endosystems, Inc. | Systems and methods for attaching a prosthesis within a body lumen or hollow organ |
US20050177180A1 (en) | 2001-11-28 | 2005-08-11 | Aptus Endosystems, Inc. | Devices, systems, and methods for supporting tissue and/or structures within a hollow body organ |
US20030176914A1 (en) | 2003-01-21 | 2003-09-18 | Rabkin Dmitry J. | Multi-segment modular stent and methods for manufacturing stents |
US6908478B2 (en) | 2001-12-05 | 2005-06-21 | Cardiac Dimensions, Inc. | Anchor and pull mitral valve device and method |
US6976995B2 (en) | 2002-01-30 | 2005-12-20 | Cardiac Dimensions, Inc. | Fixed length anchor and pull mitral valve device and method |
US6793673B2 (en) | 2002-12-26 | 2004-09-21 | Cardiac Dimensions, Inc. | System and method to effect mitral valve annulus of a heart |
US6746457B2 (en) | 2001-12-07 | 2004-06-08 | Abbott Laboratories | Snared suture trimmer |
US6978176B2 (en) | 2001-12-08 | 2005-12-20 | Lattouf Omar M | Treatment for patient with congestive heart failure |
WO2003053289A1 (en) | 2001-12-21 | 2003-07-03 | Simcha Milo | Implantation system for annuloplasty rings |
SE524709C2 (en) | 2002-01-11 | 2004-09-21 | Edwards Lifesciences Ag | Device for delayed reshaping of a heart vessel and a heart valve |
US6764510B2 (en) | 2002-01-09 | 2004-07-20 | Myocor, Inc. | Devices and methods for heart valve treatment |
CA2688796A1 (en) | 2002-01-11 | 2003-07-10 | Edwards Lifesciences Ag. | Delayed memory device |
US7048754B2 (en) | 2002-03-01 | 2006-05-23 | Evalve, Inc. | Suture fasteners and methods of use |
US6797001B2 (en) | 2002-03-11 | 2004-09-28 | Cardiac Dimensions, Inc. | Device, assembly and method for mitral valve repair |
US7094244B2 (en) | 2002-03-26 | 2006-08-22 | Edwards Lifesciences Corporation | Sequential heart valve leaflet repair device and method of use |
JP2005525169A (en) | 2002-05-10 | 2005-08-25 | コーディス・コーポレイション | Method of making a medical device having a thin wall tubular membrane on a structural frame |
US7351256B2 (en) | 2002-05-10 | 2008-04-01 | Cordis Corporation | Frame based unidirectional flow prosthetic implant |
US20040117004A1 (en) | 2002-05-16 | 2004-06-17 | Osborne Thomas A. | Stent and method of forming a stent with integral barbs |
US7416556B2 (en) | 2002-06-06 | 2008-08-26 | Abbott Laboratories | Stop-cock suture clamping system |
AU2003247526A1 (en) | 2002-06-12 | 2003-12-31 | Mitral Interventions, Inc. | Method and apparatus for tissue connection |
US20050107811A1 (en) | 2002-06-13 | 2005-05-19 | Guided Delivery Systems, Inc. | Delivery devices and methods for heart valve repair |
US7241257B1 (en) | 2002-06-28 | 2007-07-10 | Abbott Cardiovascular Systems, Inc. | Devices and methods to perform minimally invasive surgeries |
IL150855A (en) | 2002-07-22 | 2007-06-03 | Leonid Monassevitch | Intratubular anastomosis apparatus |
US8758372B2 (en) | 2002-08-29 | 2014-06-24 | St. Jude Medical, Cardiology Division, Inc. | Implantable devices for controlling the size and shape of an anatomical structure or lumen |
US20040044364A1 (en) | 2002-08-29 | 2004-03-04 | Devries Robert | Tissue fasteners and related deployment systems and methods |
CO5500017A1 (en) | 2002-09-23 | 2005-03-31 | 3F Therapeutics Inc | MITRAL PROTESTIC VALVE |
CA2498030A1 (en) | 2002-10-01 | 2004-04-15 | Ample Medical, Inc. | Devices, systems, and methods for reshaping a heart valve annulus |
AU2003277115A1 (en) | 2002-10-01 | 2004-04-23 | Ample Medical, Inc. | Device and method for repairing a native heart valve leaflet |
US7087064B1 (en) | 2002-10-15 | 2006-08-08 | Advanced Cardiovascular Systems, Inc. | Apparatuses and methods for heart valve repair |
US8460371B2 (en) | 2002-10-21 | 2013-06-11 | Mitralign, Inc. | Method and apparatus for performing catheter-based annuloplasty using local plications |
US20050119735A1 (en) | 2002-10-21 | 2005-06-02 | Spence Paul A. | Tissue fastening systems and methods utilizing magnetic guidance |
US6733536B1 (en) | 2002-10-22 | 2004-05-11 | Scimed Life Systems | Male urethral stent device |
US8010207B2 (en) | 2002-10-31 | 2011-08-30 | Medtronic, Inc. | Implantable medical lead designs |
US7112219B2 (en) | 2002-11-12 | 2006-09-26 | Myocor, Inc. | Devices and methods for heart valve treatment |
US7247134B2 (en) | 2002-11-12 | 2007-07-24 | Myocor, Inc. | Devices and methods for heart valve treatment |
US7485143B2 (en) | 2002-11-15 | 2009-02-03 | Abbott Cardiovascular Systems Inc. | Apparatuses and methods for heart valve repair |
US7331972B1 (en) | 2002-11-15 | 2008-02-19 | Abbott Cardiovascular Systems Inc. | Heart valve chord cutter |
US7335213B1 (en) | 2002-11-15 | 2008-02-26 | Abbott Cardiovascular Systems Inc. | Apparatus and methods for heart valve repair |
US7404824B1 (en) | 2002-11-15 | 2008-07-29 | Advanced Cardiovascular Systems, Inc. | Valve aptation assist device |
AU2003290979A1 (en) | 2002-11-15 | 2004-06-15 | The Government Of The United States Of America As Represented By The Secretary Of Health And Human Services | Method and device for catheter-based repair of cardiac valves |
US7175625B2 (en) | 2002-11-25 | 2007-02-13 | Triage Medical | Soft tissue anchor and method of using same |
US7108710B2 (en) | 2002-11-26 | 2006-09-19 | Abbott Laboratories | Multi-element biased suture clip |
US7608114B2 (en) | 2002-12-02 | 2009-10-27 | Gi Dynamics, Inc. | Bariatric sleeve |
US7316710B1 (en) | 2002-12-30 | 2008-01-08 | Advanced Cardiovascular Systems, Inc. | Flexible stent |
US7160309B2 (en) | 2002-12-31 | 2007-01-09 | Laveille Kao Voss | Systems for anchoring a medical device in a body lumen |
EP1596723A2 (en) | 2003-02-04 | 2005-11-23 | ev3 Sunnyvale, Inc. | Patent foramen ovale closure system |
US20040254600A1 (en) | 2003-02-26 | 2004-12-16 | David Zarbatany | Methods and devices for endovascular mitral valve correction from the left coronary sinus |
US8157810B2 (en) | 2003-02-26 | 2012-04-17 | Cook Medical Technologies Llc | Prosthesis adapted for placement under external imaging |
US7381210B2 (en) | 2003-03-14 | 2008-06-03 | Edwards Lifesciences Corporation | Mitral valve repair system and method for use |
US20040186566A1 (en) | 2003-03-18 | 2004-09-23 | Hindrichs Paul J. | Body tissue remodeling methods and apparatus |
US7357818B2 (en) | 2003-03-26 | 2008-04-15 | Boston Scientific Scimed, Inc. | Self-retaining stent |
US20050107871A1 (en) | 2003-03-30 | 2005-05-19 | Fidel Realyvasquez | Apparatus and methods for valve repair |
US7530995B2 (en) | 2003-04-17 | 2009-05-12 | 3F Therapeutics, Inc. | Device for reduction of pressure effects of cardiac tricuspid valve regurgitation |
US7159593B2 (en) | 2003-04-17 | 2007-01-09 | 3F Therapeutics, Inc. | Methods for reduction of pressure effects of cardiac tricuspid valve regurgitation |
EP2926772A1 (en) | 2003-04-24 | 2015-10-07 | Cook Medical Technologies LLC | Artificial valve prosthesis with improved flow dynamics |
EP1615673B1 (en) | 2003-04-25 | 2012-10-31 | Tyco Healthcare Group LP | Surgical access apparatus |
US20040236372A1 (en) * | 2003-05-20 | 2004-11-25 | Anspach William E. | Suture clamp |
US8267981B2 (en) | 2003-06-10 | 2012-09-18 | Depuy Mitek, Inc. | Suture anchor with improved drive head |
US20070093869A1 (en) | 2003-06-20 | 2007-04-26 | Medtronic Vascular, Inc. | Device, system, and method for contracting tissue in a mammalian body |
EP1648346A4 (en) | 2003-06-20 | 2006-10-18 | Medtronic Vascular Inc | Valve annulus reduction system |
US7316706B2 (en) | 2003-06-20 | 2008-01-08 | Medtronic Vascular, Inc. | Tensioning device, system, and method for treating mitral valve regurgitation |
US7201772B2 (en) | 2003-07-08 | 2007-04-10 | Ventor Technologies, Ltd. | Fluid flow prosthetic device |
DE10333281A1 (en) | 2003-07-18 | 2005-02-03 | Zf Lenksysteme Gmbh | Method for controlling a switching device |
EP1646332B1 (en) | 2003-07-18 | 2015-06-17 | Edwards Lifesciences AG | Remotely activated mitral annuloplasty system |
US20050016560A1 (en) | 2003-07-21 | 2005-01-27 | Dee Voughlohn | Unique hair-styling system and method |
US8211087B2 (en) | 2003-07-31 | 2012-07-03 | Cook Medical Technologies Llc | Distal wire stop |
US8021421B2 (en) | 2003-08-22 | 2011-09-20 | Medtronic, Inc. | Prosthesis heart valve fixturing device |
US7371244B2 (en) | 2003-08-25 | 2008-05-13 | Ethicon, Inc. | Deployment apparatus for suture anchoring device |
JP2007505657A (en) | 2003-09-15 | 2007-03-15 | アボット・ラボラトリーズ | Suture lock device and method |
US20050065434A1 (en) | 2003-09-22 | 2005-03-24 | Bavaro Vincent P. | Polymeric marker with high radiopacity for use in medical devices |
US7462188B2 (en) | 2003-09-26 | 2008-12-09 | Abbott Laboratories | Device and method for suturing intracardiac defects |
US20050075729A1 (en) | 2003-10-06 | 2005-04-07 | Nguyen Tuoc Tan | Minimally invasive valve replacement system |
JP4358589B2 (en) | 2003-10-08 | 2009-11-04 | オリンパス株式会社 | Medical treatment tool |
US20050090827A1 (en) | 2003-10-28 | 2005-04-28 | Tewodros Gedebou | Comprehensive tissue attachment system |
US7056286B2 (en) | 2003-11-12 | 2006-06-06 | Adrian Ravenscroft | Medical device anchor and delivery system |
EP1689329A2 (en) | 2003-11-12 | 2006-08-16 | Medtronic Vascular, Inc. | Cardiac valve annulus reduction system |
US20050177228A1 (en) | 2003-12-16 | 2005-08-11 | Solem Jan O. | Device for changing the shape of the mitral annulus |
WO2005058206A1 (en) | 2003-12-16 | 2005-06-30 | Edwards Lifesciences Ag | Device for changing the shape of the mitral annulus |
US20050273138A1 (en) | 2003-12-19 | 2005-12-08 | Guided Delivery Systems, Inc. | Devices and methods for anchoring tissue |
US7258697B1 (en) | 2003-12-22 | 2007-08-21 | Advanced Cardiovascular Systems, Inc. | Stent with anchors to prevent vulnerable plaque rupture during deployment |
US7166127B2 (en) | 2003-12-23 | 2007-01-23 | Mitralign, Inc. | Tissue fastening systems and methods utilizing magnetic guidance |
US7824443B2 (en) | 2003-12-23 | 2010-11-02 | Sadra Medical, Inc. | Medical implant delivery and deployment tool |
US9005273B2 (en) | 2003-12-23 | 2015-04-14 | Sadra Medical, Inc. | Assessing the location and performance of replacement heart valves |
EP2526898B1 (en) | 2003-12-23 | 2013-04-17 | Sadra Medical, Inc. | Repositionable heart valve |
US7449024B2 (en) | 2003-12-23 | 2008-11-11 | Abbott Laboratories | Suturing device with split arm and method of suturing tissue |
US20050137686A1 (en) | 2003-12-23 | 2005-06-23 | Sadra Medical, A Delaware Corporation | Externally expandable heart valve anchor and method |
US7329279B2 (en) | 2003-12-23 | 2008-02-12 | Sadra Medical, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US8840663B2 (en) | 2003-12-23 | 2014-09-23 | Sadra Medical, Inc. | Repositionable heart valve method |
US8864822B2 (en) | 2003-12-23 | 2014-10-21 | Mitralign, Inc. | Devices and methods for introducing elements into tissue |
US7390332B2 (en) | 2004-02-24 | 2008-06-24 | Depuy Mitek, Inc. | Methods and devices for repairing tissue |
WO2005081991A2 (en) | 2004-02-25 | 2005-09-09 | Cardio-Optics, Inc. | Coronary sinus locator sheath for biventricular pacing |
SE0400546D0 (en) | 2004-03-05 | 2004-03-05 | Dan Lundgren | Tubular bone anchoring element |
US20050203606A1 (en) | 2004-03-09 | 2005-09-15 | Vancamp Daniel H. | Stent system for preventing restenosis |
EP3308744B2 (en) | 2004-03-11 | 2023-08-02 | Percutaneous Cardiovascular Solutions Pty Limited | Percutaneous heart valve prosthesis |
NL1025830C2 (en) | 2004-03-26 | 2005-02-22 | Eric Berreklouw | Prosthesis e.g. heart valve secured in place by ring with shape memory material anchor, includes anchor temperature control system |
US20050228388A1 (en) | 2004-03-30 | 2005-10-13 | Darrel Brodke | Double lead bone screw |
WO2005099374A2 (en) | 2004-04-05 | 2005-10-27 | Genesee Biomedical, Inc. | Method and apparatus for the surgical treatment of congestive heart failure |
US7993397B2 (en) | 2004-04-05 | 2011-08-09 | Edwards Lifesciences Ag | Remotely adjustable coronary sinus implant |
US7374573B2 (en) | 2004-05-03 | 2008-05-20 | Shlomo Gabbay | System and method for improving ventricular function |
CA2563426C (en) | 2004-05-05 | 2013-12-24 | Direct Flow Medical, Inc. | Unstented heart valve with formed in place support structure |
US8057511B2 (en) * | 2004-05-07 | 2011-11-15 | Usgi Medical, Inc. | Apparatus and methods for positioning and securing anchors |
US7390329B2 (en) | 2004-05-07 | 2008-06-24 | Usgi Medical, Inc. | Methods for grasping and cinching tissue anchors |
EP1750595A4 (en) | 2004-05-07 | 2008-10-22 | Valentx Inc | Devices and methods for attaching an endolumenal gastrointestinal implant |
US20050251208A1 (en) | 2004-05-07 | 2005-11-10 | Usgi Medical Inc. | Linear anchors for anchoring to tissue |
US20060122692A1 (en) | 2004-05-10 | 2006-06-08 | Ran Gilad | Stent valve and method of using same |
US7276078B2 (en) | 2004-06-30 | 2007-10-02 | Edwards Lifesciences Pvt | Paravalvular leak detection, sealing, and prevention |
CA2580053C (en) | 2004-09-14 | 2014-07-08 | Edwards Lifesciences Ag. | Device and method for treatment of heart valve regurgitation |
US20090118776A1 (en) | 2004-09-24 | 2009-05-07 | Biomec, Inc. | Tissue anchors |
US8052592B2 (en) | 2005-09-27 | 2011-11-08 | Evalve, Inc. | Methods and devices for tissue grasping and assessment |
WO2006037131A2 (en) | 2004-09-28 | 2006-04-06 | Surgical Solutions Llc | Suture anchor |
US20070083168A1 (en) | 2004-09-30 | 2007-04-12 | Whiting James S | Transmembrane access systems and methods |
US20060079736A1 (en) | 2004-10-13 | 2006-04-13 | Sing-Fatt Chin | Method and device for percutaneous left ventricular reconstruction |
US7749250B2 (en) | 2006-02-03 | 2010-07-06 | Biomet Sports Medicine, Llc | Soft tissue repair assembly and associated method |
US7857830B2 (en) | 2006-02-03 | 2010-12-28 | Biomet Sports Medicine, Llc | Soft tissue repair and conduit device |
US7720550B2 (en) | 2004-12-03 | 2010-05-18 | Medtronic, Inc. | High impedance active fixation electrode of an electrical medical lead |
US7211110B2 (en) | 2004-12-09 | 2007-05-01 | Edwards Lifesciences Corporation | Diagnostic kit to assist with heart valve annulus adjustment |
WO2009053952A2 (en) | 2007-10-26 | 2009-04-30 | Mednua Limited | A medical device for use in treatment of a valve |
US20060178700A1 (en) | 2004-12-15 | 2006-08-10 | Martin Quinn | Medical device suitable for use in treatment of a valve |
ATE435616T1 (en) | 2004-12-15 | 2009-07-15 | Cook Urological Inc | X-RAY OPERASIVE MANIPULATION DEVICES |
US7930016B1 (en) | 2005-02-02 | 2011-04-19 | Voyage Medical, Inc. | Tissue closure system |
CA2597066C (en) | 2005-02-07 | 2014-04-15 | Evalve, Inc. | Methods, systems and devices for cardiac valve repair |
WO2011034973A2 (en) | 2005-02-07 | 2011-03-24 | Abbott Vascular | Methods, systems and devices for cardiac valve repair |
DE602006013946D1 (en) | 2005-02-08 | 2010-06-10 | Koninkl Philips Electronics Nv | SYSTEM FOR PERCUTANEOUS GLOSSOPLASTICS |
US9089323B2 (en) | 2005-02-22 | 2015-07-28 | P Tech, Llc | Device and method for securing body tissue |
JP2006255162A (en) | 2005-03-17 | 2006-09-28 | Olympus Corp | Medical suture ligation unit |
US8608797B2 (en) | 2005-03-17 | 2013-12-17 | Valtech Cardio Ltd. | Mitral valve treatment techniques |
WO2007080595A2 (en) | 2006-01-12 | 2007-07-19 | Metacure N.V. | Electrode assemblies, tools, and methods for gastric wall implantation |
WO2006105084A2 (en) | 2005-03-25 | 2006-10-05 | Mitralsolutions, Inc. | Methods and apparatus for controlling the internal circumference of an anatomic orifice or lumen |
US8864823B2 (en) | 2005-03-25 | 2014-10-21 | StJude Medical, Cardiology Division, Inc. | Methods and apparatus for controlling the internal circumference of an anatomic orifice or lumen |
AU2006230086A1 (en) | 2005-03-25 | 2006-10-05 | Ample Medical, Inc. | Device, systems, and methods for reshaping a heart valve annulus |
US7947207B2 (en) | 2005-04-12 | 2011-05-24 | Abbott Cardiovascular Systems Inc. | Method for retaining a vascular stent on a catheter |
EP1893131A1 (en) | 2005-04-20 | 2008-03-05 | The Cleveland Clinic Foundation | Apparatus and method for replacing a cardiac valve |
SE531468C2 (en) | 2005-04-21 | 2009-04-14 | Edwards Lifesciences Ag | An apparatus for controlling blood flow |
US8333777B2 (en) | 2005-04-22 | 2012-12-18 | Benvenue Medical, Inc. | Catheter-based tissue remodeling devices and methods |
US7645286B2 (en) | 2005-05-20 | 2010-01-12 | Neotract, Inc. | Devices, systems and methods for retracting, lifting, compressing, supporting or repositioning tissues or anatomical structures |
US7758594B2 (en) | 2005-05-20 | 2010-07-20 | Neotract, Inc. | Devices, systems and methods for treating benign prostatic hyperplasia and other conditions |
JP2008541952A (en) | 2005-06-02 | 2008-11-27 | コーディス・コーポレイション | Device for closing the patent foramen ovale |
US7500989B2 (en) | 2005-06-03 | 2009-03-10 | Edwards Lifesciences Corp. | Devices and methods for percutaneous repair of the mitral valve via the coronary sinus |
US7766816B2 (en) | 2005-06-09 | 2010-08-03 | Chf Technologies, Inc. | Method and apparatus for closing off a portion of a heart ventricle |
EP2510883B1 (en) | 2005-06-20 | 2018-04-11 | Nobles Medical Technologies, Inc. | Apparatus for applying a knot to a suture |
US8685083B2 (en) | 2005-06-27 | 2014-04-01 | Edwards Lifesciences Corporation | Apparatus, system, and method for treatment of posterior leaflet prolapse |
US8252005B2 (en) | 2005-06-30 | 2012-08-28 | Edwards Lifesciences Corporation | System, apparatus, and method for fastening tissue |
US8313497B2 (en) | 2005-07-01 | 2012-11-20 | Abbott Laboratories | Clip applier and methods of use |
US8951285B2 (en) | 2005-07-05 | 2015-02-10 | Mitralign, Inc. | Tissue anchor, anchoring system and methods of using the same |
ES2375738T3 (en) | 2005-07-07 | 2012-03-05 | Cordis Corporation | CLOSURE DEVICE OF AN OVAL HOLE PERSISTENCE WITH AN ORIENTABLE ADMINISTRATION SYSTEM. |
EP1919397B1 (en) | 2005-07-13 | 2013-01-02 | Medtronic, Inc. | Two-piece percutaneous prosthetic heart valves |
DE102006017873A1 (en) | 2005-07-14 | 2007-01-25 | Qualimed Innovative Medizinprodukte Gmbh | Temporary stent |
ATE442108T1 (en) | 2005-07-15 | 2009-09-15 | Cleveland Clinic Foundation | DEVICE FOR REMODELING A HEART VALVE RING |
US7875056B2 (en) | 2005-07-22 | 2011-01-25 | Anpa Medical, Inc. | Wedge operated retainer device and methods |
US7883517B2 (en) | 2005-08-08 | 2011-02-08 | Abbott Laboratories | Vascular suturing device |
WO2007022519A2 (en) | 2005-08-19 | 2007-02-22 | Chf Technologies, Inc. | Steerable heart implants for congestive heart failure |
US9492277B2 (en) | 2005-08-30 | 2016-11-15 | Mayo Foundation For Medical Education And Research | Soft body tissue remodeling methods and apparatus |
US20070078297A1 (en) | 2005-08-31 | 2007-04-05 | Medtronic Vascular, Inc. | Device for Treating Mitral Valve Regurgitation |
US7846179B2 (en) | 2005-09-01 | 2010-12-07 | Ovalis, Inc. | Suture-based systems and methods for treating septal defects |
US8968379B2 (en) | 2005-09-02 | 2015-03-03 | Medtronic Vascular, Inc. | Stent delivery system with multiple evenly spaced pullwires |
EP1928540A4 (en) | 2005-09-07 | 2010-03-10 | The Foundry Inc | Apparatus and method for disrupting subcutaneous structures |
CA2660892A1 (en) | 2005-09-09 | 2007-03-15 | Edwards Lifesciences Corporation | Device and method for reshaping mitral valve annulus |
US20070073391A1 (en) | 2005-09-28 | 2007-03-29 | Henry Bourang | System and method for delivering a mitral valve repair device |
US8778017B2 (en) | 2005-10-26 | 2014-07-15 | Cardiosolutions, Inc. | Safety for mitral valve implant |
US8852270B2 (en) | 2007-11-15 | 2014-10-07 | Cardiosolutions, Inc. | Implant delivery system and method |
US9259317B2 (en) | 2008-06-13 | 2016-02-16 | Cardiosolutions, Inc. | System and method for implanting a heart implant |
US7785366B2 (en) | 2005-10-26 | 2010-08-31 | Maurer Christopher W | Mitral spacer |
US8449606B2 (en) | 2005-10-26 | 2013-05-28 | Cardiosolutions, Inc. | Balloon mitral spacer |
US8092525B2 (en) | 2005-10-26 | 2012-01-10 | Cardiosolutions, Inc. | Heart valve implant |
US8216302B2 (en) | 2005-10-26 | 2012-07-10 | Cardiosolutions, Inc. | Implant delivery and deployment system and method |
US8343204B2 (en) | 2005-10-31 | 2013-01-01 | Cook Medical Technologies Llc | Composite stent graft |
EP1951352B1 (en) | 2005-11-10 | 2017-01-11 | Edwards Lifesciences CardiAQ LLC | Balloon-expandable, self-expanding, vascular prosthesis connecting stent |
WO2007062054A2 (en) | 2005-11-21 | 2007-05-31 | The Brigham And Women's Hospital, Inc. | Percutaneous cardiac valve repair with adjustable artificial chordae |
FR2894131B1 (en) | 2005-12-02 | 2008-12-05 | Perouse Soc Par Actions Simpli | DEVICE FOR TREATING A BLOOD VESSEL, AND ASSOCIATED TREATMENT NECESSARY. |
WO2007078772A1 (en) | 2005-12-15 | 2007-07-12 | The Cleveland Clinic Foundation | Apparatus and method for treating a regurgitant valve |
EP1959866B1 (en) | 2005-12-15 | 2019-03-06 | Georgia Tech Research Corporation | Papillary muscle position control devices and systems |
US20100030329A1 (en) | 2005-12-19 | 2010-02-04 | Robert William Mayo Frater | Annuloplasty Prosthesis |
ATE472985T1 (en) | 2005-12-22 | 2010-07-15 | Symetis Sa | STENT VALVE AS VALVE REPLACEMENT AND RELEVANT PROCEDURES AND OPERATIONAL SYSTEMS |
US20070168013A1 (en) | 2006-01-19 | 2007-07-19 | Myles Douglas | Vascular graft and deployment system |
US7628797B2 (en) | 2006-01-31 | 2009-12-08 | Edwards Lifesciences Corporation | System, apparatus, and method for fastening tissue |
US7967820B2 (en) | 2006-02-07 | 2011-06-28 | P Tech, Llc. | Methods and devices for trauma welding |
US7637946B2 (en) | 2006-02-09 | 2009-12-29 | Edwards Lifesciences Corporation | Coiled implant for mitral valve repair |
US20070203391A1 (en) | 2006-02-24 | 2007-08-30 | Medtronic Vascular, Inc. | System for Treating Mitral Valve Regurgitation |
US7431692B2 (en) | 2006-03-09 | 2008-10-07 | Edwards Lifesciences Corporation | Apparatus, system, and method for applying and adjusting a tensioning element to a hollow body organ |
US20070219558A1 (en) | 2006-03-15 | 2007-09-20 | Allen Deutsch | Method and apparatus for arthroscopic surgery using suture anchors |
US7815652B2 (en) | 2006-03-21 | 2010-10-19 | Ethicon Endo-Surgery, Inc. | Surgical fastener and instrument |
WO2007115110A2 (en) | 2006-03-29 | 2007-10-11 | The Catheter Exchange, Inc. | Method and device for cavity obliteration |
CN101415369B (en) | 2006-03-31 | 2013-01-02 | 新加坡南洋理工大学 | Tissue retractor, tissue retractor kit and method of use thereof |
CN101049267B (en) | 2006-04-03 | 2010-12-22 | 孟坚 | Medical use obstruction appliance |
US7442207B2 (en) | 2006-04-21 | 2008-10-28 | Medtronic Vascular, Inc. | Device, system, and method for treating cardiac valve regurgitation |
JP2009535128A (en) | 2006-04-29 | 2009-10-01 | アーバー・サージカル・テクノロジーズ・インコーポレイテッド | Multi-part prosthetic heart valve assembly and apparatus and method for delivering the same |
WO2007136532A2 (en) | 2006-05-03 | 2007-11-29 | St. Jude Medical, Inc. | Soft body tissue remodeling methods and apparatus |
US20070265658A1 (en) | 2006-05-12 | 2007-11-15 | Aga Medical Corporation | Anchoring and tethering system |
JP5258754B2 (en) | 2006-05-15 | 2013-08-07 | エドワーズ・ライフサイエンシス・アーゲー | System and method for altering heart geometry |
US8932348B2 (en) | 2006-05-18 | 2015-01-13 | Edwards Lifesciences Corporation | Device and method for improving heart valve function |
US8105355B2 (en) | 2006-05-18 | 2012-01-31 | C.R. Bard, Inc. | Suture lock fastening device |
EP2032044A2 (en) | 2006-05-25 | 2009-03-11 | Mitralign, Inc. | Lockers for surgical tensioning members and methods of using the same to secure surgical tensioning members |
US7811316B2 (en) | 2006-05-25 | 2010-10-12 | Deep Vein Medical, Inc. | Device for regulating blood flow |
US20070282429A1 (en) | 2006-06-01 | 2007-12-06 | Hauser David L | Prosthetic insert for improving heart valve function |
US7934506B2 (en) | 2006-06-21 | 2011-05-03 | Koninklijke Philips Electronics N.V. | System and method for temporary tongue suspension |
US20100069849A1 (en) | 2006-06-30 | 2010-03-18 | Kassab Ghassan S | Percutaneous intravascular access to cardiac tissue |
US20080077231A1 (en) | 2006-07-06 | 2008-03-27 | Prescient Medical, Inc. | Expandable vascular endoluminal prostheses |
WO2008016578A2 (en) | 2006-07-31 | 2008-02-07 | Cartledge Richard G | Sealable endovascular implants and methods for their use |
US9408607B2 (en) | 2009-07-02 | 2016-08-09 | Edwards Lifesciences Cardiaq Llc | Surgical implant devices and methods for their manufacture and use |
US20080097595A1 (en) | 2006-08-22 | 2008-04-24 | Shlomo Gabbay | Intraventricular cardiac prosthesis |
US20080065156A1 (en) | 2006-09-08 | 2008-03-13 | Hauser David L | Expandable clip for tissue repair |
US9211115B2 (en) | 2006-09-28 | 2015-12-15 | Bioventrix, Inc. | Location, time, and/or pressure determining devices, systems, and methods for deployment of lesion-excluding heart implants for treatment of cardiac heart failure and other disease states |
US7771467B2 (en) | 2006-11-03 | 2010-08-10 | The Cleveland Clinic Foundation | Apparatus for repairing the function of a native aortic valve |
US20080125400A1 (en) | 2006-11-27 | 2008-05-29 | Christopher Speirs | Use of phosphoenolpyruvate derivatives |
EP2088965B1 (en) | 2006-12-05 | 2012-11-28 | Valtech Cardio, Ltd. | Segmented ring placement |
US8236045B2 (en) | 2006-12-22 | 2012-08-07 | Edwards Lifesciences Corporation | Implantable prosthetic valve assembly and method of making the same |
US20100121433A1 (en) | 2007-01-08 | 2010-05-13 | Millipede Llc, A Corporation Of Michigan | Reconfiguring heart features |
US20100249920A1 (en) | 2007-01-08 | 2010-09-30 | Millipede Llc | Reconfiguring heart features |
US9192471B2 (en) | 2007-01-08 | 2015-11-24 | Millipede, Inc. | Device for translumenal reshaping of a mitral valve annulus |
WO2008097589A1 (en) | 2007-02-05 | 2008-08-14 | Boston Scientific Limited | Percutaneous valve, system, and method |
US20080195126A1 (en) | 2007-02-14 | 2008-08-14 | Jan Otto Solem | Suture and method for repairing a heart |
US7780702B2 (en) * | 2007-02-27 | 2010-08-24 | Olympus Medical Systems Corp. | Suture tool |
EP2120753B1 (en) | 2007-03-05 | 2022-09-28 | Tornier, Inc. | Tack anchor systems |
US8911461B2 (en) | 2007-03-13 | 2014-12-16 | Mitralign, Inc. | Suture cutter and method of cutting suture |
US20080228265A1 (en) | 2007-03-13 | 2008-09-18 | Mitralign, Inc. | Tissue anchors, systems and methods, and devices |
US8753373B2 (en) | 2007-05-08 | 2014-06-17 | Edwards Lifesciences Corporation | Suture-fastening clip |
US8480730B2 (en) | 2007-05-14 | 2013-07-09 | Cardiosolutions, Inc. | Solid construct mitral spacer |
US7991484B1 (en) | 2007-05-15 | 2011-08-02 | Pacesetter, Inc. | Active fixation medical lead and related method and system |
US8740937B2 (en) | 2007-05-31 | 2014-06-03 | Cook Medical Technologies Llc | Suture lock |
EP2157916A2 (en) | 2007-06-04 | 2010-03-03 | Mor Research Applications Ltd. | Cardiac valve leaflet augmentation |
US9814611B2 (en) | 2007-07-31 | 2017-11-14 | Edwards Lifesciences Cardiaq Llc | Actively controllable stent, stent graft, heart valve and method of controlling same |
US8100820B2 (en) | 2007-08-22 | 2012-01-24 | Edwards Lifesciences Corporation | Implantable device for treatment of ventricular dilation |
DE102007043830A1 (en) | 2007-09-13 | 2009-04-02 | Lozonschi, Lucian, Madison | Heart valve stent |
WO2009039400A1 (en) | 2007-09-20 | 2009-03-26 | Nanostim, Inc. | Leadless cardiac pacemaker with secondary fixation capability |
US20090082847A1 (en) | 2007-09-26 | 2009-03-26 | Boston Scientific Corporation | System and method of securing stent barbs |
US8454686B2 (en) | 2007-09-28 | 2013-06-04 | St. Jude Medical, Inc. | Two-stage collapsible/expandable prosthetic heart valves and anchoring systems |
US8784481B2 (en) | 2007-09-28 | 2014-07-22 | St. Jude Medical, Inc. | Collapsible/expandable prosthetic heart valves with native calcified leaflet retention features |
US20090084386A1 (en) | 2007-10-01 | 2009-04-02 | Mcclellan Annette M L | Tubal ligation |
JP2010540190A (en) | 2007-10-04 | 2010-12-24 | トリバスキュラー・インコーポレイテッド | Modular vascular graft for low profile transdermal delivery |
EP2211779B1 (en) | 2007-10-15 | 2014-08-20 | Edwards Lifesciences Corporation | Transcatheter heart valve with micro-anchors |
US8236013B2 (en) | 2007-10-19 | 2012-08-07 | Boston Scientific Scimed, Inc. | Apparatus for placing medical implants |
US8821366B2 (en) | 2007-10-24 | 2014-09-02 | Circulite, Inc. | Transseptal cannula, tip, delivery system, and method |
US8597347B2 (en) | 2007-11-15 | 2013-12-03 | Cardiosolutions, Inc. | Heart regurgitation method and apparatus |
WO2009072114A2 (en) | 2007-12-02 | 2009-06-11 | Mor Research Applications Ltd. | Access to the left atrium and reduction of mitral valve leaflet mobility |
US8893947B2 (en) | 2007-12-17 | 2014-11-25 | Abbott Laboratories | Clip applier and methods of use |
US7841502B2 (en) | 2007-12-18 | 2010-11-30 | Abbott Laboratories | Modular clip applier |
US9131928B2 (en) | 2007-12-20 | 2015-09-15 | Mor Research Applications Ltd. | Elongated body for deployment in a heart |
EP2244661B1 (en) | 2008-02-11 | 2012-03-28 | Corassist Cardiovascular Ltd. | Ventricular function assisting devices |
US8728097B1 (en) | 2008-02-26 | 2014-05-20 | Mitralign, Inc. | Tissue plication devices and methods for their use |
US9131939B1 (en) | 2008-02-27 | 2015-09-15 | Mitralign, Inc. | Device for percutaneously delivering a cardiac implant through the application of direct actuation forces external to the body |
CA3063001A1 (en) | 2008-02-29 | 2009-09-03 | Edwards Lifesciences Corporation | Expandable member for deploying a prosthetic device |
DE102008012113A1 (en) | 2008-03-02 | 2009-09-03 | Transcatheter Technologies Gmbh | Implant e.g. heart-valve-carrying stent, for e.g. arresting blood vessel, has fiber by which section of implant is reducible according to increasing of implant at extended diameter by unfolding or expansion of diameter with expansion unit |
US8382829B1 (en) | 2008-03-10 | 2013-02-26 | Mitralign, Inc. | Method to reduce mitral regurgitation by cinching the commissure of the mitral valve |
US8262725B2 (en) | 2008-04-16 | 2012-09-11 | Cardiovascular Technologies, Llc | Transvalvular intraannular band for valve repair |
US20100121435A1 (en) | 2008-04-16 | 2010-05-13 | Cardiovascular Technologies, Llc | Percutaneous transvalvular intrannular band for mitral valve repair |
FR2930137B1 (en) | 2008-04-18 | 2010-04-23 | Corevalve Inc | TREATMENT EQUIPMENT FOR A CARDIAC VALVE, IN PARTICULAR A MITRAL VALVE. |
US20090276040A1 (en) | 2008-05-01 | 2009-11-05 | Edwards Lifesciences Corporation | Device and method for replacing mitral valve |
US8152844B2 (en) | 2008-05-09 | 2012-04-10 | Edwards Lifesciences Corporation | Quick-release annuloplasty ring holder |
WO2009140298A2 (en) | 2008-05-12 | 2009-11-19 | Wright John T M | Device and method for the surgical treatment of ischemic mitral regurgitation |
US20090287304A1 (en) | 2008-05-13 | 2009-11-19 | Kardium Inc. | Medical Device for Constricting Tissue or a Bodily Orifice, for example a mitral valve |
US9282965B2 (en) | 2008-05-16 | 2016-03-15 | Abbott Laboratories | Apparatus and methods for engaging tissue |
US20100049293A1 (en) | 2008-06-04 | 2010-02-25 | Zukowski Stanislaw L | Controlled deployable medical device and method of making the same |
US8591460B2 (en) | 2008-06-13 | 2013-11-26 | Cardiosolutions, Inc. | Steerable catheter and dilator and system and method for implanting a heart implant |
EP2296744B1 (en) | 2008-06-16 | 2019-07-31 | Valtech Cardio, Ltd. | Annuloplasty devices |
US8323335B2 (en) | 2008-06-20 | 2012-12-04 | Edwards Lifesciences Corporation | Retaining mechanisms for prosthetic valves and methods for using |
ES2851152T3 (en) | 2008-07-21 | 2021-09-03 | Jenesis Surgical Llc | Endoluminal support device and method for its manufacture |
US20100023118A1 (en) | 2008-07-24 | 2010-01-28 | Edwards Lifesciences Corporation | Method and apparatus for repairing or replacing chordae tendinae |
US7776743B2 (en) | 2008-07-30 | 2010-08-17 | Tel Epion Inc. | Method of forming semiconductor devices containing metal cap layers |
US8777990B2 (en) | 2008-09-08 | 2014-07-15 | Howmedica Osteonics Corp. | Knotless suture anchor for soft tissue repair and method of use |
US8945211B2 (en) | 2008-09-12 | 2015-02-03 | Mitralign, Inc. | Tissue plication device and method for its use |
EP2617388B2 (en) | 2008-10-10 | 2019-11-06 | Boston Scientific Scimed, Inc. | Medical devices and delivery systems for delivering medical devices |
JP2012505048A (en) | 2008-10-10 | 2012-03-01 | ガイデッド デリバリー システムズ, インコーポレイテッド | Termination device and related methods |
US8126642B2 (en) | 2008-10-24 | 2012-02-28 | Gray & Company, Inc. | Control and systems for autonomously driven vehicles |
WO2010071494A1 (en) | 2008-12-19 | 2010-06-24 | St.Jude Medical Ab | A medical implantable lead and a method for ensuring proper and safe attachment of such a lead to an organ |
US8858594B2 (en) | 2008-12-22 | 2014-10-14 | Abbott Laboratories | Curved closure device |
US8911494B2 (en) | 2009-05-04 | 2014-12-16 | Valtech Cardio, Ltd. | Deployment techniques for annuloplasty ring |
US8808368B2 (en) | 2008-12-22 | 2014-08-19 | Valtech Cardio, Ltd. | Implantation of repair chords in the heart |
US8147542B2 (en) | 2008-12-22 | 2012-04-03 | Valtech Cardio, Ltd. | Adjustable repair chords and spool mechanism therefor |
US8323312B2 (en) | 2008-12-22 | 2012-12-04 | Abbott Laboratories | Closure device |
US8715342B2 (en) | 2009-05-07 | 2014-05-06 | Valtech Cardio, Ltd. | Annuloplasty ring with intra-ring anchoring |
US8241351B2 (en) | 2008-12-22 | 2012-08-14 | Valtech Cardio, Ltd. | Adjustable partial annuloplasty ring and mechanism therefor |
ES2873182T3 (en) | 2008-12-22 | 2021-11-03 | Valtech Cardio Ltd | Adjustable annuloplasty devices |
US20110011917A1 (en) | 2008-12-31 | 2011-01-20 | Hansen Medical, Inc. | Methods, devices, and kits for treating valve prolapse |
US20100185278A1 (en) | 2009-01-21 | 2010-07-22 | Tendyne Medical | Apical Papillary Msucle Attachment for Left Ventricular Reduction |
US8108054B2 (en) | 2009-02-04 | 2012-01-31 | Pacesetter, Inc. | Active fixation implantable medical lead configured to indicate via fluoroscopy embedment of helical anchor in cardiac tissue |
US8353956B2 (en) | 2009-02-17 | 2013-01-15 | Valtech Cardio, Ltd. | Actively-engageable movement-restriction mechanism for use with an annuloplasty structure |
US20100217309A1 (en) | 2009-02-20 | 2010-08-26 | Boston Scientific Scimed, Inc. | Plug for arteriotomy closure and method of use |
US20100217382A1 (en) | 2009-02-25 | 2010-08-26 | Edwards Lifesciences | Mitral valve replacement with atrial anchoring |
BRPI1008902A2 (en) | 2009-02-27 | 2016-03-15 | St Jude Medical | prosthetic heart valve. |
WO2010099437A1 (en) | 2009-02-27 | 2010-09-02 | Silk Road Medical, Inc. | Vessel closure clip device |
US9980818B2 (en) | 2009-03-31 | 2018-05-29 | Edwards Lifesciences Corporation | Prosthetic heart valve system with positioning markers |
US9642662B2 (en) | 2009-04-02 | 2017-05-09 | DePuy Synthes Products, Inc. | Locking spiral anchoring system |
WO2010115072A1 (en) * | 2009-04-03 | 2010-10-07 | Wilson-Cook Medical, Inc. | Tissue anchors and medical devices for rapid deployment of tissue anchors |
EP2419050B2 (en) | 2009-04-15 | 2023-10-18 | Edwards Lifesciences CardiAQ LLC | Vascular implant and delivery system |
US20100286628A1 (en) | 2009-05-07 | 2010-11-11 | Rainbow Medical Ltd | Gastric anchor |
US8523881B2 (en) | 2010-07-26 | 2013-09-03 | Valtech Cardio, Ltd. | Multiple anchor delivery tool |
US20110238112A1 (en) | 2009-05-29 | 2011-09-29 | Kim Andrew C | Suture anchor |
US20110077733A1 (en) | 2009-09-25 | 2011-03-31 | Edwards Lifesciences Corporation | Leaflet contacting apparatus and method |
US20110082538A1 (en) | 2009-10-01 | 2011-04-07 | Jonathan Dahlgren | Medical device, kit and method for constricting tissue or a bodily orifice, for example, a mitral valve |
EP2485689B1 (en) | 2009-10-09 | 2020-03-18 | Boston Scientific Scimed, Inc. | Stomach bypass |
US20110093002A1 (en) | 2009-10-20 | 2011-04-21 | Wilson-Cook Medical Inc. | Stent-within-stent arrangements |
US9011520B2 (en) | 2009-10-29 | 2015-04-21 | Valtech Cardio, Ltd. | Tissue anchor for annuloplasty device |
US8690939B2 (en) | 2009-10-29 | 2014-04-08 | Valtech Cardio, Ltd. | Method for guide-wire based advancement of a rotation assembly |
US9180007B2 (en) | 2009-10-29 | 2015-11-10 | Valtech Cardio, Ltd. | Apparatus and method for guide-wire based advancement of an adjustable implant |
US8277502B2 (en) | 2009-10-29 | 2012-10-02 | Valtech Cardio, Ltd. | Tissue anchor for annuloplasty device |
US8812134B2 (en) | 2009-11-12 | 2014-08-19 | Cardiac Pacemakers Inc. | Helix fixation mechanism |
US8903514B2 (en) | 2009-11-30 | 2014-12-02 | St. Jude Medical Ab | Medical implantable lead with fixation detection |
US8449599B2 (en) | 2009-12-04 | 2013-05-28 | Edwards Lifesciences Corporation | Prosthetic valve for replacing mitral valve |
WO2011072084A2 (en) | 2009-12-08 | 2011-06-16 | Avalon Medical Ltd. | Device and system for transcatheter mitral valve replacement |
US8870950B2 (en) | 2009-12-08 | 2014-10-28 | Mitral Tech Ltd. | Rotation-based anchoring of an implant |
US8961596B2 (en) | 2010-01-22 | 2015-02-24 | 4Tech Inc. | Method and apparatus for tricuspid valve repair using tension |
US8475525B2 (en) | 2010-01-22 | 2013-07-02 | 4Tech Inc. | Tricuspid valve repair using tension |
US9307980B2 (en) | 2010-01-22 | 2016-04-12 | 4Tech Inc. | Tricuspid valve repair using tension |
US9107749B2 (en) | 2010-02-03 | 2015-08-18 | Edwards Lifesciences Corporation | Methods for treating a heart |
DE102010008360A1 (en) | 2010-02-17 | 2011-09-29 | Transcatheter Technologies Gmbh | Medical implant in which gaps remain during crimping or folding, method and device for moving |
US9226826B2 (en) | 2010-02-24 | 2016-01-05 | Medtronic, Inc. | Transcatheter valve structure and methods for valve delivery |
WO2011111047A2 (en) | 2010-03-10 | 2011-09-15 | Mitraltech Ltd. | Prosthetic mitral valve with tissue anchors |
ES2365317B1 (en) | 2010-03-19 | 2012-08-03 | Xavier Ruyra Baliarda | PROTESTIC BAND, IN PARTICULAR FOR THE REPAIR OF A MITRAL VALVE. |
US8398680B2 (en) | 2010-04-07 | 2013-03-19 | Lsi Solutions, Inc. | Bioabsorbable magnesium knots for securing surgical suture |
US8524132B2 (en) | 2010-04-14 | 2013-09-03 | Abbott Cardiovascular Systems Inc. | Method of fabricating an intraluminal scaffold with an enlarged portion |
US9795482B2 (en) | 2010-04-27 | 2017-10-24 | Medtronic, Inc. | Prosthetic heart valve devices and methods of valve repair |
CN103124537B (en) | 2010-05-10 | 2015-08-26 | 心叶科技公司 | Without rack supporting structure |
US8790394B2 (en) * | 2010-05-24 | 2014-07-29 | Valtech Cardio, Ltd. | Adjustable artificial chordeae tendineae with suture loops |
US20130030522A1 (en) | 2010-06-16 | 2013-01-31 | Rowe Stanton J | Devices and methods for heart treatments |
JP5096622B2 (en) | 2010-06-22 | 2012-12-12 | オリンパスメディカルシステムズ株式会社 | Manufacturing method of tissue fastener |
WO2012012209A2 (en) | 2010-07-19 | 2012-01-26 | Sukhjit Gill | Guiding catheter stabilization system |
US9132009B2 (en) | 2010-07-21 | 2015-09-15 | Mitraltech Ltd. | Guide wires with commissural anchors to advance a prosthetic valve |
US8992604B2 (en) | 2010-07-21 | 2015-03-31 | Mitraltech Ltd. | Techniques for percutaneous mitral valve replacement and sealing |
EP4098227A1 (en) | 2010-07-23 | 2022-12-07 | Edwards Lifesciences Corporation | Retaining mechanisms for prosthetic valves |
US8518107B2 (en) | 2010-08-04 | 2013-08-27 | Valcare, Inc. | Percutaneous transcatheter repair of heart valves |
US20120053680A1 (en) | 2010-08-24 | 2012-03-01 | Bolling Steven F | Reconfiguring Heart Features |
US8940002B2 (en) | 2010-09-30 | 2015-01-27 | Kardium Inc. | Tissue anchor system |
US8568475B2 (en) | 2010-10-05 | 2013-10-29 | Edwards Lifesciences Corporation | Spiraled commissure attachment for prosthetic valve |
US8968335B2 (en) | 2010-10-27 | 2015-03-03 | Mitralign, Inc. | Hand operated device for controlled deployment of a tissue anchor and method of using the same |
US8758402B2 (en) | 2010-12-17 | 2014-06-24 | Boston Scientific Scimed, Inc. | Tissue puncture closure device |
US20120158021A1 (en) | 2010-12-19 | 2012-06-21 | Mitralign, Inc. | Steerable guide catheter having preformed curved shape |
EP2478868A1 (en) | 2011-01-25 | 2012-07-25 | The Provost, Fellows, Foundation Scholars, and the other Members of Board, of the College of the Holy and Undivided Trinity of Queen Elizabeth | Implant device |
US9445898B2 (en) | 2011-03-01 | 2016-09-20 | Medtronic Ventor Technologies Ltd. | Mitral valve repair |
EP4119095A1 (en) | 2011-03-21 | 2023-01-18 | Cephea Valve Technologies, Inc. | Disk-based valve apparatus |
US9072511B2 (en) | 2011-03-25 | 2015-07-07 | Kardium Inc. | Medical kit for constricting tissue or a bodily orifice, for example, a mitral valve |
WO2012158186A1 (en) | 2011-05-17 | 2012-11-22 | Boston Scientific Scimed, Inc. | Percutaneous mitral annulus mini-plication |
US8753357B2 (en) | 2011-05-19 | 2014-06-17 | Abbott Cardiovascular Systems, Inc. | Devices and methods for suturing tissue |
US9289282B2 (en) | 2011-05-31 | 2016-03-22 | Edwards Lifesciences Corporation | System and method for treating valve insufficiency or vessel dilatation |
WO2013003228A1 (en) | 2011-06-27 | 2013-01-03 | University Of Maryland, Baltimore | Transapical mitral valve repair device |
CA2842288A1 (en) | 2011-07-21 | 2013-01-24 | 4Tech Inc. | Method and apparatus for tricuspid valve repair using tension |
US20140324164A1 (en) | 2011-08-05 | 2014-10-30 | Mitraltech Ltd. | Techniques for percutaneous mitral valve replacement and sealing |
CA2846497C (en) | 2011-08-25 | 2017-06-27 | Mis Solutions, Inc. | Apparatus and method for intra-abdominal movement of internal organs |
US9011468B2 (en) | 2011-09-13 | 2015-04-21 | Abbott Cardiovascular Systems Inc. | Independent gripper |
US8945177B2 (en) | 2011-09-13 | 2015-02-03 | Abbott Cardiovascular Systems Inc. | Gripper pusher mechanism for tissue apposition systems |
US8900295B2 (en) | 2011-09-26 | 2014-12-02 | Edwards Lifesciences Corporation | Prosthetic valve with ventricular tethers |
WO2013049708A1 (en) | 2011-09-30 | 2013-04-04 | Bioventrix, Inc. | Trans-catheter ventricular reconstruction structures, methods, and systems for treatment of congestive heart failure and other conditions |
US8764798B2 (en) | 2011-10-03 | 2014-07-01 | Smith & Nephew, Inc. | Knotless suture anchor |
US9039757B2 (en) | 2011-10-19 | 2015-05-26 | Twelve, Inc. | Prosthetic heart valve devices, prosthetic mitral valves and associated systems and methods |
US9827093B2 (en) | 2011-10-21 | 2017-11-28 | Edwards Lifesciences Cardiaq Llc | Actively controllable stent, stent graft, heart valve and method of controlling same |
US8858623B2 (en) | 2011-11-04 | 2014-10-14 | Valtech Cardio, Ltd. | Implant having multiple rotational assemblies |
US8968336B2 (en) | 2011-12-07 | 2015-03-03 | Edwards Lifesciences Corporation | Self-cinching surgical clips and delivery system |
CA2858149C (en) | 2011-12-12 | 2017-04-18 | David Alon | Heart valve repair device |
US9827092B2 (en) | 2011-12-16 | 2017-11-28 | Tendyne Holdings, Inc. | Tethers for prosthetic mitral valve |
US9078645B2 (en) | 2011-12-19 | 2015-07-14 | Edwards Lifesciences Corporation | Knotless suture anchoring devices and tools for implants |
US9078652B2 (en) | 2011-12-19 | 2015-07-14 | Edwards Lifesciences Corporation | Side-entry knotless suture anchoring clamps and deployment tools |
US9078747B2 (en) | 2011-12-21 | 2015-07-14 | Edwards Lifesciences Corporation | Anchoring device for replacing or repairing a heart valve |
US9017347B2 (en) | 2011-12-22 | 2015-04-28 | Edwards Lifesciences Corporation | Suture clip deployment devices |
US10226339B2 (en) | 2012-01-31 | 2019-03-12 | Mitral Valve Technologies Sarl | Mitral valve docking devices, systems and methods |
US9138214B2 (en) | 2012-03-02 | 2015-09-22 | Abbott Cardiovascular Systems, Inc. | Suture securing systems, devices and methods |
EP3508173A1 (en) | 2012-05-16 | 2019-07-10 | Edwards Lifesciences Corporation | Systems for placing a coaptation member between valvular leaflets |
US9474605B2 (en) | 2012-05-16 | 2016-10-25 | Edwards Lifesciences Corporation | Devices and methods for reducing cardiac valve regurgitation |
US8961594B2 (en) | 2012-05-31 | 2015-02-24 | 4Tech Inc. | Heart valve repair system |
DE102012010798A1 (en) | 2012-06-01 | 2013-12-05 | Universität Duisburg-Essen | Implantable device for improving or eliminating heart valve insufficiency |
US9504571B2 (en) | 2012-06-07 | 2016-11-29 | Edwards Lifesciences Corporation | Systems for implanting annuloplasty rings with microanchors |
US9498202B2 (en) | 2012-07-10 | 2016-11-22 | Edwards Lifesciences Corporation | Suture securement devices |
EP2872077B1 (en) | 2012-07-12 | 2017-10-04 | Boston Scientific Scimed, Inc. | Low profile heart valve delivery system |
US8992761B2 (en) | 2012-07-13 | 2015-03-31 | Abbott Cardiovascular Systems, Inc. | Methods for passivating metallic implantable medical devices including radiopaque markers |
WO2014018903A1 (en) | 2012-07-27 | 2014-01-30 | Rowan University | Autoantibody profiles in early detection and diagnosis of cancer |
WO2014022124A1 (en) | 2012-07-28 | 2014-02-06 | Tendyne Holdings, Inc. | Improved multi-component designs for heart valve retrieval device, sealing structures and stent assembly |
US9550058B2 (en) | 2012-08-27 | 2017-01-24 | Cardiac Pacemakers, Inc. | Compound-shaped stylet for torque transmission |
US20140067048A1 (en) | 2012-09-06 | 2014-03-06 | Edwards Lifesciences Corporation | Heart Valve Sealing Devices |
EP2895111B1 (en) | 2012-09-14 | 2023-08-09 | Boston Scientific Scimed, Inc. | Mitral valve inversion prostheses |
US9216018B2 (en) | 2012-09-29 | 2015-12-22 | Mitralign, Inc. | Plication lock delivery system and method of use thereof |
US9023099B2 (en) | 2012-10-31 | 2015-05-05 | Medtronic Vascular Galway Limited | Prosthetic mitral valve and delivery method |
US8628571B1 (en) | 2012-11-13 | 2014-01-14 | Mitraltech Ltd. | Percutaneously-deliverable mechanical valve |
US20140142689A1 (en) | 2012-11-21 | 2014-05-22 | Didier De Canniere | Device and method of treating heart valve malfunction |
WO2014087402A1 (en) | 2012-12-06 | 2014-06-12 | Valtech Cardio, Ltd. | Techniques for guide-wire based advancement of a tool |
US9211203B2 (en) | 2012-12-20 | 2015-12-15 | Abbott Cardiovascular Systems, Inc. | Hinge for medical device |
EP2943132B1 (en) | 2013-01-09 | 2018-03-28 | 4Tech Inc. | Soft tissue anchors |
WO2014134183A1 (en) | 2013-02-26 | 2014-09-04 | Mitralign, Inc. | Devices and methods for percutaneous tricuspid valve repair |
JP6329570B2 (en) | 2013-03-14 | 2018-05-23 | 4テック インコーポレイテッド | Stent with tether interface |
WO2014160330A1 (en) | 2013-03-14 | 2014-10-02 | Millepede, Llc. | Systems and methods for reshaping a heart valve |
US20140277427A1 (en) | 2013-03-14 | 2014-09-18 | Cardiaq Valve Technologies, Inc. | Prosthesis for atraumatically grasping intralumenal tissue and methods of delivery |
US9730791B2 (en) | 2013-03-14 | 2017-08-15 | Edwards Lifesciences Cardiaq Llc | Prosthesis for atraumatically grasping intralumenal tissue and methods of delivery |
US9289297B2 (en) | 2013-03-15 | 2016-03-22 | Cardiosolutions, Inc. | Mitral valve spacer and system and method for implanting the same |
EP2968847B1 (en) | 2013-03-15 | 2023-03-08 | Edwards Lifesciences Corporation | Translation catheter systems |
US20140358224A1 (en) | 2013-05-30 | 2014-12-04 | Tendyne Holdlings, Inc. | Six cell inner stent device for prosthetic mitral valves |
KR20160041040A (en) | 2013-06-14 | 2016-04-15 | 카디오솔루션즈, 인코포레이티드 | Mitral valve spacer and system and method for implanting the same |
US20140379076A1 (en) | 2013-06-25 | 2014-12-25 | Tendyne Holdings, Inc. | Halo Wire Fluid Seal Device for Prosthetic Mitral Valves |
CN109394320B (en) | 2013-07-30 | 2021-12-31 | 阿库洛医药有限公司 | Ligation device, kit and method |
WO2015020816A1 (en) | 2013-08-06 | 2015-02-12 | Lc Therapeutics, Inc. | Synthetic chord for cardiac valve repair applications |
WO2015022710A1 (en) | 2013-08-14 | 2015-02-19 | Sorin Group Italia S.R.L. | Apparatus and method for chordal replacement |
US10588613B2 (en) | 2013-08-30 | 2020-03-17 | Bioventrix, Inc. | Cardiac tissue anchoring devices, methods, and systems for treatment of congestive heart failure and other conditions |
US10070857B2 (en) | 2013-08-31 | 2018-09-11 | Mitralign, Inc. | Devices and methods for locating and implanting tissue anchors at mitral valve commissure |
US9248018B2 (en) | 2013-09-27 | 2016-02-02 | Surendra K. Chawla | Valve repair device |
US20150100116A1 (en) | 2013-10-07 | 2015-04-09 | Medizinische Universitat Wien | Implant and method for improving coaptation of an atrioventricular valve |
EP3062709A2 (en) | 2013-10-30 | 2016-09-07 | 4Tech Inc. | Multiple anchoring-point tension system |
US9775591B2 (en) | 2013-11-21 | 2017-10-03 | Edwards Lifesciences Corporation | Sealing devices and related delivery apparatuses |
US9610162B2 (en) | 2013-12-26 | 2017-04-04 | Valtech Cardio, Ltd. | Implantation of flexible implant |
US9801720B2 (en) | 2014-06-19 | 2017-10-31 | 4Tech Inc. | Cardiac tissue cinching |
WO2016011275A2 (en) | 2014-07-16 | 2016-01-21 | Edwards Lifesciences Corporation | Devices and methods for suturing a cardiac implant |
US9180005B1 (en) | 2014-07-17 | 2015-11-10 | Millipede, Inc. | Adjustable endolumenal mitral valve ring |
US10195026B2 (en) | 2014-07-22 | 2019-02-05 | Edwards Lifesciences Corporation | Mitral valve anchoring |
US20160081829A1 (en) | 2014-09-22 | 2016-03-24 | Edwards Lifesciences Corporation | Aortic insufficiency repair device and method |
US9700445B2 (en) | 2014-11-04 | 2017-07-11 | Abbott Cardiovascular Systems, Inc. | One-way actuator knob |
WO2016087934A1 (en) | 2014-12-02 | 2016-06-09 | 4Tech Inc. | Off-center tissue anchors |
CN107205817B (en) | 2014-12-04 | 2020-04-03 | 爱德华兹生命科学公司 | Percutaneous clamp for repairing heart valve |
US10188392B2 (en) | 2014-12-19 | 2019-01-29 | Abbott Cardiovascular Systems, Inc. | Grasping for tissue repair |
US10231834B2 (en) | 2015-02-09 | 2019-03-19 | Edwards Lifesciences Corporation | Low profile transseptal catheter and implant system for minimally invasive valve procedure |
US10105226B2 (en) | 2015-02-10 | 2018-10-23 | Edwards Lifesciences Corporation | Offset cardiac leaflet coaptation element |
US9848983B2 (en) | 2015-02-13 | 2017-12-26 | Millipede, Inc. | Valve replacement using rotational anchors |
US20160256269A1 (en) | 2015-03-05 | 2016-09-08 | Mitralign, Inc. | Devices for treating paravalvular leakage and methods use thereof |
US10470759B2 (en) | 2015-03-16 | 2019-11-12 | Edwards Lifesciences Corporation | Suture securement devices |
US10010315B2 (en) | 2015-03-18 | 2018-07-03 | Mitralign, Inc. | Tissue anchors and percutaneous tricuspid valve repair using a tissue anchor |
US20160287383A1 (en) | 2015-04-01 | 2016-10-06 | Edwards Lifesciences Corporation | Heart valve repair devices |
US10524912B2 (en) | 2015-04-02 | 2020-01-07 | Abbott Cardiovascular Systems, Inc. | Tissue fixation devices and methods |
-
2014
- 2014-10-28 US US14/525,668 patent/US10022114B2/en not_active Expired - Fee Related
-
2018
- 2018-07-15 US US16/035,654 patent/US20180344311A1/en not_active Abandoned
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