Patent Grant
11234813
Embodiments are described herein that relate to prosthetic heart valves, and devices and methods for use in the delivery and deployment of such valves.
Prosthetic heart valves can pose challenges for delivery and deployment within a heart, particularly for delivery by catheters through the patient's vasculature rather than through a surgical approach. Delivery of traditional transcatheter prosthetic valves generally includes compressing the valve in a radial direction and loading the valve into a delivery catheter such that a central annular axis of the valve is parallel to the lengthwise axis of the delivery catheter. The valves are deployed from the end of the delivery catheter and expanded outwardly in a radial direction from the central annular axis. The expanded size (e.g., diameter) of traditional valves, however, can be limited by the internal diameter of the delivery catheter. The competing interest of minimizing delivery catheter size presents challenges to increasing the expanded diameter of traditional valves (e.g., trying to compress too much material and structure into too little space).
Some transcatheter prosthetic valves can be configured for orthogonal delivery, which can have an increased expanded diameter relative to traditional valves. In orthogonal delivery, for example, the valve is compressed and loaded into a delivery catheter such that a central annular axis of the valve is substantially orthogonal to the lengthwise axis of the delivery catheter, which can allow the valve to be compressed laterally and extended longitudinally (e.g., in a direction parallel to the lengthwise axis of the delivery catheter). With traditional and/or orthogonally delivered transcatheter prosthetic valves, it is also desirable to provide one or more ways of anchoring, securing, and/or stabilizing the valve in the native annuls without substantially increasing a compressed size of the valve.
Accordingly, a need exists for prosthetic valves with one or more anchoring and/or stabilizing features while maintaining a relatively small compressed size that allows for transcatheter delivery of the valve.
The embodiments described herein relate generally to transcatheter prosthetic valves and methods for delivering transcatheter prosthetic valves. In some embodiments, a prosthetic heart valve includes a valve frame defining an aperture that extends along a central axis and a flow control component mounted within the aperture. The flow control component is configured to permit blood flow along the central axis in a first direction from an inflow end to an outflow end of the flow control component and block blood flow in a second direction, opposite the first direction. The valve frame includes a distal anchoring element, a proximal anchoring element, and a septal subannular anchoring element. The prosthetic heart valve has a compressed configuration for side-delivery to a heart of a patient via a delivery. The prosthetic heart valve is configured to transition from the compressed configuration to an expanded configuration when released from the delivery catheter. The prosthetic heart valve is configured to be seated in an annulus of a native valve of the heart when in the expanded configuration. The distal, proximal, and septal anchoring elements are configured to be inserted through the annulus of the native valve prior to the prosthetic heart valve being fully seated therein. The septal anchoring element is configured to extend below the annulus and contact ventricular septal tissue to stabilize the prosthetic heart valve in the annulus when the prosthetic heart valve is seated in the annulus.
Disclosed embodiments are directed to transcatheter prosthetic heart valves and/or components thereof, and methods of manufacturing, loading, delivering, and/or deploying the transcatheter prosthetic valves and/or components thereof. The transcatheter prosthetic heart valves can have a valve frame having at least a septal subannular anchoring element mounted on a septal side of the valve frame and a flow control component mounted within a central lumen or aperture of the valve frame. The flow control component can be configured to permit blood flow in a first direction through an inflow end of the valve and block blood flow in a second direction, opposite the first direction, through an outflow end of the valve. The valves described herein can be compressible and expandable along a long-axis (also referred to as a longitudinal axis) substantially parallel to a lengthwise cylindrical axis of a delivery catheter used to deliver the valves. The valves can be configured to transition between a compressed configuration for introduction into the body using the delivery catheter, and an expanded configuration for implanting at a desired location in the body.
In some implementations, the embodiments described herein are directed to a prosthetic heart valve that is a low-profile, side-delivered implantable prosthetic heart valve. The prosthetic heart valves can have at least a ring-shaped or annular valve frame, an inner flow control component (e.g., a 2-leaflet or 3-leaflet sleeve, and/or the like) mounted in the valve frame, a distal anchoring element (e.g., a subannular distal anchoring element, tab, or the like) configured to extend into the right ventricular outflow tract (RVOT), a septal anchoring element configured to extend down the septal wall to pin the septal leaflet away from the coapting leaflets of the prosthetic valve, and a proximal anchoring element (e.g., a subannular proximal anchoring element, tab, or the like) configured to extend into the proximal subannular space, preferably between the septal and the posterior leaflets of the heart.
In some embodiments, a prosthetic heart valve includes a valve frame defining an aperture that extends along a central axis and a flow control component mounted within the aperture. The flow control component is configured to permit blood flow along the central axis in a first direction from an inflow end to an outflow end of the flow control component and block blood flow in a second direction, opposite the first direction. The valve frame includes a distal anchoring element, a proximal anchoring element, and a septal subannular anchoring element. The prosthetic heart valve has a compressed configuration for side-delivery to a heart of a patient via a delivery. The prosthetic heart valve is configured to transition from the compressed configuration to an expanded configuration when released from the delivery catheter. The prosthetic heart valve is configured to be seated in an annulus of a native valve of the heart when in the expanded configuration. The distal, proximal, and septal anchoring elements are configured to be inserted through the annulus of the native valve prior to the prosthetic heart valve being fully seated therein. The septal anchoring element is configured to extend below the annulus and contact ventricular septal tissue to stabilize the prosthetic heart valve in the annulus when the prosthetic heart valve is seated in the annulus.
In some implementations, the distal anchoring element is configured to engage, for example, ventricular tissue distal to the annulus, the proximal anchoring element is configured to engage, for example, ventricular tissue proximal to the annulus, and the septal anchoring element is configured to engage, for example, at least one of a native septal wall or a native septal leaflet when the prosthetic heart valve is seated in the annulus. In some implementations, the septal anchoring element can stabilize the valve against any intra-annular rolling forces and/or any intra-annular twisting forces that might affect a desired location or positioning of the prosthetic valve within the annulus, (e.g., tilted, angled, twisted, rolled, etc.).
In some embodiments, a prosthetic heart valve includes a valve frame having a transannular section and a supra-annular section (e.g., an atrial collar) attached around a top edge of the transannular section, a distal anchoring element coupled to the transannular section, a proximal anchoring element coupled to the transannular section, a septal anchoring element coupled to the transannular section, and a flow control component mounted within the valve frame. The flow control component is configured to permit blood flow in a first direction from an inflow end to an outflow end of the prosthetic heart valve and to block blood flow in a second direction, opposite the first direction. The prosthetic heart valve has a compressed configuration for introduction into a heart of a patient via a delivery catheter and an expanded configuration when the prosthetic heart valve is released from the delivery catheter into the heart. The prosthetic heart valve is configured to be seated in an annulus of a native valve of the heart when in the expanded configuration. When the prosthetic heart valve is seated in the annulus of the native valve, the distal anchoring element is configured to be disposed in a ventricular outflow tract, he proximal anchoring element is configured to be disposed in a proximal subannular area of the heart, and the septal anchoring element is configured to extend below the annulus and contact at least one of a native septal wall or a native septal leaflet.
In some embodiments, a side-deliverable transcatheter prosthetic heart valve includes (i) a self-expanding annular support frame, said annular support frame with an outer perimeter wall having at least a distal side, a proximal side, and a septal side and circumscribing a central channel extending along a central vertical axis in an expanded configuration; (ii) a flow control component mounted within the annular support frame and configured to permit blood flow in a first direction through an inflow end of the valve and block blood flow in a second direction, opposite the first direction, through an outflow end of the valve; (iii) a distal subannular anchoring element mounted on the distal side of the annular support frame; (iv) a proximal subannular anchoring element mounted on the proximal side of the annular support frame; and (v) a septal subannular anchoring element or tab mounted on the septal side of the annular support frame. The valve is compressible to a compressed configuration for introduction into the body using a delivery catheter. The valve in the compressed configuration has a height of 8-12 mm, a width of 8-12 mm, and a length of 25-80 mm. A horizontal axis of the valve in the compressed configuration is substantially parallel to a lengthwise cylindrical axis of the delivery catheter. The valve in the expanded configuration has a height of about 5-60 mm and a diameter of about 25-80 mm. In some implementations, the valve in the compressed configuration can be oriented such that the horizontal axis is at an intersecting angle of between 45-135 degrees to the central vertical axis. In some implementations, the valve in the expanded configuration can be oriented such that the horizontal axis is at an intersecting angle of between 45-135 degrees to the central vertical axis.
Any of the prosthetic heart valves described herein can be configured to transition between an expanded configuration and a compressed configuration. For example, any of the embodiments described herein can be a balloon-inflated prosthetic heart valve, a self-expanding prosthetic heart valve, and/or the like.
Any of the prosthetic heart valves described herein can be compressible—into the compressed configuration—in a lengthwise or orthogonal direction relative to the central axis of the flow control component that can allow a large diameter valve (e.g., having a height of about 5-60 mm and a diameter of about 20-80 mm) to be delivered and deployed from the inferior vena cava directly into the annulus of a native mitral or tricuspid valve using, for example, a 24-36 Fr delivery catheter and without delivery and deployment from the delivery catheter at an acute angle of approach.
Any of the prosthetic heart valves described herein can have a central axis when in a compressed configuration that is co-axial or at least substantially parallel with blood flow direction through the valve. In some embodiments, the compressed configuration of the valve is orthogonal to the blood flow direction. In some embodiments, a long-axis is oriented at an intersecting angle of between 45-135 degrees to the first direction when in the compressed configuration and/or the expanded configuration.
In some embodiments, the annular support frame is a compressible wire frame including one of braided-wire cells, laser-cut wire cells, photolithography produced wire cells, 3D printed wire cells, wire cells formed from intermittently connected single strand wires in a wave shape, a zig-zag shape, or spiral shape, and combinations thereof.
Any of the prosthetic heart valves described herein can include a septal anchoring element extending from a lower septal side of a frame of the prosthetic heart valve, which can be used, for example, as a septal tissue and/or leaflet anchoring and/or stabilization element or tab. The septal anchoring element can include and/or can be formed from a wire loop or wire frame, an integrated frame section, and/or a stent, extending from the frame (e.g., about 10-40 mm away from the frame).
Any of the prosthetic heart valves described herein can include a distal anchoring element extending from a lower distal side of the frame of the prosthetic heart valve, which can be used, for example, as a ventricular outflow tract tab. The distal anchoring element can include and/or can be formed from a wire loop or wire frame, an integrated frame section, and/or a stent, extending from the frame (e.g., about 10-40 mm away the tubular frame).
Any of the prosthetic heart valves described herein can include a proximal anchoring element extending from a lower proximal side of the frame of the prosthetic heart valve, which can be used, for example, as a proximal tissue and/or area anchoring and/or stabilization tab. The proximal anchoring element can include and/or can be formed from a wire loop or wire frame, an integrated frame section, and/or a stent, extending away from the frame (e.g., about 10-40 mm away from the frame). The proximal anchoring element can be one of a fixed anchoring element or an anchoring element configured to transition from a first (e.g., compressed) configuration to a second (e.g., expanded) configuration after the prosthetic heart valve is seated in an annulus of a native heart valve. For example, the proximal anchoring element can be moveable from a first stowed position (e.g., held against an outer perimeter wall of the frame) while the prosthetic heart valve is being positioned in the native annulus to a second deployed position that extends away from the outer perimeter wall to provide a proximal subannular anchor.
Any of the prosthetic heart valves described herein can include (i) an upper anchoring element attached to a distal upper edge of the tubular frame, the upper anchoring element can include or be formed from a wire loop or wire frame extending from about 2-20 mm away from the tubular frame, and (ii) a lower anchoring element (e.g., used as a RVOT tab) extending from a distal side of the tubular frame, the lower anchoring element can include and/or can be formed from a wire loop or wire frame extending from about 10-40 mm away from the tubular frame.
Any of the prosthetic heart valves described herein can include a distal lower anchoring element configured to be positioned into the RVOT of the right ventricle, a proximal lower anchoring element configured to be positioned into a subannular position in contact with and/or adjacent to subannular tissue of the right ventricle on a proximal side of the annulus, and a septal subannular anchoring tab mounted on the septal side of the annular support frame and configured to be positioned into a subannular position in contact with and/or in contact with septal wall tissue and/or native septal leaflets. The prosthetic heart valve can also include a distal upper anchoring element configured to be positioned into a supra-annular position in contact with and/or adjacent to supra-annular tissue of the right atrium. The distal upper anchoring element can provide a supra-annular downward force in the direction of the right ventricle and the distal and proximal lower anchoring elements can provide a subannular upward force in the direction of the right atrium. The septal anchoring element similarly can provide an upward force in the direction of the right atrium and/or can stabilize the valve against any intra-annular rolling forces and/or any intra-annular twisting forces that might affect a desired location or positioning of the prosthetic valve within the annulus, (e.g., tilted, angled, twisted, rolled, etc.).
Any of the prosthetic valves and/or components thereof may be fabricated from any suitable biocompatible material or combination of materials. For example, an outer valve frame, an inner valve frame (e.g., of an inner flow control component), and/or components thereof may be fabricated from biocompatible metals, metal alloys, polymer coated metals, and/or the like. Suitable biocompatible metals and/or metal alloys can include stainless steel (e.g., 316 L stainless steel), cobalt chromium (Co—Cr) alloys, nickel-titanium alloys (e.g., Nitinol®), and/or the like. Moreover, any of the outer or inner frames described herein can be formed from superelastic or shape-memory alloys such as nickel-titanium alloys (e.g., Nitinol®). Any of the prosthetic valves and/or components thereof can include any suitable coating, covering, and/or the like. Suitable polymer coatings can include, for example, polyethylene vinyl acetate (PEVA), poly-butyl methacrylate (PBMA), translute Styrene Isoprene Butadiene (SIBS) copolymer, polylactic acid, polyester, polylactide, D-lactic polylactic acid (DLPLA), polylactic-co-glycolic acid (PLGA), and/or the like. Some such polymer coatings may form a suitable carrier matrix for drugs such as, for example, Sirolimus, Zotarolimus, Biolimus, Novolimus, Tacrolimus, Paclitaxel, Probucol, and/or the like.
Additional biocompatible synthetic material(s) can include, for example, polyesters, polyurethanes, elastomers, thermoplastics, thermoplastic polycarbonate urethane, polyether urethane, segmented polyether urethane, silicone polyether urethane, polyetheretherketone (PEEK), silicone-polycarbonate urethane, polypropylene, polyethylene, low-density polyethylene (LDPE), high-density polyethylene (HDPE), ultra-high density polyethylene (UHDPE), polyolefins, polyethylene-glycols, polyethersulphones, polysulphones, polyvinylpyrrolidones, polyvinylchlorides, other fluoropolymers, polyesters, polyethylene-terephthalate (PET) (e.g., Dacron), Poly-L-lactic acids (PLLA), polyglycolic acid (PGA), poly(D, L-lactide/glycolide) copolymer (PDLA), silicone polyesters, polyamides (Nylon), polytetrafluoroethylene (PTFE) (e.g., Teflon), elongated PTFE, expanded PTFE, siloxane polymers and/or oligomers, polylactones, and/or the like or block co-polymers using the same. For example, where a thin, durable synthetic material is contemplated (e.g., for a covering), synthetic polymer materials such expanded PTFE or polyester (or any of the other materials described herein) may optionally be used.
Any of the outer valve frames, inner valve frames (e.g., of the flow control components), and/or portions or components thereof can be internally or externally covered, partially or completely, with a biocompatible material such as pericardium. A valve frame may also be optionally externally covered, partially or completely, with a second biocompatible material such as polyester or Dacron®. Disclosed embodiments may use tissue, such as a biological tissue that is a chemically stabilized pericardial tissue of an animal, such as a cow (bovine pericardium), sheep (ovine pericardium), pig (porcine pericardium), or horse (equine pericardium). Preferably, the tissue is bovine pericardial tissue. Examples of suitable tissue include that used in the products DuraGuard®, Peri-Guard®, and Vascu-Guard®, all products currently used in surgical procedures, and which are marketed as being harvested generally from cattle less than 30 months old. Alternatively, disclosed embodiments may use and/or may be covered, partially or completely, with a biocompatible synthetic such as any of those described above.
Any method for delivering prosthetic heart valves described herein can include side/orthogonal delivery of the prosthetic heart valve to a desired location in the body that includes advancing a delivery catheter to the desired location in the body and delivering the prosthetic heart valve in a compressed configuration to the desired location in the body by releasing the valve from the delivery catheter. The valve transitions to an expanded configuration when released from the delivery catheter.
Any method for delivering prosthetic heart valves described herein can include attaching a pulling/pushing wire (e.g., a rigid elongated rod, draw wire, and/or the like) to a sidewall or an anchoring element (e.g., a distal anchoring element) of the prosthetic heart valve. Such methods can include releasing the valve from the delivery catheter by one of (i) pulling the valve out of the delivery catheter using the pulling/pushing wire, wherein advancing the pulling/pushing wire away from a distal end of the delivery catheter pulls the compressed valve out of the delivery catheter, or (ii) pushing the valve out of the delivery catheter using the pulling/pushing wire, wherein advancing the pulling/pushing wire through and/or out of a distal end of the delivery catheter pushes the compressed valve out of the delivery catheter.
Any method for delivering prosthetic heart valves described herein can include orthogonal delivery of the prosthetic heart valve to a native annulus of a human heart that includes at least one of (i) advancing the delivery catheter to the tricuspid valve or pulmonary artery of the heart through the inferior vena cava (IVC) via the femoral vein, (ii) advancing to the tricuspid valve or pulmonary artery of the heart through the superior vena cava (SVC) via the jugular vein, or (iii) advancing to the mitral valve of the heart through a trans-atrial approach (e.g., fossa ovalis or lower), via the IVC-femoral or the SVC jugular approach; and (iv) delivering prosthetic heart valve to the native annulus by releasing the valve from the delivery catheter.
In some embodiments, a prosthetic heart valve has a valve frame with a distal anchoring element, a proximal anchoring element, a septal anchoring element, and a flow control component mounted within the valve frame. In some implementations, a method of deploying the prosthetic heart valve in an annulus of a native valve of a heart of a patient includes disposing in the atrium of the heart a distal end of a delivery catheter having disposed in a lumen thereof the prosthetic heart valve in a compressed configuration. The prosthetic heart valve is released from the lumen of the delivery catheter such that the prosthetic heart valve transitions from the compressed configuration to an expanded configuration. At least a portion of the prosthetic heart valve is seated in the annulus of the native valve. The septal anchoring element is placed in contact with at least one of a native septal wall or a septal leaflet area to stabilize the prosthetic heart valve in the annulus when the prosthetic heart valve is seated in the annulus.
Any method for delivering prosthetic heart valves described herein can include releasing the valve from a delivery catheter while increasing blood flow during deployment of the valve by partially releasing the valve from the delivery catheter to establish blood flow around the partially released valve and blood flow through the flow control component; (ii) completely releasing the valve from the delivery catheter while maintaining attachment to the valve to transition to a state with increased blood flow through the flow control component and decreased blood flow around the valve; (iii) deploying the valve into a final mounted position in a native annulus to transition to a state with complete blood flow through the flow control component and minimal or no blood flow around the valve; and (iv) disconnecting and withdrawing a positioning catheter, pulling or pushing wire or rod, and/or the delivery catheter.
In some embodiments, a method of delivering a prosthetic heart valve to an annulus of a native valve between an atrium and a ventricle of a heart of a patient includes disposing adjacent to the annulus of the native valve a distal end of a delivery catheter having disposed in a lumen thereof the prosthetic heart valve. The prosthetic heart valve includes a valve frame with a septal anchoring element configured to extend down the septal wall to pin the septal leaflet away from the coapting leaflets of the prosthetic heart valve, a distal anchoring element and a proximal anchoring element, and a flow control component mounted within the valve frame. The prosthetic heart valve is in a compressed configuration within the lumen of the delivery catheter. The prosthetic heart valve is released from the lumen of the delivery catheter. The prosthetic heart valve is configured to transition from the compressed configuration to an expanded configuration in response to being released. A portion of the distal anchoring element is placed on the ventricle side of the annulus of the native valve. The prosthetic heart valve is seated in the annulus when the proximal anchoring element is in a first configuration and the proximal anchoring element is transitioned from the first configuration to a second configuration after the prosthetic heart valve is seated in the annulus.
In some embodiments, the septal anchoring element is transitioned from a first stowed or folded position to a second expanded position. For example, the septal anchoring element can be formed from a shape-memory alloy or the like that can transition between two or more configurations. In some implementations, the transition can be actuated and/or initiated when the valve is sufficiently released from the delivery catheter. In some implementations, the transition can be actuated and/or initiated by releasing a tensile element. In some implementations, the transition can be actuated and/or initiated by a secondary catheter tool that folds the septal anchoring element down from a first stowed position and into the second expanded, subannular position. Similarly, in some embodiments, the proximal anchoring element is transitioned from a first stowed or folded position to a second expanded position. In such embodiments, the seating of the proximal anchoring element includes releasing the proximal anchoring element from a compressed pre-release configuration to an expanded post-release configuration with the proximal anchoring element extending into the proximal subannular anchoring area.
The terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the full scope of the claims. Unless defined otherwise, all technical and scientific terms used herein have the same meanings as commonly understood by one of ordinary skill in the art.
As used herein, the singular forms “a,” “an,” and “the” are intended to include the plural forms as well, unless the context clearly indicates otherwise. With respect to the use of substantially any plural and/or singular terms herein, those having skill in the art can translate from the plural to the singular and/or from the singular to the plural as is appropriate to the context and/or application. The various singular/plural permutations may be expressly set forth herein for sake of clarity.
In general, terms used herein, and especially in the appended claims (e.g., bodies of the appended claims) are generally intended as “open” terms (e.g., the term “including” should be interpreted as “including but not limited to,” the term “having” should be interpreted as “having at least,” etc.). Similarly, the terms “comprises” and/or “comprising,” when used in this specification, specify the presence of stated features, integers (or fractions thereof), steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, integers (or fractions thereof), steps, operations, elements, components, and/or groups thereof. As used in this document, the term “comprising” means “including, but not limited to.”
As used herein the term “and/or” includes any and all combinations of one or more of the associated listed items. It should be understood that any suitable disjunctive word and/or phrase presenting two or more alternative terms, whether in the description, claims, or drawings, contemplate the possibilities of including one of the terms, either of the terms, or both/all terms. For example, the phrase “A or B” will be understood to include the possibilities of “A” or “B” or “A and B.”
All ranges disclosed herein also encompass any and all possible subranges and combinations of subranges thereof unless expressly stated otherwise. Any listed range should be recognized as sufficiently describing and enabling the same range being broken down into at least equal subparts unless expressly stated otherwise. As will be understood by one skilled in the art, a range includes each individual member.
The term “valve prosthesis,” “prosthetic heart valve,” and/or “prosthetic valve” can refer to a combination of a frame and a leaflet or flow control structure or component, and can encompass both complete replacement of an anatomical part (e.g., a new mechanical valve replaces a native valve), as well as medical devices that take the place of and/or assist, repair, or improve existing anatomical parts (e.g., the native valve is left in place).
Prosthetic valves disclosed herein can include a member (e.g., a frame) that can be seated within a native valve annulus and can be used as a mounting element for a leaflet structure, a flow control component, or a flexible reciprocating sleeve or sleeve-valve. It may or may not include such a leaflet structure or flow control component, depending on the embodiment. Such members can be referred to herein as an “annular support frame,” “tubular frame,” “wire frame,” “valve frame,” “flange,” “collar,” and/or any other similar terms.
The term “flow control component” can refer in a non-limiting sense to a leaflet structure having 2-, 3-, 4-leaflets of flexible biocompatible material such a treated or untreated pericardium that is sewn or joined to a annular support frame, to function as a prosthetic heart valve. Such a valve can be a heart valve, such as a tricuspid, mitral, aortic, or pulmonary, that is open to blood flowing during diastole from atrium to ventricle, and that closes from systolic ventricular pressure applied to the outer surface. Repeated opening and closing in sequence can be described as “reciprocating.” The flow control component is contemplated to include a wide variety of (bio)prosthetic artificial heart valves and/or components. For example, such (bio)prosthetics can include ball valves (e.g., Starr-Edwards), bileaflet valves (St. Jude), tilting disc valves (e.g., Bjork-Shiley), stented pericardium heart-valve prosthesis' (bovine, porcine, ovine) (Edwards line of bioprostheses, St. Jude prosthetic valves), as well as homograft and autograft valves. Bioprosthetic pericardial valves can include bioprosthetic aortic valves, bioprosthetic mitral valves, bioprosthetic tricuspid valves, and bioprosthetic pulmonary valves.
The terms “anchoring element” or “tab” or “arm” refer to structural elements extending from a portion of the valve or valve frame (e.g., extending away from a valve sidewall or body or collar) to provide an anchoring or stabilizing function to the valve. When used in conjunction with the terms distal, proximal, septal, and/or anterior, it should be understood that the anchoring or stabilizing element so described is attached to and/or integral with the valve at a distal, proximal, septal, and/or anterior location, respectively. A distal location on a valve refers to a portion of the valve furthest from the practitioner which exits the delivery catheter first, and which can be placed at or near distal subannular native tissue such as the ventricular outflow tract. A proximal location on a valve refers to a portion of the valve closest to the practitioner which exits the delivery catheter last, and which can be placed at or near proximal subannular native tissue such as tissue closest to the inferior vena cava. A septal location on a valve refers to a portion of the valve at a point between a proximal and a distal location, and which can be placed at or near septal subannular native tissue such as the septal leaflet or septal wall. An anterior location on a valve refers to a portion of the valve at a point between a proximal and a distal location, and which can be placed at or near anterior tissue opposite the septal tissue. When used in conjunction with the term “lower,” it should be understood that the anchoring or stabilizing element so described is attached to and/or integral with the valve sidewall or body at or along subannular region of the valve. Conversely, when used in conjunction with the term “upper,” it should be understood that the anchoring or stabilizing element so described is attached to and/or integral with the valve at or along a supra-annular region, collar, or atrial cuff of the valve.
Any of the disclosed valve embodiments may be delivered by a transcatheter approach. The term “transcatheter” is used to define the process of accessing, controlling, and/or delivering a medical device or instrument within the lumen of a catheter that is deployed into a heart chamber (or other desired location in the body), as well as an item that has been delivered or controlled by such as process. Transcatheter access is known to include cardiac access via the lumen of the femoral artery and/or vein, via the lumen of the brachial artery and/or vein, via lumen of the carotid artery, via the lumen of the jugular vein, via the intercostal (rib) and/or sub-xiphoid space, and/or the like. Moreover, transcatheter cardiac access can be via the inferior vena cava (IVC), superior vena cava (SVC), and/or via a trans-atrial (e.g., fossa ovalis or lower). Transcatheter can be synonymous with transluminal and is functionally related to the term “percutaneous” as it relates to delivery of heart valves. As used herein, the term “lumen” can refer to the inside of a cylinder or tube.
The mode of cardiac access can be based at least in part on a “body channel,” used to define a blood conduit or vessel within the body, and the particular application of the disclosed embodiments of prosthetic valves can determine the body channel at issue. An aortic valve replacement, for example, would be implanted in, or adjacent to, the aortic annulus. Likewise, a tricuspid or mitral valve replacement would be implanted at the tricuspid or mitral annulus, respectively. While certain features described herein may be particularly advantageous for a given implantation site, unless the combination of features is structurally impossible or excluded by claim language, any of the valve embodiments described herein could be implanted in any body channel.
The term “expandable” as used herein may refer to a prosthetic heart valve or a component of the prosthetic heart valve capable of expanding from a first, delivery size or configuration to a second, implantation size or configuration. An expandable structure, therefore, is not intended to refer to a structure that might undergo slight expansion, for example, from a rise in temperature or other such incidental cause, unless the context clearly indicates otherwise. Conversely, “non-expandable” should not be interpreted to mean completely rigid or a dimensionally stable, as some slight expansion of conventional “non-expandable” heart valves, for example, may be observed.
The prosthetic valves disclosed herein and/or components thereof are generally capable of transitioning between two or more configurations, states, shapes, and/or arrangements. For example, prosthetic valves described herein can be “compressible” and/or “expandable” between any suitable number of configurations. Various terms can be used to describe or refer to these configurations and are not intended to be limiting unless the context clearly states otherwise. For example, a prosthetic valve can be described as being placed in a “delivery configuration,” which may be any suitable configuration that allows or enables delivery of the prosthetic valve. Examples of delivery configurations can include a compressed configuration, a folded configuration, a rolled configuration, and/or similar configuration or any suitable combinations thereof. Similarly, a prosthetic valve can be described as being placed in an “expanded configuration,” which may be any suitable configuration that is not expressly intended for delivery of the prosthetic valve. Examples of expanded configuration can include a released configuration, a relaxed configuration, a deployed configuration, a non-delivery configuration, and/or similar configurations or any suitable combinations thereof. Some prosthetic valves described herein and/or components or features thereof can have a number of additional configurations that can be associated with various modes, levels, states, and/or portions of actuation, deployment, engagement, etc. Examples of such configurations can include an actuated configuration, a seated configuration, a secured configuration, an engaged configuration, and/or similar configurations or any suitable combinations thereof. While specific examples are provided above, it should be understood that they are not intended to be an exhaustive list of configurations. Other configurations may be possible. Moreover, various terms can be used to describe the same or substantially similar configurations and thus, the use of particular terms are not intended to be limiting and/or to the exclusion of other terms unless the terms and/or configurations are mutually exclusive, or the context clearly states otherwise.
Any of the disclosed valve embodiments may be delivered via traditional transcatheter delivery techniques or via orthogonal delivery techniques. For example, traditional delivery of prosthetic valves can be such that a central cylinder axis of the valve is substantially parallel to a length-wise axis of a delivery catheter used to deliver the valve. Typically, the valves are compressed in a radial direction relative to the central cylinder axis and advanced through the lumen of the delivery catheter. The valves are deployed from the end of the delivery catheter and expanded outwardly in a radial direction from the central cylinder axis. The delivery orientation of the valve generally means that the valve is completely released from the delivery catheter while in the atrium of the heart and reoriented relative to the annulus, which in some instances, can limit a size of the valve.
As used herein the terms “side-delivered,” “side-delivery,” “orthogonal delivery,” “orthogonally delivered,” and/or so forth can be used interchangeably to describe such a delivery method and/or a valve delivered using such a method. Orthogonal delivery of prosthetic valves can be such that the central cylinder axis of the valve is substantially orthogonal to the length-wise axis of the delivery catheter. With orthogonal delivery, the valves are compressed (or otherwise reduced in size) in a direction substantially parallel to the central cylinder axis and/or in a lateral direction relative to the central cylinder axis. As such, a length-wise axis (e.g., a longitudinal axis) of an orthogonally delivered valve is substantially parallel to the length-wise axis of the delivery catheter. In other words, an orthogonally delivered prosthetic valve is compressed and/or delivered at a roughly 90-degree angle compared to traditional processes of compressing and delivering transcatheter prosthetic valves. Moreover, in some instances, the orientation of orthogonally delivered valves relative to the annulus can allow a distal portion of the valve to be at least partially inserted into the annulus of the native heart valve while the proximal portion of the valve, at least in part, remains in the delivery catheter, thereby avoiding at least some of the size constraints faced with some know traditional delivery techniques.
Examples of prosthetic valves configured to be orthogonally delivered and processes of delivering such valves are described in detail in U.S. Patent Publication No. 2020/0188097, filed Dec. 11, 2019, entitled “Compressible Bileaflet Frame for Side Delivered Transcatheter Heart Valve” (“the '097 publication”); International Patent Publication No. WO 2020/061331, filed Sep. 19, 2019, entitled “Transcatheter Deliverable Prosthetic Heart Valves and Method of Delivery” (“the '331 WIPO publication”); International Patent Publication No. WO 2020/131978, filed Dec. 18, 2019, entitled “Transcatheter Deliverable Prosthetic Heart Valves and Methods of Delivery” (“the '978 WIPO publication”); International Patent Publication No. WO 2020/154734, filed Jan. 27, 2020, entitled “Collapsible Inner Flow Control Component for Side-Deliverable Transcatheter Heart Valve Prosthesis” (“the '734 WIPO publication”); International Patent Publication No. WO 2020/227249, filed May 4, 2020, entitled “Cinch Device and Method for Deployment of a Side-Delivered Prosthetic Heart Valve in a Native Annulus” (“the '249 WIPO publication”); International Patent Application Serial No. PCT/US2020/045195, filed Aug. 6, 2020, entitled “Side-Deliverable Transcatheter Prosthetic Valves and Methods for Delivering and Anchoring the Same” (“the '195 PCT application”); and/or International Patent Application Serial No. PCT/US2020/047162, filed Aug. 20, 2020, entitled “Delivery and Retrieval Devices and Methods for Side-Deliverable Transcatheter Prosthetic Valves” (“the '162 PCT application”), the disclosure of each of which is incorporated herein by reference in its entirety.
Mathematically, the term “orthogonal” refers to an intersecting angle of 90 degrees between two lines or planes. As used herein, the term “substantially orthogonal” refers to an intersecting angle of 90 degrees plus or minus a suitable tolerance. For example, “substantially orthogonal” can refer to an intersecting angle ranging from 75 to 105 degrees.
The embodiments herein, and/or the various features or advantageous details thereof, are explained more fully with reference to the non-limiting embodiments that are illustrated in the accompanying drawings and detailed in the following description. Descriptions of well-known components and processing techniques are omitted so as to not unnecessarily obscure the embodiments herein. Like numbers refer to like elements throughout.
The examples and/or embodiments described herein are intended to facilitate an understanding of structures, functions, and/or aspects of the embodiments, ways in which the embodiments may be practiced, and/or to further enable those skilled in the art to practice the embodiments herein. Similarly, methods and/or ways of using the embodiments described herein are provided by way of example only and not limitation. Specific uses described herein are not provided to the exclusion of other uses unless the context expressly states otherwise. For example, any of the prosthetic valves described herein can be used to replace a native valve of a human heart including, for example, a mitral valve, a tricuspid valve, an aortic valve, and/or a pulmonary valve. While some prosthetic valves are described herein in the context of replacing a native mitral valve or a native tricuspid valve, it should be understood that such a prosthetic valve can be used to replace any native valve unless expressly stated otherwise or unless one skilled in the art would clearly recognize that one or more components and/or features would otherwise make the prosthetic valve incompatible for such use. Accordingly, specific examples, embodiments, methods, and/or uses described herein should not be construed as limiting the scope of the inventions or inventive concepts herein. Rather, examples and embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the inventive concepts to those skilled in the art.
The prosthetic valve 100 is compressible and expandable between an expanded configuration (
In some embodiments, the valve 100 (and/or at least a portion thereof) may be heat-shaped and/or otherwise formed into any desired shape such as, for example, a roughly tubular shape, a roughly hourglass shape, and/or the like. In some embodiments, the valve 100 can include an upper atrial cuff or flange for atrial sealing, a lower ventricle cuff or flange for ventricular sealing, and a transannular section or region (e.g., a body section, a tubular section, a cylindrical section, etc.) disposed therebetween. The transannular region can have an hourglass cross-section for about 60-80% of the circumference to conform to the native annulus along the posterior and anterior annular segments while remaining substantially vertically flat along 20-40% of the annular circumference to conform to the septal annular segment. While the valve 100 is shown in
For example, the valve 100 can be centric (e.g., radially symmetrical relative to a central y-axis 104) or eccentric (e.g., radially asymmetrical relative to the central y-axis axis 104). In some eccentric embodiments, the valve 100, or an outer frame thereof, may have a complex shape determined by the anatomical structures where the valve 100 is being mounted. For example, in some instances, the valve 100 may be deployed in an annulus of a native tricuspid valve having a circumference in the shape of a rounded ellipse with a substantially vertical septal wall, which is known to enlarge in disease states along an anterior-posterior line. In some instances, the valve 100 may be deployed in an annulus of a native mitral valve (e.g., near the anterior leaflet) having a circumference in the shape of a rounded ellipse with a substantially vertical septal wall, which is known to enlarge in disease states. As such, the valve 100 can have a complex shape that determined, at least in part, by the native annulus and/or a disease state of the native valve. By way of example, the valve 100 or the outer frame thereof may have a D-shape (viewed from the top) so the flat portion can be matched to the anatomy in which the valve 100 will be deployed (e.g., a substantially vertical septal wall). In some embodiments, the valve 100 or the outer frame thereof can have a circumference in the shape of a rounded ellipse, such as a hyperbolic paraboloid, to account for the positions of native septal, anterior, and/or posterior leaflets, and/or the native septal wall; to avoid native electrical bundles such as the atrioventricular (A-V) node and/or A-V node-related structures like the Triangle of Koch, AV bundle, etc.; to avoid interference with coronary blood flow such as the coronary sinus; to accommodate variances in the septal wall that is known to be substantially vertical but that enlarges along the Anterior-Posterior axis toward the free wall in disease states.
As shown, the valve 100 generally includes an annular support frame 110 and a flow control component 150 mounted within the annular support frame 110. In addition, the valve 100 and/or at least the annular support frame 110 of the valve 100 can include, couple to, and/or otherwise engage a delivery system 180. In some implementations, the valve 100 and/or aspects or portions thereof can be similar to and/or substantially the same as the valves (and/or the corresponding aspects or portions thereof) described in detail in the '097 publication, the '331 WIPO publication, the '978 WIPO publication, the '734 WIPO publication, the '249 WIPO publication, the '195 PCT application, and/or the '162 PCT application incorporated by reference hereinabove. Accordingly, certain aspects, portions, and/or details of the valve 100 may not be described in further detail herein.
The annular support frame 110 (also referred to herein as “tubular frame,” “valve frame,” “wire frame,” “outer frame,” or “frame”) can have a supra-annular region 120, a subannular region 130, and a transannular region 112, disposed and/or coupled therebetween. In some embodiments, the frame 110 can be monolithically and/or unitarily constructed. In some embodiments, one or more of the supra-annular region 120, the subannular region 130, and/or the transannular region 112 can be separate, independent, and/or modular components that are coupled to collectively form the frame 110. For example, in some embodiments, the supra-annular region 120 can be, for example, an atrial collar or cuff coupled to a top, upper, and/or supra-annular edge of the transannular region 112 and the subannular region 130 can be a bottom, lower, and/or subannular portion or section of the transannular region 112 of the fame 110.
In some implementations, a modular and/or at least partially modular configuration can allow the frame 110 to be adapted to a given size and/or shape of the anatomical structures where the valve 100 is being mounted. For example, one or more of the supra-annular region(s) 120, the subannular region 130, and/or the transannular region 112 can be designed and/or adapted so that that the support frame 110 has any desirable height, outer diameter, and/or inner diameter such as any of those described above. Moreover, such a modular configuration can allow the frame 110 to bend, flex, compress, fold, roll, and/or otherwise reconfigure without plastic or permanent deformation thereof. For example, the frame 110 is compressible to a compressed or delivery configuration for delivery and when released it is configured to return to its original shape (uncompressed, expanded, or released configuration) substantially without plastic or permanent deformation.
The support frame 110 and/or the supra-annular region 120, sub annular region 130, and/or transannular region 112 can be formed from or of any suitable material. In some embodiments, the frame 110 and/or one or more portions or regions thereof can be formed from or of a shape-memory or superelastic metal, metal alloy, plastic, and/or the like. For example, the frame 110 (e.g., one or more of the supra-annular region 120, the subannular region 130, and the transannular region 112) can be formed from or of Nitinol or the like. In some embodiments, the frame 110 (and/or any of the regions thereof) can be laser cut from a Nitinol sheet or tube. In other embodiments, the frame 110 (and/or any of the regions thereof) can be formed of or from a Nitinol wire that is bent, kink, formed, and/or manipulated into a desired shape. In still other embodiments, the frame 110 (and/or any of the regions thereof) can be formed of or from a desired material using any suitable additive or subtractive manufacturing process such as those described above. Moreover, the frame 110 and/or one or more of the supra-annular region 120, the subannular region 130, and the transannular region 112 can be formed of or from a metal or other structural frame material, which in turn, is covered by a biocompatible material such as, for example, pericardium tissue (e.g., DuraGuard®, Peri-Guard®, VascuGuard®, etc.), polymers (e.g., polyester, Dacron®, etc.), and/or the like, as described above.
The supra-annular region 120 of the frame 110 can be and/or can form, for example, a cuff or collar that can be attached or coupled to an upper edge or upper portion of the transannular region 112. When the valve 100 is deployed within a human heart, the supra-annular region 120 can be an atrial collar that is shaped to conform to the native deployment location. In a tricuspid and/or mitral valve replacement, for example, the supra-annular region 120 (e.g., atrial collar) can have various portions configured to conform to the native valve and/or a portion of the atrial floor surrounding the tricuspid and/or mitral valve, respectively. In some implementations, the supra-annular region 120 can be deployed on the atrial floor to direct blood from the atrium into the flow control component 150 of the valve 100 and to seal against blood leakage (perivalvular leakage) around the frame 110.
In some embodiments, the supra-annular region 120 can be a wire frame that is laser cut out of any suitable material. In some embodiments, the supra-annular region 120 can be formed from a tube or sheet of a shape-memory or superelastic material such as, for example, Nitinol and, for example, heat-set into a desired shape and/or configuration. In some embodiments, forming the supra-annular region 120 in such a manner can allow the supra-annular region 120 to bend, flex, fold, compress, and/or otherwise reconfigure substantially without plastically deforming and/or without fatigue that may result in failure or breaking of one or more portions thereof. Moreover, the wire frame of the supra-annular region 120 can be covered by any suitable biocompatible material such as any of those described above.
The supra-annular region 120 includes a distal portion and a proximal portion. In some embodiments, the distal portion can be and/or can include a distal supra-annular anchoring element and/or the like that can engage supra-annular native tissue on a distal side of the annulus as the prosthetic valve 100 is seated into the annulus. In some embodiments, the proximal portion can be and/or can include a proximal supra-annular anchoring element and/or the like that can engage supra-annular native tissue on a proximal side of the annulus as the prosthetic valve 100 is seated in the annulus. In some embodiments, the distal portion and/or the distal supra-annular anchoring element can be sized and/or shaped to correspond to a size and/or shape of the distal portion of the atrial floor of the heart in which the prosthetic valve 100 is disposed. Similarly, the proximal portion and/or the proximal supra-annular anchoring element can be sized and/or shaped to correspond to a size and/or shape of a proximal portion of the atrial floor of the heart.
Although not shown in
The transannular region 112 of the support frame 110 is coupled to the supra-annular region 120 and extends from the supra-annular region 120 and at least partially through the annulus of the native valve when the prosthetic valve 100 is seated therein. In some embodiments, the transannular region 112 can be coupled to the supra-annular region 120 such that a desired amount of movement and/or flex is allowed therebetween (e.g., welded, bonded, sewn, bound, and/or the like). For example, in some implementations, the transannular region 112 and/or portions thereof can be sewn to the supra-annular region 120 (and/or portions thereof).
The transannular region 112 can be shaped and/or formed into a ring, a cylindrical tube, a conical tube, D-shaped tube, and/or any other suitable annular shape. In some embodiments, the transannular region 112 may have a side profile of a flat-cone shape, an inverted flat-cone shape (narrower at top, wider at bottom), a concave cylinder (walls bent in), a convex cylinder (walls bulging out), an angular hourglass, a curved, graduated hourglass, a ring or cylinder having a flared top, flared bottom, or both. Moreover, the transannular region 112 can form and/or define an aperture or central channel 114 that extends along the central axis 104 (e.g., the y-axis). The central channel 114 (e.g., a central axial lumen or channel) can be sized and configured to receive the flow control component 150 across at least a portion of a diameter of the central channel 114. In some embodiments, the transannular region 112 can have a shape and/or size that is at least partially based on a size, shape, and/or configuration of the supra-annular region 120 (and/or subannular region 130) and/or the native annulus in which it is configured to be deployed. For example, the transannular region 112 can have an outer circumference surface for engaging native annular tissue that may be tensioned against an inner aspect of the native annulus to provide structural patency to a weakened native annular ring.
In some embodiments, the transannular region 112 can be a wire frame that is laser cut out of any suitable material. For example, the transannular region 112 can be formed from a tube or sheet of a shape-memory or superelastic material such as, for example, Nitinol and, for example, heat-set into a desired shape and/or configuration. Although not shown in
As described above with reference to the supra-annular region 120, the wire frame of the transannular region 112 can be covered by any suitable biocompatible material such as any of those described above. In some implementations, the wire frame of at least the supra-annular region 120 and transannular region 112 can be flexibly coupled (e.g., sewn) to form a wire frame portion of the support frame 110, which in turn, is covered in the biocompatible material. Said another way, at least the supra-annular region 120 and the transannular region 112 can be covered with the biocompatible material prior to being coupled or after being coupled. In embodiments in which the wire frames are covered after being coupled, the biocompatible material can facilitate and/or support the coupling therebetween.
The subannular region 130 of the frame 110 can be and/or can form, for example, a cuff or collar along an end of the transannular region 112 opposite the supra-annular region 120. In some embodiments, the subannular region 130 is a lower or subannular portion of the transannular region 112 (e.g., the transannular region 112 and the subannular region 130 are monolithically and/or unitarily formed). Said another way, a lower or subannular portion of the transannular region 112 can form and/or include the subannular annular region 130. In other embodiments, the subannular region 130 is a separate and/or independent component that can be attached or coupled to a lower edge or portion of the transannular region 112, as described above with reference to the supra-annular region 120. In such embodiments, for example, the subannular region 130 can be a wire frame that is laser cut out of any suitable material such as a shape-memory or superelastic material like Nitinol, heat-set into a desired shape and/or configuration, covered by any suitable biocompatible material, and attached to a lower edge of the transannular region 112, as described above with reference to the supra-annular region. In some implementations, forming the subannular region 130 in such a manner can allow the subannular region 130 to bend, flex, fold, compress, and/or otherwise reconfigure substantially without plastically deforming and/or without fatigue that may result in failure or breaking of one or more portions thereof.
When the valve 100 is deployed within a human heart, the subannular region 130 can be and/or can form a ventricular collar that is shaped to conform to the native deployment location. In a tricuspid and/or mitral valve replacement, for example, the subannular region 130 or collar can have various portions configured to conform to the native valve and/or a portion of the ventricular ceiling surrounding the tricuspid and/or mitral valve, respectively. In some implementations, the subannular region 130 or at least a portion thereof can engage the ventricular ceiling surrounding the native annulus to secure the valve 100 in the native annulus, to stabilize the valve 100 in the annulus, to prevent dislodging of the valve 100, to sandwich or compress the native annulus or adjacent tissue between the supra-annular region 120 and the subannular region 130 (or lower portion of the transannular region 112), and/or to seal against blood leakage (perivalvular leakage and/or regurgitation during systole) around the frame 110.
The subannular region 130 of the frame 110 can be shaped and/or formed to include any number of features configured to engage native tissue, one or more other portions of the valve 100, one or more portions of the delivery system 180, one or more actuators (not shown), and/or the like. For example, as shown in
In some embodiments, the distal anchoring element 132 can optionally include a guidewire coupler 133 configured to selectively engage and/or receive a portion of a guidewire or a portion of a guidewire assembly (not shown). The guidewire coupler 133 is configured to allow a portion of the guidewire to extend through an aperture of the guidewire coupler 133, thereby allowing the valve 100 to be advanced over or along the guidewire during delivery and deployment. In some embodiments, the guidewire coupler 133 can selectively allow the guidewire to be advanced therethrough while blocking or preventing other elements and/or components such as a pusher or the like.
The distal anchoring element 132 is configured to engage a desired portion of the native tissue on a distal side of the native annulus to facilitate the seating, mounting, and/or deploying of the valve 100 in the annulus of the native valve. For example, in some implementations, the distal anchoring element 132 can be a projection or protrusion extending from the frame 110 (e.g., the subannular region 130 and/or the lower portion of the transannular region 112) and into a distal subannular position relative to the annulus (e.g., the RVOT for tricuspid valve replacement, and/or the like). In such implementations, the distal anchoring element 132 can be shaped and/or biased such that the distal anchoring element 132 exerts a force on the subannular tissue operable to at least partially secure, stabilize, and/or anchor the distal end portion of the valve 100 in the native annulus. In some embodiments, the distal anchoring element 132 can extend from the distal portion of the subannular region 130 (or lower portion of the transannular region 112) by about 10-40 mm.
The proximal anchoring element 134 is configured to engage subannular tissue on a proximal side of the native annulus to facilitate the seating, mounting, and/or deploying of the valve 100 in the annulus. In some embodiments, the proximal anchoring element 134 can be an anchoring element having a substantially fixed configuration. In such embodiments, the proximal anchoring element 134 can be flexible and/or movable through a relatively limited range of motion but otherwise has a single configuration. In some such embodiments, the proximal anchoring element 134 can extend from the proximal portion of the subannular region 130 (or lower portion of the transannular region 112) by about 10-40 mm.
In other embodiments, the proximal anchoring element 134 can be configured to transition, move, and/or otherwise reconfigure between two or more configurations. For example, the proximal anchoring element 134 can be transitioned between a first configuration in which the proximal anchoring element 134 extends from the subannular region 130 a first amount or distance and a second configuration in which the proximal anchoring element 134 extends from the subannular region 130 a second amount or distance, different from the first amount or distance. For example, in some embodiments, the proximal anchoring element 134 can have a first configuration in which the proximal anchoring element 134 is in a compressed, contracted, retracted, undeployed, folded, and/or restrained state (e.g., in a position that is near, adjacent to, and/or in contact with the transannular region 112 and/or the supra-annular region 120 of the frame 110), and a second configuration in which the proximal anchoring element 134 is in an expanded, extended, deployed, unfolded, and/or unrestrained state (e.g., extending away from the transannular region 112). In some implementations, the proximal anchoring element 134 in the expanded or deployed configuration (e.g., the second configuration) can extend from the transannular region 112 by about 10-40 mm and in the compressed or undeployed configuration (e.g., the first configuration) can be in contact with the transannular region 112 or can extend from the transannular region 112 by less than about 10 mm. Moreover, in some implementations, the proximal anchoring element 134 can be transitioned from the first configuration to the second configuration in response to actuation of an actuator, tensile member, portion of the delivery system 180, and/or the like, as described in further detail herein.
The frame 110 also includes the septal stability and/or anchoring element 136 (also referred to herein as “septal anchoring element”). The septal anchoring element 136 can be any suitable shape, size, and/or configuration such as any of those described herein with respect to specific embodiments. In some embodiments, for example, the septal anchoring element 136 can be, for example, integrally formed with the lower sidewall portion 130 of the frame 110 (e.g., can be a portion of the wireframe or laser-cut frame portion). In some embodiments, the septal anchoring element 136 can be formed at least in part by a wire-braid frame, a wire loop, an integrated frame section, a stent, and/or the like and can extend away from the transannular region 112 and/or the supra-annular region 120 (e.g., downward and outward).
The septal anchoring element 136 can be positioned along the septal side of the subannular region 130 (or lower portion of the transannular region 112) at any suitable position. For example, in some embodiments, the septal anchoring element 136 can be a wire frame or the like have a U-shape, an inverted parabolic shape, and/or the like such that a local minima of the septal anchoring element 136 is substantially centered along the septal side of the subannular region 130. In other embodiments, the septal anchoring element 136 can have the U-shape, the inverted parabolic shape, and/or the like but can be shifted in a proximal direction or in a distal direction (e.g., closer to the proximal anchoring element 132 and further from the distal anchoring element 134, or vice versa). In some embodiments, the septal anchoring element 136 can be substantially symmetric relative to an anteroposterior (AP) plane. In other embodiments, the septal anchoring element 136 can be asymmetric relative to the AP plane. In some embodiments, the septal anchoring element 136 can have an irregular or an at least semi-irregular shape that can be based, for example, on the anatomy of the heart in which the valve 100 is disposed. In some embodiments, the septal anchoring element 136 can extend from the septal portion of the subannular region 130 (or lower portion of the transannular region 112) by about 10-40 mm.
In some implementations, the septal anchoring element 136 is a lower anchoring element configured to engage subannular tissue of the ventricle to aid in the stability, anchoring, and/or securement of the valve 100 in the annulus. More specifically, the septal anchoring element 136 can be configured to engage subannular septal tissue, septal leaflet tissue, and/or any other suitable tissue at, near, and/or along the septum of the heart. In some implementations, when the valve 100 is at least partially inserted into the annulus, the septal anchoring element 136 can extend down the septal wall to pin the native septal leaflet away from, for example, the coapting leaflets of the prosthetic valve 100. In some implementations, the septal anchoring element can stabilize the valve against any intra-annular rolling forces and/or any intra-annular twisting forces that might affect a desired location or positioning of the prosthetic valve within the annulus, (e.g., tilted, angled, twisted, rolled, etc.). In some embodiments, the septal anchoring element 136 can be size, shaped, and/or configured for treating specific anatomical structures, avoiding interference with native electrical tissue or with the coronary sinus return, avoiding excessive cutting effect on the ventricular tissue, blocking native tissue from interfering with the functioning of the prosthetic valve 100 (e.g., leaflets of the flow control component 150), providing additional ventricular stability to prevent unwanted movement of the prosthetic valve 100 prior to in-growth, such as rolling, tilting, twisting or other unwanted migration of the implant, and/or the like.
As described above with reference to the proximal anchoring element 134, the septal anchoring element 136 can be an anchoring element that has a substantially fixed configuration or can be an anchoring element that can be reconfigurable between any number of configurations. For example, in some embodiments, the septal anchoring element 136 can be configured to transition, move, and/or otherwise reconfigure between a first configuration in which the septal anchoring element 136 extends from the subannular region 130 a first amount or distance and a second configuration in which the septal anchoring element 136 extends from the subannular region 130 a second amount or distance, different from the first amount or distance. In some implementations, the septal anchoring element 136 can be compressed, contracted, retracted, undeployed, folded, and/or restrained when in the first configuration (e.g., in a position that is near, adjacent to, and/or in contact with the transannular region 112 and/or the supra-annular region 120 of the frame 110), and can be expanded, extended, deployed, unfolded, actuated, and/or unrestrained when in the second configuration (e.g., extending away from the transannular region 112). Moreover, in some implementations, the septal anchoring element 136 can be transitioned from the first configuration to the second configuration in response to actuation of an actuator, tensile member, portion of the delivery system 180, and/or the like, as described in further detail herein.
Although not shown in
The flow control component 150 can refer in a non-limiting sense to a device for controlling fluid flow therethrough. In some embodiments, the flow control component 150 can be a leaflet structure having two, three, four, or more leaflets, made of flexible biocompatible material such a treated or untreated pericardium. The leaflets can be sewn or joined to a support structure such as an inner frame, which in turn, can be sewn or joined to the outer frame 110. The leaflets can be configured to move between an open and a closed or substantially sealed state to allow blood to flow through the flow control component 150 in a first direction through an inflow end of the valve 100 and block blood flow in a second direction, opposite to the first direction, through an outflow end of the valve 100. For example, the flow control component 150 can be configured such that the valve 100 functions, for example, as a heart valve, such as a tricuspid valve, mitral valve, aortic valve, or pulmonary valve, that can open to blood flowing during diastole from atrium to ventricle, and that can close from systolic ventricular pressure applied to the outer surface. Repeated opening and closing in sequence can be described as “reciprocating.”
The inner frame and/or portions or aspects thereof can be similar in at least form and/or function to the outer frame 110 and/or portions or aspects thereof. For example, the inner frame can be a laser cut frame formed from or of a shape-memory material such as Nitinol. Moreover, the inner frame can be compressible for delivery and configured to return to its original (uncompressed) shape when released (e.g., after delivery). In some embodiments, the inner frame can include and/or can form any suitable number of compressible, elastically deformable diamond-shaped or eye-shaped wire cells, and/or the like. The wire cells can have an orientation and cell geometry substantially orthogonal to an axis of the flow control component 150 to minimize wire cell strain when the inner frame is in a compressed configuration.
In some embodiments, the flow control component 150 and/or the inner frame thereof can have a substantially cylindrical or tubular shape when the valve 100 is in the expanded configuration (see e.g.,
As shown in
The flow control component 150 can be at least partially disposed in the central channel 114 such that the axis of the flow control component 150 that extends in the direction of blood flow through the flow control component 150 is substantially parallel to the central axis 104 of the frame 110. In some embodiments, the arrangement of the support frame 110 can be such that the flow control component 150 is centered within the central channel 114. In other embodiments, the arrangement of the support frame 110 can be such that the flow control component 150 is off-centered within the central channel 114. In some embodiments, the central channel 114 can have a diameter and/or perimeter that is larger than a diameter and/or perimeter of the flow control component 150. Although not shown in
In some embodiments, the flow control component 150 (or portions and/or aspects thereof) can be similar to, for example, any of the flow control components described in the '734 WIPO publication. Thus, the flow control component 150 and/or aspects or portions thereof are not described in further detail herein.
Referring back to
The delivery system 180, shown in
As described above, the valve 100 is compressible and expandable between the expanded configuration (
The valve 100 is compressed during delivery of the valve 100 and is configured to expand once released from the delivery catheter. More specifically, the valve 100 is configured for transcatheter orthogonal delivery to the desired location in the body (e.g., the annulus of a native valve), in which the valve 100 is compressed in an orthogonal or lateral direction relative to the dimensions of the valve 100 in the expanded configuration (e.g., along the central axis 104 and/or the lateral axis 106). During delivery, the longitudinal axis 102 of the valve 100 is substantially parallel to a longitudinal axis of the delivery catheter, as described in the '331 WIPO publication.
The valve 100 is in the expanded configuration prior to being loaded into the delivery system 180 and after being released from the delivery catheter and deployed or implanted (or ready to be deployed or implanted) at the desired location in the body. When in the expanded configuration shown in
When in the compressed configuration shown in
As shown in
In some implementations, the delivery of the valve 100 can include advancing a guidewire into the atrium of the human heart, through the native valve, and to a desired position within the ventricle (e.g., the RVOT). After positioning the guidewire, the delivery catheter can be advanced along and/or over the guidewire and into the atrium (e.g., via the IVC, the SVC, and/or a trans-septal access). In some embodiments, a guidewire coupler 133 of the valve 100 (e.g., included in or on the distal anchoring element 132) can be coupled to a proximal end portion of the guidewire and the valve 100 can be placed in the compressed configuration, allowing the valve 100 to be advanced along the guidewire and through a lumen of the delivery catheter, and into the atrium.
The deployment of the valve 100 can include placing the distal anchoring element 132 of the subannular region 130 in the ventricle (RV, LV) below the annulus while the remaining portions of the valve 100 are in the atrium (RA, LA). In some instances, the distal anchoring element 132 can be advanced over and/or along the guidewire to a desired position within the ventricle such as, for example, an outflow tract of the ventricle. For example, in some implementations, the valve 100 can be delivered to the annulus of the native tricuspid valve (TV) and at least a portion of the distal anchoring element 132 can be positioned in the RVOT. In other implementations, the valve 100 can be delivered to the annulus of the native mitral valve (MV) and at least a portion of the distal anchoring element 132 can be positioned in a subannular position distal to the annulus and/or in any other suitable position in which the distal anchoring element 132 can engage native tissue, leaflets, chordae, etc.
In some implementations, the prosthetic valve 100 can be temporarily maintained in a partially deployed state. For example, the valve 100 can be partially inserted into the annulus and held at an angle relative to the annulus to allow blood to flow from the atrium to the ventricle partially through the native valve annulus around the valve 100, and partially through the valve 100, which can allow for assessment of the valve function.
The valve 100 can be placed or seated in the annulus (PVA, MVA, AVA, and/or TVA) of the native valve (PV, MV, AV, and/or TV) such that the subannular region 130 (e.g., a ventricular collar) is disposed in a subannular position, the transannular region 112 of the valve frame 110 extends through the annulus, and the supra-annular region 120 (e.g., a atrial collar) remains in a supra-annular position. For example, in some embodiments, the delivery system 180, the actuator, and/or any other suitable member, tool, etc. can be used to push at least the proximal end portion of the valve 100 into the annulus. In addition, the septal anchoring element 136 can be at least partially inserted through the annulus prior to the valve 100 being fully seated in the annulus. In some implementations, the septal anchoring element 136 can be in contact with, for example, subannular septal tissue (e.g., the native septal wall, a native septal leaflet, and/or the like) as the valve 100 is seated in the annulus, thereby providing stability during the seating process (e.g., rolling, twisting, rotating, and/or spinning about a distal-proximal axis of the valve 100 and/or about an axis associated with, for example, the guidewire or guidewire assembly extending along the longitudinal length of the valve 100.
In some implementations, the proximal anchoring element 134 can be maintained in its first configuration as the valve 100 is seated in the annulus. For example, as described above, the proximal anchoring element 134 can be in a compressed, contracted, and/or retracted configuration in which the proximal anchoring element 134 is in contact with, adjacent to, and/or near the transannular region 112 and/or the supra-annular region 120 of the frame 110, which in turn, can limit an overall circumference of the subannular region 130 of the frame 110, thereby allowing the subannular region 130 and the transannular region 112 of the frame 110 to be inserted into and/or through the annulus.
Once seated, the proximal anchoring element 134 can be transitioned from its first configuration to its second configuration, as described in detail in the '978 WIPO publication. For example, in some implementations, a user can manipulate a portion of the delivery system to actuate the actuator. In some implementations, actuating the actuator can release and/or reduce an amount of tension within or more tethers, cables, connections, and/or portions of the actuator, thereby allowing the proximal anchoring element 134 to transition. Accordingly, once the valve 100 is seated in the annulus, the proximal anchoring element 134 can be placed in its second configuration in which the proximal anchoring element 134 contacts, engages, and/or is otherwise disposed adjacent to subannular tissue. In some embodiments, the septal anchoring element 136 similarly can be transitioned from a first configuration to a second configuration. In some implementations, placing at least one of the proximal anchoring element 134 and/or the septal anchoring element 136 can reduce an extent (e.g., size or diameter) of the subannular region 130 or lower portion of the transannular region 112 to allow the valve 100 to be inserted into and at least partially through the annulus. In such implementations, once the valve 100 is at least partially seated in the annulus, the proximal anchoring element 134 and/or the septal anchoring element 136 can then be transitioned from the first (e.g., compressed) configuration(s) to the second (e.g., extended) configuration(s) to stabilize, anchor, and/or secure the valve 100 in the annulus of the native valve.
Although not shown in
As described above, the distal anchoring element 132 can be configured to engage native tissue on a distal side of the annulus, the proximal anchoring element 134 can be configured to engage native tissue on a proximal side of the annulus (e.g., when in the second or expanded configuration), and the septal anchoring element 136 can be configured to engage native tissue of a septal side of the annulus (e.g., the septal wall or native septal leaflet tissue), thereby securely seating the valve 100 in the native annulus, as shown in
As shown, the valve 200 generally includes an annular support frame 210 and a flow control component 250. In addition, the valve 200 and/or at least the annular support frame 210 of the valve 200 includes one or more anchoring element. For example, the annular support frame 210 can include at least a septal stability and/or anchoring element 236, a distal anchoring element 232 and a proximal anchoring element 234. In some implementations, the septal stability and/or anchoring element 236, the distal anchoring element 232 and the proximal anchoring element 234 can all be lower anchoring elements. In other embodiments, the valve 200 and/or the annular support frame 210 can include a distal upper anchoring element and a proximal upper anchoring element for atrial anchoring.
The annular support frame 210 (also referred to herein as “tubular frame,” “valve frame,” “wire frame,” or “frame”) can have or can define an aperture 214 that extends along a central axis. The aperture 214 (e.g., a central axial lumen) can be sized and configured to receive the flow control component 250 across a diameter of the aperture 214. The frame 210 may have an outer circumferential surface for engaging native annular tissue that may be tensioned against an inner aspect of the native annulus to provide structural patency to a weakened native annular ring.
The frame 210 includes a cuff or collar 220 (e.g., a supra-annular region) and a tubular or transannular section 212. The cuff or collar 220 (referred to herein as “collar”) can be attached to and/or can form an upper edge of the frame 210. When the valve 200 is deployed within a human heart, the collar 220 can be an atrial collar. The collar 220 can be shaped to conform to the native deployment location. In a mitral replacement, for example, the collar 220 will be configured with varying portions to conform to the native valve. In one embodiment, the collar 220 will have a distal and proximal upper collar portion. The distal collar portion can be larger than the proximal upper collar portion to account for annular geometries, supra-annular geometries, and/or sub annular geometries.
The frame 210 may optionally have a separate atrial collar attached to the upper (atrial) edge of the frame 210, for deploying on the atrial floor that is used to direct blood from the atrium into the flow control component 250 and to seal against blood leakage (perivalvular leakage) around the frame 210. The frame 210 may also optionally have a separate ventricular collar (e.g., a subannular region) attached to the lower (ventricular) edge of the frame 210, for deploying in the ventricle immediately below the native annulus that is used to prevent regurgitant leakage during systole, to prevent dislodging of the valve 200 during systole, to sandwich or compress the native annulus or adjacent tissue against the atrial collar or collar 220, and/or optionally to attach to and support the flow control component 250. Some embodiments may have both an atrial collar and a ventricular collar, whereas other embodiments either include a single atrial collar, a single ventricular collar, or have no additional collar structure.
The frame 210 can be a ring, or cylindrical or conical tube, but may also have a side profile of a flat-cone shape, an inverted flat-cone shape (narrower at top, wider at bottom), a concave cylinder (walls bent in), a convex cylinder (walls bulging out), an angular hourglass, a curved, graduated hourglass, a ring or cylinder having a flared top, flared bottom, or both. The frame 210 may have a height in the range of about 5-60 mm, may have an outer diameter dimension, R, in the range of about 20-80 mm, and may have an inner diameter dimension in the range of about 21-79 mm, accounting for the thickness of the frame 210 (e.g., a wire material forming the frame 210).
The frame 210 is compressible for delivery and when released it is configured to return to its original (uncompressed) shape. The frame 210 may be compressed for transcatheter delivery and may be expandable using a transcatheter expansion balloon. In other implementations, the frame 210 can include and/or can be formed of a shape-memory element allowing the frame 210 to be self-expanding. In some instances, suitable shape-memory materials can include metals and/or plastics that are durable and biocompatible. For example, the frame 210 can be made from super elastic metal wire, such as a Nitinol wire or other similarly functioning material. The frame 210 may be constructed as a braid, wire, or laser cut wire frame. The frame 210 may also have and/or form additional functional elements (e.g., loops, anchors, etc.) for attaching accessory components such as biocompatible covers, tissue anchors, releasable deployment and retrieval control guides, knobs, attachments, rigging, and so forth.
As described above, the frame 210 and/or the valve 200 can include at least the distal anchoring element 232 and the proximal anchoring element 234. The distal and proximal anchoring elements 232 and 234 can be, for example, lower anchoring elements (e.g., coupled to and/or included in a lower portion or subannular region of the frame 210). In some embodiments, the frame 210 and/or the valve 200 can also optionally include one or more of a distal upper anchoring element and a proximal upper anchoring element. The anchoring elements 232 and 234 of the valve 200 can be configured to engage a desired portion of the annular tissue to mount the frame 210 to the annulus of the native valve in which the valve 200 is deployed, as described in further detail herein. The anchoring elements 232 and 234 of the valve 200 and/or the frame 210 can be any suitable shape, size, and/or configuration. Moreover, certain aspects, features, and/or configurations of at least the distal and proximal anchoring elements 232 and 234 are described below reference to specific embodiments.
The frame 210 can also include the septal stability and/or anchoring element 236 (also referred to herein as “septal anchoring element”). The septal anchoring element 236 can be any suitable shape, size, and/or configuration such as any of those described herein with respect to specific embodiments. In some embodiments, for example, the septal anchoring element 236 can be, for example, integrally formed with the lower sidewall portion 230 of the frame 210 (e.g., can be a portion of the wireframe or laser-cut frame portion). In some implementations, the septal anchoring element 236 (e.g., leaflet brace or the like) is a lower anchoring element configured to engage subannular tissue of the ventricle to aid in the securement of the valve 200 in the annulus. More specifically, the septal anchoring element 236 can be configured to engage subannular septal tissue, septal leaflet tissue, and/or any other suitable tissue at, near, and/or along the septum of the heart.
In some implementations, the proximal anchoring element 234 can be configured to transition between a first configuration in which the proximal anchoring element 234 is maintained in a compressed, undeployed, and/or restrained state, to a second configuration in which the proximal anchoring element 234 is expanded, extended, deployed, and/or unrestrained. More specifically, the proximal anchoring element 234 when in the first configuration can be maintained in a first position that is in contact with, adjacent to, and/or otherwise near the transannular section 250 of the valve frame 210, and when in the second configuration, can be released to a second position that extends away from the transannular section 250 of the frame 210. Said another way, the second position proximal anchoring element 234 can be further from the transannular section 250 than the first position of the proximal anchoring element 234.
In some embodiments, the valve 200 and/or the frame 210 can include a feature, member, mechanism, etc. configured to at least temporarily retain the proximal anchoring element 234 in the first configuration. For example, as shown in
The flow control component 250 can refer in a non-limiting sense to a device for controlling fluid flow therethrough. In some embodiments, the flow control component 250 can be a leaflet structure having two, three, four, or more leaflets made of flexible biocompatible material such a treated or untreated pericardium. The flow control component 250 with leaflets can be sewn or joined to a support structure and/or can be sewn or joined to the frame 210. The flow control component 250 can be mounted within the frame 210 and configured to permit blood flow in a first direction through an inflow end of the valve and block blood flow in a second direction, opposite the first direction, through an outflow end of the valve. For example, the flow control component 250 can be configured such that the valve 200 functions, for example, as a heart valve, such as a tricuspid valve, mitral valve, aortic valve, or pulmonary valve, that can open to blood flowing during diastole from atrium to ventricle, and that can close from systolic ventricular pressure applied to the outer surface. Repeated opening and closing in sequence can be described as “reciprocating.”
The flow control component 250 is contemplated to include a wide variety of (bio)prosthetic artificial valves, including ball valves (e.g., Starr-Edwards), bileaflet valves (St. Jude), tilting disc valves (e.g., Bjork-Shiley), stented pericardium heart-valve prosthesis' (bovine, porcine, ovine) (Edwards line of bioprostheses, St. Jude prosthetic valves), as well as homograft and autograft valves. Bioprosthetic pericardial valves can include bioprosthetic aortic valves, bioprosthetic mitral valves, bioprosthetic tricuspid valves, and bioprosthetic pulmonary valves. In some implementations, a suitable commercially available valve (flow control component 250) can be received or accepted by and/or otherwise mounted in the frame 210. Commercially available valves (flow control components 250) may include, for example, a Sapien, Sapien 3, or Sapien XT from Edwards Lifesciences, an Inspiris Resilia aortic valve from Edwards Lifesciences, a Masters HP 15 mm valve from Abbott, a Lotus Edge valve from Boston Scientific, a Crown PRT leaflet structure from Livanova/Sorin, a valve from the Carbomedics family of valves from Sorin, or other flow control component(s), or a flexible reciprocating sleeve or sleeve-valve.
In one embodiment,
Referring now to
The method 10 includes disposing in the atrium of the heart a distal end of a delivery catheter having disposed in a lumen thereof the prosthetic heart valve in the compressed configuration, at 11. For example, for tricuspid valve or pulmonary valve replacement, the atrium can be accessed, for example, through the inferior vena cava (IVC) via the femoral vein or through the superior vena cava (SVC) via the jugular vein. As another example, for mitral valve the atrium can be accessed through a trans-atrial approach (e.g., fossa ovalis or lower), via the IVC-femoral or the SVC jugular approach. When the distal end of the delivery catheter is disposed in a desired position in the atrium of the heart, the prosthetic valve in the compressed configuration can be advanced (e.g., along a guidewire) through the lumen of the delivery catheter. As described above, the prosthetic heart valve can be a side-deliverable prosthetic heart valve such that an axis extending through the inflow end and the outflow end of the prosthetic heart valve is substantially orthogonal to a lengthwise axis extending through the lumen of the delivery catheter. Said another way a longitudinal axis extending through the prosthetic valve is substantially parallel to the lengthwise axis extending through the lumen of the delivery catheter, as described in detail above with reference to the valve 100.
The prosthetic heart valve is released from the lumen of the delivery catheter such that the prosthetic heart valve transitions from the compressed configuration to the expanded configuration, at 12. In some implementations, the prosthetic heart valve can be advanced through the delivery catheter such that the distal anchoring element is distal to the remaining portions of the valve and thus, is first released from the distal end of the delivery catheter. As the prosthetic valve is further advances, the valve and/or at least the valve frame is allowed to expand (e.g., it is no longer constrained by the inner surface of the delivery catheter. In some implementations, the prosthetic valve can be in its expanded configuration when the prosthetic valve is completely released or otherwise outside of the delivery catheter (e.g., disposed in the atrium of the heart).
In some implementations, at least a portion of the prosthetic valve can be inserted into the annulus of the native valve while portions of the prosthetic valve are still being released from the delivery catheter. For example, for tricuspid valve replacement, the distal anchoring element can be inserted through the annulus and into a right ventricular outflow track (RVOT) as the prosthetic valve is released from the delivery catheter. As another example, for mitral valve replacement, the distal anchoring element can be inserted through the annulus and into a subannular position distal to the annulus as the prosthetic valve is released from the delivery catheter.
At least a portion of the prosthetic heart valve is seated in the annulus of the native valve, at 13. In some implementations, the seating of the prosthetic valve in the annulus can include inserting the proximal anchoring element and the septal anchoring element into and/or through the annulus prior to or as the prosthetic valve is being seated in the annulus. In addition, the method 10 includes placing the septal anchoring element in contact with at least one of a native septal wall or a septal leaflet area to stabilize the prosthetic heart valve in the annulus when the prosthetic heart valve is seated in the annulus, at 14. For example, the septal anchoring element can stabilize the prosthetic heart valve against at least one of intra-annular rolling forces or intra-annular twisting forces within the annulus during deployment or seating of the valve in the annulus or after the valve is deployed and/or secured in the annulus.
In some implementations, seating the prosthetic valve in the annulus is such that the proximal anchoring element is placed in contact with subannular tissue on the proximal side of the annulus. In some implementations, the proximal anchoring element is configured to transition from a first configuration to a second configuration after seating the prosthetic heart valve in the annulus to contact the proximal subannular tissue. In some implementations, the proximal anchoring element is transitioned from the first configuration to the second configuration by manipulating a tensile member coupled to the valve frame.
In some implementations, the septal anchoring element similarly can be configured to transition from a first configuration to a second configuration after the prosthetic valve in the annulus. In other implementations, the septal anchoring element can be an anchoring element having a single or substantially fixed configuration. The septal anchoring element can have any suitable configuration indicated, in some implementations, for treating specific anatomical structures, avoiding interference with native electrical tissue or with the coronary sinus return, avoiding excessive cutting effect on the ventricular tissue, blocking native tissue from interfering with the functioning of the prosthetic valve (e.g., leaflets of a flow control component), providing additional ventricular stability to prevent unwanted movement of the prosthetic valve prior to in-growth, such as rolling, tilting, or other unwanted migration of the implant, and/or the like, as described above with reference to the septal anchoring elements described above with reference to specific embodiments.
While various embodiments have been described above, it should be understood that they have been presented by way of example only, and not limitation. Likewise, it should be understood that the specific terminology used herein is for the purpose of describing particular embodiments and/or features or components thereof and is not intended to be limiting. Various modifications, changes, and/or variations in form and/or detail may be made without departing from the scope of the disclosure and/or without altering the function and/or advantages thereof unless expressly stated otherwise. Functionally equivalent embodiments, implementations, and/or methods, in addition to those enumerated herein, will be apparent to those skilled in the art from the foregoing descriptions and are intended to fall within the scope of the disclosure.
Where schematics and/or embodiments described above indicate certain components arranged in certain orientations or positions, the arrangement of components may be modified. Although various embodiments have been described as having particular features and/or combinations of components, other embodiments are possible having a combination of any features and/or components from any of embodiments described herein, except mutually exclusive combinations. The embodiments described herein can include various combinations and/or sub-combinations of the functions, components, and/or features of the different embodiments described.
Where methods described above indicate certain events occurring in certain order, the ordering of certain events may be modified. Additionally, certain of the events may be performed concurrently in a parallel process when possible, as well as performed sequentially as described above. While methods have been described as having particular steps and/or combinations of steps, other methods are possible having a combination of any steps from any of methods described herein, except mutually exclusive combinations and/or unless the context clearly states otherwise.
This application is a continuation of International Patent Application Serial No. PCT/US2021/013570, filed Jan. 15, 2021, entitled “Ventricular Stability Elements for Side-Deliverable Prosthetic Heart Valve and Methods of Delivery,” which claims priority to and the benefit of U.S. Provisional Patent Application Ser. No. 62/962,902, filed Jan. 17, 2020, entitled “Ventricular Stability Tab for Side-Delivered Transcatheter Heart Valve and Methods of Delivery,” the disclosures of which are incorporated herein by reference in their entireties.
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| Number | Date | Country | |
|---|---|---|---|
| 20210220126 A1 | Jul 2021 | US |
| Number | Date | Country | |
|---|---|---|---|
| 62962902 | Jan 2020 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | PCT/US2021/013570 | Jan 2021 | US |
| Child | 17154438 | US |
