Patent Grant
11076956
Provided by Application Data Sheet per USPTO rules.
Provided by Application Data Sheet per with USPTO rules.
Provided by Application Data Sheet per with USPTO rules.
Provided by Application Data Sheet per USPTO rules.
Provided by Application Data Sheet per USPTO rules.
The invention relates to an extendable proximal, distal, and anterior anchoring tabs for a side-delivered transcatheter mitral valve replacement (A61F2/2412).
In 1952 surgeons implanted the first mechanical heart valve, a ball valve that could only be placed in the descending aorta instead of the heart itself. For this reason it did not fully correct the valve problem, only alleviate the symptoms. However it was a significant achievement because it proved that synthetic materials could be used to create heart valves.
In 1960, a new type of valve was invented and was successfully implanted. This valve is the Starr-Edwards ball valve, named after its originators. This valve was a modification of Hufnagel's original valve. The ball of the valve was slightly smaller and caged from both sides so it could be inserted into the heart itself.
The next development was tilting disc technology which was introduced in the late 1960s. These valves were a great improvement over the ball designs. The tilting dic technology allowed blood to flow in a more natural way while reducing damage to blood cells from mechanical forces. However, the struts of these valves tended to fracture from fatigue over time. As of 2003, more than 100,000 Omniscience and 300,000 Hall-Kaster/Medtronic-Hall tilting disc valves were implanted with essentially no mechanical failure.
In 1977, bi-leaflet heart valves were introduced by St. Jude. Similar to a native heart valve, blood flows directly through the center of the annulus of pyrolytic carbon valves mounted within nickel-titanium housing which makes these valves superior to other designs. However, a downside of this design is that it allows some regurgitation. A vast majority of mechanical heart valves used today have this design. As of 2003, more than 1.3 million St. Jude valves were deployed and over 500,000 Carbomedics valves with no failures to leaflets or housing. It should be noted that the human heart beats about 31 million times per year.
Development continues with compressible valves that are delivered via a catheter instead of requiring the trauma and complications of open heart surgery. This means that a cardiologist trained in endoscopy can, in theory, deploy a heart valve replacement during an outpatient procedure. However, transcatheter valves are often delivered by perforating the apex of the heart to access the ventricle, and the perforation is often used to anchor an annular valve replacement.
Additionally, a problem with stent-style replacement valves is that they often continue to have the regurgitation or leakage problems of prior generations of valves, as well as require expensive materials engineering in order to cope with the 100's of millions of cycles encountered during just a few years of normal heart function. Accordingly, there is still a need for alternative and simpler solutions to addressing valve-related heart pathologies.
The present invention is directed to a proximal anchoring tab for a side delivered prosthetic mitral valve having an elongated distal tab, where the proximal tab anchors the proximal side of the prosthetic valve using a tab or loop deployed to the A3-P3 (proximal) commissure area of the mitral valve, and wherein the elongated distal tab is extended around the posterior leaflet and/or chordae using a guide wire to capture native mitral leaflet and/or chordae tissue and where withdrawing the guide wire contracts the tab and pins the native posterior tissue against the subannular posterior-side sidewall of the prosthetic valve.
Use of an side-delivered transcatheter mitral valve replacement allows a very large diameter valve to be delivered and deployed from the inferior vena cava trans-septally into the mitral valve, e.g. has a height of about 5-60 mm and a diameter of about 25-80 mm, without requiring an oversized diameter catheter and without requiring delivery and deployment from a catheter at an acute angle of approach.
Side-delivered mitral valves have a collapsible outer frame and collapsible inner flow control component that are foldable along a horizontal axis (z-axis, axis parallel to central axis of delivery catheter) and compressible along a vertical axis (y-axis)
Accordingly, the present invention is directed to a side delivered mitral valve having a proximal tab anchoring tab component, comprising:
(i) a self-expanding annular outer support frame, said annular support frame having a central channel and an outer perimeter wall circumscribing a central vertical y-axis in an expanded configuration, said outer perimeter wall having an anterior side, a posterior side, a distal side and a proximal side, said outer support frame covered with a polyester mesh, pericardium-based material or both;
(ii) a subannular proximal tab mounted on the proximal side of the outer perimeter wall, said proximal tab comprising a wire form extending from 5-20 mm away from the outer perimeter wall and covered with a polyester mesh, pericardium-based material or both;
(iii) a collapsible inner flow control component mounted within the annular support frame,
the collapsible (inner) flow control component having a leaflet frame with 2-4 flexible leaflets mounted thereon, wherein the 2-4 leaflets are configured to permit blood flow in a first direction through an inflow end of the flow control component and block blood flow in a second direction, opposite the first direction, through an outflow end of the flow control component;
the outer support frame and the leaflet frame comprising diamond- or eye-shaped wire cells made from heat-set Nitinol and configured to be foldable along a z-axis from a rounded or cylindrical configuration to a flattened cylinder configuration having a width of 8-12 mm, and compressible along a vertical axis y-axis to a shortened configuration having a height of 8-12 mm;
(iv) a distal anchoring tab mounted on the distal side of the annular support frame, wherein the tab is an elongated member attached at a first end to the perimeter wall of the annular support frame and has an unattached second end that is heat set to a folded position to press against the perimeter wall, wherein the tab engages with a guide wire during deployment to an opened configuration, wherein the tab in the opened configuration tracks over the guide wire allowing the tab to capture native posterior P1, P2 and/or P3 leaflet and/or chordae, and upon withdrawal of the guide wire releasing the tab to the folded position, the native posterior leaflet and/or chordae are sandwiched between the folded tab and the perimeter wall of the annular support frame;
wherein the valve is compressible to a compressed configuration for introduction into the body using a delivery catheter for implanting at a desired location in the body, said compressed configuration is oriented along a horizontal x-axis at an intersecting angle of between 45-135 degrees to the central vertical y-axis, and expandable to an expanded configuration having a horizontal x-axis at an intersecting angle of between 45-135 degrees to the central vertical y-axis,
wherein the horizontal x-axis of the compressed configuration of the valve is substantially parallel to a length-wise cylindrical axis of the delivery catheter, and
wherein the valve has a height of about 5-60 mm and a diameter of about 25-80 mm.
In another preferred embodiment, the invention includes the valve, and further comprises (v) an integrated subannular A2 anterior leaflet anchoring system mounted on the anterior side of the outer perimeter wall, wherein the system comprises an A2 clip sleeve having a pre-loaded A2 clip disposed within a lumen of the sleeve, the pre-loaded A2 clip comprising an elongated loop or tab, wherein said A2 clip is compressed or folded within the sleeve and a distal portion of the A2 clip presses against the perimeter wall when said A2 clip is compressed or folded, and wherein said A2 clip is extended or unfolded when released from the sleeve along the cylindrical axis or extended or unfolded when actuated with a guide wire during deployment, and when said A2 clip is in extended or unfolded position allows the A2 clip to capture native leaflet and/or native chordae, and upon retracting or re-folding the A2 clip, the native leaflet and/or native chordae are sandwiched between the A2 clip and the perimeter wall of the annular support frame.
In another preferred embodiment, the invention includes the valve wherein the proximal tab and annular support frame are comprised of a plurality of compressible wire cells having an orientation and cell geometry substantially orthogonal to the central vertical axis to minimize wire cell strain when the annular support frame is configured in a vertical compressed configuration, a rolled compressed configuration, or a folded compressed configuration.
In another preferred embodiment, the invention includes the valve wherein the annular support frame has a lower body portion and an upper collar portion, wherein the lower body portion in an expanded configuration forms a shape selected from a funnel, cylinder, flat cone, or circular hyperboloid.
In another preferred embodiment, the invention includes the valve wherein said proximal tab and annular support frame are comprised of a braided, wire, or laser-cut wire frame.
In another preferred embodiment, the invention includes the valve wherein the annular support frame has a side profile of a flat cone shape having a diameter R of 40-80 mm, a diameter r of 20-60 mm, and a height of 5-60 mm.
In another preferred embodiment, the invention includes the valve wherein the annular support frame has an inner surface and an outer surface, said inner surface and said outer surface covered with a biocompatible material selected from the following consisting of: the inner surface covered with pericardial tissue, the outer surface covered with a woven synthetic polyester material, and both the inner surface covered with pericardial tissue and the outer surface covered with a woven synthetic polyester material.
In another preferred embodiment, the invention includes the valve wherein the annular support frame has a side profile of an hourglass shape having a top diameter R1 of 40-80 mm, a bottom diameter R2 of 50-70 mm, an internal diameter r of 20-60 mm, and a height of 5-60 mm.
In another preferred embodiment, the invention includes the valve wherein the valve in an expanded configuration has a central vertical y-axis that is substantially parallel to the first direction.
In another preferred embodiment, the invention includes the valve wherein the flow control component has an internal diameter of 20-60 mm and a height of 10-40 mm, and a plurality of leaflets of pericardial material joined to form a rounded cylinder at an inflow end and having a flat closable aperture at an outflow end.
In another preferred embodiment, the invention includes the valve wherein the flow control component is supported with one or more longitudinal supports integrated into or mounted upon the flow control component, the one or more longitudinal supports selected from rigid or semi-rigid posts, rigid or semi-rigid ribs, rigid or semi-rigid battons, rigid or semi-rigid panels, and combinations thereof.
In another preferred embodiment, the invention includes the valve wherein the distal anchoring tab is comprised of wire loop, a wire frame, a laser cut frame, an integrated frame section, or a stent, and the distal anchoring tab extends from about 10-40 mm away from the distal side of the annular support frame.
In another preferred embodiment, the invention includes the valve wherein the proximal anchoring tab is comprised of wire loop, a wire frame, a laser cut frame, an integrated frame section, or a stent, and the distal anchoring tab extends from about 10-40 mm away from the proximal side of the annular support frame.
In another preferred embodiment, the invention includes the valve and further comprises an upper distal anchoring tab attached to a distal upper edge of the annular support frame, the upper distal anchoring tab comprised of wire loop, a wire frame, a laser cut frame, an integrated frame section, or a stent, and extends from about 2-20 mm away from the annular support frame.
In another preferred embodiment, the invention includes the valve comprising at least one tissue anchor connected to the annular support frame for engaging native tissue.
In another preferred embodiment, the invention includes the valve wherein the outer perimeter wall comprises a front wall portion that is a first flat panel and a back wall portion that is a second flat panel, and wherein a proximal fold area and a distal fold area each comprise a sewn seam, a fabric panel, a rigid hinge, or a flexible fabric span without any wire cells.
In another preferred embodiment, the invention includes the valve wherein the annular support frame is comprised of compressible wire cells selected from the group consisting 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.
In another preferred embodiment, the invention includes a method for side delivery of implantable prosthetic mitral valve to a patient, the method comprising the steps:
withdrawing the guide wire to a second A2 clip release position to release the A2 clip to the open position allowing the A2 clip to capture native leaflet and/or native chordae, and sandwich the native leaflet and/or chordae between the A2 clip and the perimeter wall of the annular support frame.
In another preferred embodiment, the invention includes the method wherein releasing the valve from the delivery catheter is selected from the steps consisting of: (i) pulling the valve out of the delivery catheter using a rigid elongated pushing rod/draw wire that is releasably connected to the distal side of the valve, wherein advancing the pushing rod away from the delivery catheter pulls the compressed valve out of the delivery catheter, or (ii) pushing the valve out of the delivery catheter using a rigid elongated pushing rod that is releasably connected to the proximal side of the valve, wherein advancing the pushing rod out of from the delivery catheter pushes the compressed valve out of the delivery catheter.
In another preferred embodiment, the invention includes the method comprising the additional step of anchoring one or more tissue anchors attached to the valve into native tissue.
In another preferred embodiment, the invention includes the method comprising the additional step of rotating the heart valve prosthesis using a steerable catheter along an axis parallel to the plane of the valve annulus.
The invention is directed to a transcatheter mitral heart valve replacement that is a low profile, orthogonally delivered implantable prosthetic heart valve having an ring-shaped or annular support frame, an inner 2- or 3-panel sleeve, and an elongated sub-annular distal anchoring tab extending around and capturing the posterior leaflet.
The embodiments herein and the various features and 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. The examples used herein are intended merely to facilitate an understanding of ways in which the embodiments herein may be practiced and to further enable those of skill in the art to practice the embodiments herein. Accordingly, the examples should not be construed as limiting the scope of the embodiments herein.
Rather, these embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the invention to those skilled in the art. Like numbers refer to like elements throughout. As used herein the term “and/or” includes any and all combinations of one or more of the associated listed items.
The terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the full scope of the invention. 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. It will be further understood that the terms “comprises” and/or “comprising,” when used in this specification, specify the presence of stated features, integers, steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, integers, steps, operations, elements, components, and/or groups thereof.
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. Nothing in this disclosure is to be construed as an admission that the embodiments described in this disclosure are not entitled to antedate such disclosure by virtue of prior invention. As used in this document, the term “comprising” means “including, but not limited to.”
Many modifications and variations can be made without departing from its spirit and scope, as will be apparent to those skilled in the art. Functionally equivalent methods and apparatuses within the scope of the disclosure, in addition to those enumerated herein, will be apparent to those skilled in the art from the foregoing descriptions. Such modifications and variations are intended to fall within the scope of the appended claims. The present disclosure is to be limited only by the terms of the appended claims, along with the full scope of equivalents to which such claims are entitled. It is to be understood that this disclosure is not limited to particular methods, reagents, compounds, compositions or biological systems, which can, of course, vary. It is also to be understood that the terminology used herein is for the purpose of describing particular embodiments only, and is not intended to be limiting.
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.
It will be understood by those within the art that, 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,” the term “includes” should be interpreted as “includes but is not limited to,” etc.). It will be further understood by those within the art that virtually any disjunctive word and/or phrase presenting two or more alternative terms, whether in the description, claims, or drawings, should be understood to contemplate the possibilities of including one of the terms, either of the terms, or both terms. For example, the phrase “A or B” will be understood to include the possibilities of “A” or “B” or “A and B.”
In addition, where features or aspects of the disclosure are described in terms of Markush groups, those skilled in the art will recognize that the disclosure is also thereby described in terms of any individual member or subgroup of members of the Markush group.
As will be understood by one skilled in the art, for any and all purposes, such as in terms of providing a written description, all ranges disclosed herein also encompass any and all possible subranges and combinations of subranges thereof. Any listed range can be easily recognized as sufficiently describing and enabling the same range being broken down into at least equal subparts. As will be understood by one skilled in the art, a range includes each individual member.
Side-Delivery or Orthogonal Delivery
In the description and claims herein, the terms “side-delivered”, “side-delivery”, “orthogonal”, “orthogonally delivered” and so forth are used to describe that the valves of the present invention are compressed and delivered at a roughly 90 degree angle compared to traditional transcatheter heart valves. Orthogonal delivery is a transverse delivery where a perimeter distal sidewall exits the delivery catheter first, followed by the central aperture, followed by the proximal sidewall.
Traditional valves have a central cylinder axis that is parallel to the length-wise axis of the delivery catheter and are deployed from the end of the delivery catheter and expanded radially outward from the central annular axis, in a manner akin to pushing a closed spring-loaded umbrella out of a sleeve to make it spring open. However, the valves of the present invention are compressed and delivered in a sideways manner. To begin with the shape of the expanded valve is that of a large diameter shortened cylinder with an extended collar or cuff. The valves are compressed, in one preferred embodiment, where the central axis of the valve is roughly perpendicular to (orthogonal to) the length-wise axis of the delivery catheter. In one preferred embodiment, the valves are compressed vertically, similar to collapsing the height of a cylinder accordion-style from taller to shorter, and the valves are also compressed by folding a front panel against a back panel. In another preferred embodiment, the valves may be compressed by rolling.
Traditional valves can only be expanded as large as what the internal diameter of the delivery catheter will allow. Efforts to increase the expanded diameter of traditional valves have run into the problems of trying to compress too much material and structure into too little space.
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 ranging from 75 to 105 degrees. The intersecting angle or orthogonal angle refers to both (i) the relationship between the length-wise cylindrical axis of the delivery catheter and the long-axis of the compressed valve of the invention, where the long-axis is perpendicular to the central cylinder axis of traditional valves, and (ii) the relationship between the long-axis of the compressed or expanded valve of the invention and the axis defined by the blood flow through the prosthetic heart valve where the blood is flowing, eg. from one part of the body or chamber of the heart to another downstream part of the body or chamber of the heart, such as from an atrium to a ventricle through a native annulus.
Transcatheter
In the description and claims herein, the term “transcatheter” is used to define the process of accessing, controlling, and delivering a medical device or instrument within the lumen of a catheter that is deployed into a heart chamber, as well as an item that has been delivered or controlled by such as process. Transcatheter access is known to include via femoral artery and femoral vein, via brachial artery and vein, via carotid and jugular, via intercostal (rib) space, and via sub-xyphoid. Transcatheter can be synonymous with transluminal and is functionally related to the term “percutaneous” as it relates to delivery of heart valves.
In preferred embodiments of the invention, the transcatheter approach includes (i) advancing to the mitral valve or pulmonary artery of the heart through the inferior vena cava via the femoral vein, (ii) advancing to the mitral valve or pulmonary artery of the heart through the superior vena cava via the jugular vein, (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.
Annular Support Frame
In the description and claims herein, the term “annular support frame”, and also “wire frame” or “flange or “collar” refers to a three-dimensional structural component that is seated within a native valve annulus and is used as a mounting element for a leaflet structure, a flow control component, or a flexible reciprocating valve.
In a preferred embodiment, the annular support frame is a self-expanding annular support frame, having a central channel and an outer perimeter wall circumscribing a central vertical axis in an expanded configuration. The perimeter wall encompasses both the collar and the lower body portions.
The perimeter wall can be further defined as having a front wall portion and a back wall portion, which are connected along a near side (to the IVC) or proximal side to a proximal fold area, and connected along a far or distal side to a distal fold area.
This front wall portion can be further defined as having a front upper collar portion and a front lower body portion, and the the back wall portion can be further defined as having a back upper collar portion and a back lower body portion.
The annular (outer) support frame has 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.
Since the outer frame is preferably made of superelastic metal or alloy such as Nitinol, the frame is compressible. Preferably, the outer frame is constructed of a plurality of compressible wire cells having a orientation and cell geometry substantially orthogonal to the central vertical axis to minimize wire cell strain when the annular support frame when configured in a vertical compressed configuration, a rolled compressed configuration, or a folded compressed configuration.
Annular Support Frame Structure
The annular support frame can be a ring, or cylindrical or conical tube, made from a durable, biocompatible structural material such as Nitinol or similar alloy, wherein the annular support frame is formed by manufacturing the structural material as a braided wire frame, a laser-cut wire frame, or a wire loop. The annular support frame is about 5-60 mm in height, has an outer diameter dimension, R, of 30-80 mm, and an inner diameter dimension of 31-79 mm, accounting for the thickness of the wire material itself. As stated, the annular support frame can have a side-profile of a ring shape, cylinder shape, conical tube shape, 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. In one preferred embodiment, the annular support frame used in the prosthetic heart valve deployed in the mitral annulus may have a complex shape determined by the anatomical structures where the valve is being mounted. For example, in the mitral annulus, the circumference of the mitral valve may be a rounded ellipse, the septal wall is known to be substantially vertical, and the mitral is known to enlarge in disease states. Accordingly, a prosthetic heart valve may start in a roughly tubular configuration, and be heat-shaped to provide an upper atrial cuff or flange for atrial sealing and a lower trans-annular tubular or cylindrical section having 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.
Annular Support Frame Covering
The annular support frame is optionally internally or externally covered, partially or completely, with a biocompatible material such as pericardium. The annular support frame may also be optionally externally covered, partially or completely, with a second biocompatible material such as polyester or Dacron®.
Annular Support Frame Purpose
The annular support frame has a central axial lumen where a prosthetic heart valve or flow-control structure, such as a reciprocating compressible sleeve, is mounted across the diameter of the lumen. The annular support frame is also tensioned against the inner aspect of the native annulus and provides structural patency to a weakened annular ring.
Annular Support Frame Optional Collars
The annular support frame may optionally have a separate atrial collar attached to the upper (atrial) edge of the frame, for deploying on the atrial floor, that is used to direct blood from the atrium into the sleeve and to seal against blood leakage around the annular support frame. The annular support frame may also optionally have a separate ventricular collar attached to the lower (ventricular) edge of the frame, for deploying in the ventricle immediately below the native annulus that is used to prevent regurgitant leakage during systole, to prevent dislodging of the device during systole, to sandwich or compress the native annulus or adjacent tissue against the atrial collar, and optionally to attach to and support the sleeve/conduit.
Annular Support Frame Delivery
The annular support frame may be compressed for transcatheter delivery and may be expandable as a self-expandable shape-memory element or using a transcatheter expansion balloon. Some embodiments may have both an atrial collar and a ventricular collar, whereas other embodiments within the scope of the invention include prosthetic heart valves having either a single atrial collar, a single ventricular collar, or having no additional collar structure.
Frame Material
Preferably, the frame is made from a superelastic metal component, such as laser-cut Nitinol tube, or flat sheet or other similarly functioning material such as braided wire. The material may be used for the frame/stent, for the collar, and/or for anchors. It is contemplated as within the scope of the invention to use other shape memory alloys, as well as polymer composites including composites containing carbon nanotubes, carbon fibers, metal fibers, glass fibers, and polymer fibers. It is contemplated that the frame may be constructed as a braid, wire, or laser cut frame. Laser cut frames are preferably made from Nitinol, but also without limitation made from stainless steel, cobalt chromium, titanium, and other functionally equivalent metals and alloys.
One key aspect of the frame design is that it be compressible and when released have the stated property that it returns to its original (uncompressed) shape. This requirement limits the potential material selections to metals and plastics that have shape memory properties. With regards to metals, Nitinol has been found to be especially useful since it can be processed to be austenitic, martensitic or super elastic. Martensitic and super elastic alloys can be processed to demonstrate the required mechanical behavior.
Laser Cut
One possible construction of the wire frame envisions the laser cutting of a thin, isodiametric Nitinol tube. The laser cuts form regular cutouts in the thin Nitinol tube. In one preferred embodiment, the Nitinol tube expands to form a three-dimensional structure formed from diamond-shaped cells. The structure may also have 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.
Secondarily the tube is thermo-mechanically processed using industry standard Nitinol shape forming methods. The treatment of the wire frame in this manner will form a device that has shape memory properties and will readily revert to the memory shape once deployed.
Braided Wire
Another possible construction of the wire frame envisions utilizing simple braiding techniques using a Nitinol wire and a simple braiding fixture. The wire is wound on the braiding fixture in a pattern until an isodiametric tube is formed. Secondarily, the braided wire frame is placed on a shaping fixture and processed using industry standard Nitinol shape forming methods.
Flow Control Component
In the description and claims herein, the term “flow control component” refers 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”.
Tissue Anchor
In the description and claims herein, the term “tissue anchor” or “plication tissue anchor” or “secondary tissue anchor”, or “dart” or “pin” refers to a fastening device that connects the upper atrial frame to the the native annular tissue, usually at or near the periphery of the collar. The anchor may be positioned to avoid piercing tissue and just rely on the compressive force of the two plate-like collars on the captured tissue, or the anchor, itself or with an integrated securement wire, may pierce through native tissue to provide anchoring, or a combination of both. The anchor may have a specialized securement mechanism, such as a pointed tip with a groove and flanged shoulder that is inserted or popped into a mated aperture or an array of mated apertures that allow the anchor to attach, but prevent detachment when the aperture periphery locks into the groove near the flanged shoulder. The securement wire may be attached or anchored to the collar opposite the pin by any attachment or anchoring mechanisms, including a knot, a suture, a wire crimp, a wire lock having a cam mechanism, or combinations.
Support Post
The term “support post” refers to a rigid or semi-rigid length of material such as Nitinol or PEEK, that may be mounted on a spoked frame and that runs axially, or down the center of, or within a sewn seam of—, the flexible sleeve. The sleeve may be unattached to the support post, or the sleeve may be directly or indirectly attached to the support post.
In the description that follows, the term “body channel” is used to define a blood conduit or vessel within the body. Of course, the particular application of the prosthetic heart valve determines 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 will be implanted at the tricuspid or mitral annulus. Certain features of the present invention are particularly advantageous for one implantation site or the other. However, unless the combination is structurally impossible, or excluded by claim language, any of the heart valve embodiments described herein could be implanted in any body channel.
The term “lumen” refers to the inside of the cylinder tube. The term “bore” refers to the inner diameter.
Displacement—The volume of fluid displaced by one complete stroke or revolution.
Ejection fraction is a measurement of the percentage of blood leaving your heart each time it contracts. During each heartbeat pumping cycle, the heart contracts and relaxes. When your heart contracts, it ejects blood from the two pumping chambers (ventricles).
As a point of further definition, the term “expandable” is used herein to refer to a component of the heart valve capable of expanding from a first, delivery diameter to a second, implantation diameter. An expandable structure, therefore, does not mean one that might undergo slight expansion from a rise in temperature, or other such incidental cause. 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.
Prosthetic Heart Valve
The term prosthesis or prosthetic encompasses 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. native valve is left in place. For mounting within a passive assist cage, the invention contemplates a wide variety of (bio)prosthetic artificial heart valves. Contemplated as within the scope of the invention are 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 heart valves), as well as homograft and autograft valves. For bioprosthetic pericardial valves, it is contemplated to use bioprosthetic aortic valves, bioprosthetic mitral valves, bioprosthetic mitral valves, and bioprosthetic pulmonary valves.
Tethers—
The tethers are made from surgical-grade materials such as biocompatible polymer suture material. Non-limiting examples of such material include ultra high-molecular weight polyethylene (UHMWPE), 2-0 exPFTE(polytetrafluoroethylene) or 2-0 polypropylene. In one embodiment the tethers are inelastic. It is also contemplated that one or more of the tethers may optionally be elastic to provide an even further degree of compliance of the valve during the cardiac cycle.
Tines—Anchors—Tines/Barbs
The device can be seated within the valvular annulus through the use of tines or barbs. These may be used in conjunction with, or in place of one or more tethers. The tines or barbs are located to provide attachment to adjacent tissue. Tines are forced into the annular tissue by mechanical means such as using a balloon catheter. In one non-limiting embodiment, the tines may optionally be semi-circular hooks that upon expansion of the wire frame body, pierce, rotate into, and hold annular tissue securely. Anchors are deployed by over-wire delivery of an anchor or anchors through a delivery catheter. The catheter may have multiple axial lumens for delivery of a variety of anchoring tools, including anchor setting tools, force application tools, hooks, snaring tools, cutting tools, radio-frequency and radiological visualization tools and markers, and suture/thread manipulation tools. Once the anchor(s) are attached to the moderator band, tensioning tools may be used to adjust the length of tethers that connect to an implanted valve to adjust and secure the implant as necessary for proper functioning. It is also contemplated that anchors may be spring-loaded and may have tether-attachment or tether-capture mechanisms built into the tethering face of the anchor(s). Anchors may also have in-growth material, such as polyester fibers, to promote in-growth of the anchors into the myocardium.
In one embodiment, where a prosthetic heart valve may or may not include a ventricular collar, the anchor or dart is not attached to a lower ventricular collar, but is attached directly into annular tissue or other tissue useful for anchoring.
Tube and/or Cover Material—Biological Tissue—
The tissue used herein is a biological tissue that is a chemically stabilized pericardial tissue of an animal, such as a cow (bovine pericardium) or sheep (ovine pericardium) or 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. Other patents and publications disclose the surgical use of harvested, biocompatible animal thin tissues suitable herein as biocompatible “jackets” or sleeves for implantable stents, including for example, U.S. Pat. No. 5,554,185 to Block, U.S. Pat. No. 7,108,717 to Design & Performance-Cyprus Limited disclosing a covered stent assembly, U.S. Pat. No. 6,440,164 to Scimed Life Systems, Inc. disclosing a bioprosthetic heart valve for implantation, and U.S. Pat. No. 5,336,616 to LifeCell Corporation discloses acellular collagen-based tissue matrix for transplantation.
Polymers
In one preferred embodiment, the conduit may optionally be made from a synthetic material such a polyurethane or polytetrafluoroethylene.
Where a thin, durable synthetic material is contemplated, e.g. for a covering, synthetic polymer materials such expanded polytetrafluoroethylene or polyester may optionally be used. Other suitable materials may optionally include thermoplastic polycarbonate urethane, polyether urethane, segmented polyether urethane, silicone polyether urethane, silicone-polycarbonate urethane, and ultra-high molecular weight polyethylene. Additional biocompatible polymers may optionally include polyolefins, elastomers, polyethylene—glycols, polyethersulphones, polysulphones, polyvinylpyrrolidones, polyvinylchlorides, other fluoropolymers, silicone polyesters, siloxane polymers and/or oligomers, and/or polylactones, and block co-polymers using the same.
Polyamides (PA)
PA is an early engineering thermoplastic invented that consists of a “super polyester” fiber with molecular weight greater than 10,000. It is commonly called Nylon.
Application of polyamides includes transparent tubing's for cardiovascular applications, hemodialysis membranes, and also production of percutaneous transluminal coronary angioplasty (PTCA) catheters.
Polyolefin
Polyolefins include polyethylene and polypropylene are the two important polymers of polyolefins and have better biocompatibility and chemical resistance. In cardiovascular uses, both low-density polyethylene and high-density polyethylene are utilized in making tubing and housings.
Polypropylene is used for making heart valve structures.
Polyesters Polyesters includes polyethylene-terephthalate (PET), using the name Dacron. It is typically used as knitted or woven fabric for vascular grafts. Woven PET has smaller pores which reduces blood leakage and better efficiency as vascular grafts compared with the knitted one. PET grafts are also available with a protein coating (collagen or albumin) for reducing blood loss and better biocompatibility [39]. PET vascular grafts with endothelial cells have been searched as a means for improving patency rates. Moreover, polyesters are widely preferred material for the manufacturing of bioabsorbable stents. Poly-L-lactic acids (PLLA), polyglycolic acid (PGA), and poly(D, L-lactide/glycolide) copolymer (PDLA) are some of the commonly used bioabsorbable polymers.
Polytetrafluoroethylene
Polytetrafluoroethylene (PTFE) is synthetic fluorocarbon polymer with the common commercial name of Teflon by Dupont Co. Common applications of PTFE in cardiovascular engineering include vascular grafts and heart valves. PTFE sutures are used in the repair of mitral valve for myxomatous disease and also in surgery for prolapse of the anterior or posterior leaflets of mitral valves. PTFE is particularly used in implantable prosthetic heart valve rings. It has been successfully used as vascular grafts when the devices are implanted in high-flow, large-diameter arteries such as the aorta. Problem occurs when it is implanted below aortic bifurcations and another form of PTFE called elongated-PTFE (e-PTFE) was explored. Expanded PTFE is formed by compression of PTFE in the presence of career medium and finally extruding the mixture. Extrudate formed by this process is then heated to near its glass transition temperature and stretched to obtain microscopically porous PTFE known as e-PTFE. This form of PTFE was indicated for use in smaller arteries with lower flow rates promoting low thrombogenicity, lower rates of restenosis and hemostasis, less calcification, and biochemically inert properties.
Polyurethanes
Polyurethane has good physiochemical and mechanical properties and is highly biocompatible which allows unrestricted usage in blood contacting devices. It has high shear strength, elasticity, and transparency. Moreover, the surface of polyurethane has good resistance for microbes and the thrombosis formation by PU is almost similar to the versatile cardiovascular biomaterial like PTFE. Conventionally, segmented polyurethanes (SPUs) have been used for various cardiovascular applications such as valve structures, pacemaker leads and ventricular assisting device.
Covered Wire Frame Materials
Drug-eluting wire frames are contemplated for use herein. DES basically consist of three parts: wire frame platform, coating, and drug. Some of the examples for polymer free DES are Amazon Pax (MINVASYS) using Amazonia CroCo (L605) cobalt chromium (Co—Cr) wire frame with Paclitaxel as an antiproliferative agent and abluminal coating have been utilized as the carrier of the drug. BioFreedom (Biosensors Inc.) using stainless steel as base with modified abluminal coating as carrier surface for the antiproliferative drug Biolimus A9. Optima (CID S.r.I.) using 316 L stainless steel wire frame as base for the drug Tacrolimus and utilizing integrated turbostratic carbofilm as the drug carrier. VESTA sync (MIV Therapeutics) using GenX stainless steel (316 L) as base utilizing microporous hydroxyapatite coating as carrier for the drug Sirolimus. YUKON choice (Translumina) used 316 L stainless steel as base for the drugs Sirolimus in combination with Probucol.
Biosorbable polymers may also be used herein as a carrier matrix for drugs. Cypher, Taxus, and Endeavour are the three basic type of bioabsorbable DES. Cypher (J&J, Cordis) uses a 316 L stainless steel coated with polyethylene vinyl acetate (PEVA) and poly-butyl methacrylate (PBMA) for carrying the drug Sirolimus. Taxus (Boston Scientific) utilizes 316 L stainless steel wire frames coated with translute Styrene Isoprene Butadiene (SIBS) copolymer for carrying Paclitaxel which elutes over a period of about 90 days. Endeavour (Medtronic) uses a cobalt chrome driver wire frame for carrying zotarolimus with phosphorylcholine as drug carrier. BioMatrix employing S-Wire frame (316 L) stainless steel as base with polylactic acid surface for carrying the antiproliferative drug Biolimus. ELIXIR-DES program (Elixir Medical Corp) consisting both polyester and polylactide coated wire frames for carrying the drug novolimus with cobalt-chromium (Co—Cr) as base. JACTAX (Boston Scientific Corp.) utilized D-lactic polylactic acid (DLPLA) coated (316 L) stainless steel wire frames for carrying Paclitaxel. NEVO (Cordis Corporation, Johnson & Johnson) used cobalt chromium (Co—Cr) wire frame coated with polylactic-co-glycolic acid (PLGA) for carrying the drug Sirolimus.
Examples of preferred embodiments include the following details and features.
The transcatheter prosthetic heart valve may be percutaneously delivered using a transcatheter process via the femoral through the IVC, carotid, sub-xyphoid, intercostal access across the chest wall, and trans-septal to the mitral annulus through the fossa ovalis.
The device is delivered via catheter to the right or left atrium and is expanded from a compressed shape that fits with the internal diameter of the catheter lumen. The compressed valve is loaded external to the patient into the delivery catheter, and is then pushed out of the catheter when the capsule arrives to the atrium. The cardiac treatment technician visualizes this delivery using available imaging techniques such as fluoroscopy or ultrasound.
In a preferred embodiment the valve self-expands upon release from the catheter since it is constructed in part from shape-memory material, such as Nitinol®, a nickel-titanium alloy, or a cobalt-chromium alloy, alloys used in biomedical implants.
In another embodiment, the valve may be constructed of materials that requires balloon-expansion after the capsule has been ejected from the catheter into the atrium.
The atrial collar/frame and the flow control component are expanded to their functional diameter, as they are deployed into the native annulus, providing a radial tensioning force to secure the valve. Once the frame is deployed about the mitral annulus, fasteners secure the device about the native annulus. Additional fastening of the device to native structures may be performed, and the deployment is complete. Further adjustments using hemodynamic imaging techniques are contemplated as within the scope of the invention in order to ensure the device is secure, is located and oriented as planned, and is functioning as a substitute or successor to the native mitral valve.
In a preferred embodiment the invention includes a process for manufacturing a side delivered transcatheter prosthetic heart valve frame, comprising:
In another preferred embodiment, there is provided a process for manufacturing a side delivered transcatheter prosthetic heart valve frame, further comprising the steps of: (ii) mounting a flow control component within the valve frame, said flow control component configured to permit blood flow along the central vertical axis through an inflow end of the flow control component and block blood flow through an outflow end of the valve, (iii) covering an outer surface of the valve frame with a pericardium material or similar biocompatible material.
In another preferred embodiment, there is provided a method of compressing, wherein the implantable prosthetic heart valve is rolled or folded into a compressed configuration using a step selected from the group consisting of:
(i) unilaterally rolling into a compressed configuration from one side of the annular support frame;
(ii) bilaterally rolling into a compressed configuration from two opposing sides of the annular support frame;
(iii) flattening the annular support frame into two parallel panels that are substantially parallel to the long-axis, and then rolling the flattened annular support frame into a compressed configuration; and
(iv) flattening the annular support frame along a vertical axis to reduce a vertical dimension of the valve from top to bottom.
Referring now to the drawings,
The annular outer support frame 102 is made from a shape-memory material such as Nickel-Titanium alloy, for example NiTiNOL, and is therefore a self-expanding structure starting from a compressed configuration. The annular (outer) support frame 102 has a central (interior) channel and an outer perimeter wall circumscribing a central vertical axis 108, when in an expanded configuration, and said annular outer support frame 102 having a distal side 118 and a proximal side 114.
The flow control component 130 is mounted within the annular outer support frame 102 and is configured to permit blood flow in a first direction, e.g. atrial to ventricular, through an inflow end 132 of the valve 100 and block blood flow in a second direction, opposite the first direction, through an outflow end 134 of the valve 100.
The inner flow control component 130, like the outer annular frame 102, is foldable and compressible. The inner flow control component 130 comprises leaflet frame 231 with 2-4 flexible leaflets 258 mounted on the leaflet frame 231.
The flow control component 130, and thereby the leaflet frame 231, like the outer frame 102, is foldable along a z-axis (front to back) from a cylindrical configuration to a flattened cylinder configuration, where the fold lines are located on a distal side and on a proximal side, taking the leaflet frame 231 from a ring or cylinder shape, and flattening it from a ring to a two-layer band i.e. folded over on itself, or like a cylinder flattened into a rectangle or square joined along two opposing sides. This allows the outer frame 102 and the flow control component 130 to reduce the radius along z-axis until the side walls are in contact or nearly so. This also allows the outer frame 102 and the flow control component 130 to maintain the radius along the horizontal axis, the y-axis, to minimize the number of wire cells, which make up the outer and the inner, that are damaged by forces applied during folding and/or compression necessary for loading into the delivery catheter.
The flow control component 130, leaflet frame 231, and the outer frame 102 are also vertically (y-axis) compressible, reducing the height of the entire valve structure to fit within the inner diameter of a delivery catheter 138 (not shown in this Figure). By folding in the z-axis and vertically compressing in the y-axis, the valve structure is permitted to maintain a very large dimension along the horizontal, or x-axis. For example, a 60 mm or larger diameter valve can be delivered via transcatheter techniques. The length of the long axis of a valve, e.g. 60 mm, since it runs parallel to the central axis of the delivery catheter, is not limited by the large amount of wire frame and cover material necessary for such a large valve. This is not possible with existing center-axis delivery (axial) transcatheter valves. The use of a folded, compressed valve that is orthogonal to the traditional axial-delivery valves permits treatment options not available previously.
In a preferred embodiment, the horizontal x-axis of the valve is orthogonal to (90 degrees), or substantially orthogonal to (75-105 degrees), or substantially oblique to (45-135 degrees) to the central vertical y-axis when in an expanded configuration.
In a preferred embodiment, the horizontal x-axis of the compressed configuration of the valve is substantially parallel to a length-wise cylindrical axis of the delivery catheter.
In another preferred embodiment, the valve has a compressed height (y-axis) and width (z-axis) of 6-15 mm, preferably 8-12 mm, and more preferably 9-10 mm, and an expanded deployed height of about 5-60 mm, preferably about 5-30 mm, and more preferably about 5-20 mm or even 8-12 mm or 8-10 mm. It is contemplated in preferred embodiments that the length of the valve, x-axis, does not require compression since it can extend along the length of the central cylindrical axis of the delivery catheter.
In a preferred embodiment, the valve has an expanded diameter length and width of 25-80 mm, preferably 40-80 mm, and in certain embodiments length and/or width may vary and include lengths of 25 mm, 30 mm, 35 mm, 40 mm, 45 mm, 50 mm, 55 mm, 60 mm, 65 mm, 70 mm, 75 mm, and 80 mm, in combination with widths that are the same or different as the length.
In certain preferred embodiments, the valve is centric, or radially symmetrical. In other preferred embodiments, the valve is eccentric, or radially (y-axis) asymmetrical. In some eccentric embodiments, the frame 102 may have a D-shape in cross-section so the flat portion can be matched to the mitral annulus near the anterior leaflet.
In certain preferred embodiments, the inner frame 231 is 25-29 mm in diameter, the outer frame 102 is 50-70 mm in diameter, and the collar structure 103 extends beyond the top edge of the outer frame by 10-30 mm to provide a seal on the atrial floor against perivalvular leaks (PVLs).
Atrial collar 103 is shaped to conform to the native deployment location. In a mitral replacement, the atrial collar will be configured with varying portions to conform to the native valve. In one preferred embodiment, the collar 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 or subannular geometries.
Atrial collar 103 is shaped to conform to the native deployment location. In a mitral replacement, the atrial collar will have a tall back wall portion to conform to the native valve, and 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 the larger flat space above (atrial) the left ventricular outflow tract (LVOT) subannular area.
Integrated tabs 269 and 271 are unitary construction with the body of the outer frame. The tabs may vary in size and shape. In a preferred embodiment, the Distal tab, e.g. 269 may be longer in the case of a mitral replacement. In above preferred embodiment, the shape of the distal tab is configured to wrap around the P1-P2 posterior leaflet and chordae, and the shape of the proximal tab is configured to conform to the A3 and P3 commissural areas of the mitral valve.
A2 clip 111 is vertically extended subannularly during deployment of the valve to capture native leaflet, e.g. A2, tissue, when the A2 clip 111 is retracted. The A2 clip is actuated using a steerable catheter and/or guidewire system to deliver an external A2 clip 111 or to extend a pre-existing sheathed A2 clip from a mesh pocket on the sidewall of the valve body. When an external A2 clip 111 is delivered, imaging markers on or around the sleeve/pocket/sheath 113 help guide the steerable catheter to the A2 clip sleeve/pocket/sheath 113, where the A2 clip 111 is pushed to a subannular position, then a catheter sheath is withdrawn to expose a distal portion of the A2 clip and expand the distal portion to a shape-memory (spring-effect) configuration. When the expanded distal portion of the A2 clip 111 is pulled up atrially in the direction of the underside of the native annulus, the expanded distal portion captures the native leaflet (A2 or other desired leaflet) and secures it against the underside of the annulus and/or valve body.
Distal anchoring tab 269 tracks on a guide wire inserted near the A1 leaflet/commissure of the mitral valve. The guide wire is pre-positioned around the native mitral leaflets and/or chordae, especially the mitral P2 leaflet, to facilitate the over-wire placement of the distal anchoring tab 269 around the “back side” of the P2 leaflet to clamp the native P2 leaflet against the frame 102.
The use of an A2 clip on one side (A2) and a wrap-around distal tab 269 on an opposite side (P2) provides oppositional anchoring and securement and can reduce micro-motion and encourage in-growth success of the valve.
As in
Like the inner leaflet frame, the annular outer support frame 102 is made from a shape-memory material such as Nickel-Titanium alloy, for example NiTiNOL, and is therefore a self-expanding structure starting from a compressed configuration. The annular (outer) support frame 102, 103 has a central (interior) channel and an outer perimeter wall circumscribing a central vertical axis, when in an expanded configuration, and said annular outer support frame 102 having a distal side 118 and a proximal side 114.
The flow control component 130 is mounted within the annular outer support frame 102 and is configured to permit blood flow in a first direction, e.g. atrial to ventricular, through an inflow end 132 of the valve and block blood flow in a second direction, opposite the first direction, through an outflow end 134 of the valve.
The inner flow control component 130, like the outer annular frame 102, is foldable and compressible. The inner flow control component 130 comprises leaflet frame 231 with 2-4 flexible leaflets 258 mounted on the leaflet frame 231.
The flow control component 130, and thereby the leaflet frame 231, like the outer frame, is foldable along a z-axis (front to back) from a cylindrical configuration to a flattened cylinder configuration, where the fold lines are located on a distal side and on a proximal side, taking the leaflet frame 231 from a ring or cylinder shape, and flattening it from a ring to a two-layer band i.e. folded over on itself, or like a cylinder flattened into a rectangle or square joined along two opposing sides. This allows the outer frame 102 and the flow control component 130 to reduce the radius along z-axis until the side walls are in contact or nearly so. This also allows the outer frame 102 and the flow control component 130 to maintain the radius along the horizontal axis, the y-axis, to minimize the number of wire cells, which make up the outer and the inner, that are damaged by forces applied during folding and/or compression necessary for loading into the delivery catheter.
The flow control component 130, leaflet frame 231, and the outer frame 102 are also vertically (y-axis) compressible, reducing the height of the entire valve structure to fit within the inner diameter of a 24-36 Fr (8-12 mm inner diameter) delivery catheter 138 (not shown in this Figure).
By folding in the z-axis and vertically compressing in the y-axis, the valve structure is permitted to maintain a very large dimension along the horizontal, or x-axis. For example, a 60 mm or larger diameter valve can be delivered via transcatheter techniques. The length of the long axis of a valve, e.g. 60 mm, since it runs parallel to the central axis of the delivery catheter, is not limited by the large amount of wire frame and cover material necessary for such a large valve. This is not possible with existing center-axis delivery (axial) transcatheter valves. The use of a folded, compressed valve that is orthogonal (transverse) to the traditional axial-delivery valves permits treatment options not available previously.
Atrial collar 103 is shaped to conform to the native deployment location. In a mitral replacement, the atrial collar will have a tall back wall portion to conform to the septal area of the native valve, and 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 the larger flat space above (atrial) the left ventricular outflow tract (LVOT) subannular area.
Integrated tabs are unitary construction with the body of the outer frame. The tabs may vary in size and shape. In a preferred embodiment, the distal tab, e.g. 269 may be longer to reach posterior leaflet tissue and chordae. In above preferred embodiment, the shapes of the tabs are configured to conform to the A1 and A3 commissural areas of the mitral valve.
Below is provide a parts list in relation to claimed elements. Part numbering may refer to functional components and may be re-used across differing preferred embodiments to aid in uniformly understanding structure-function relationships. To avoid cluttering in drawing sheets, not every number may be added to the drawing sheets, or may be added later during examination as needed.
Various of the above-disclosed and other features and functions, or alternatives thereof, may be combined into many other different systems or applications. Various presently unforeseen or unanticipated alternatives, modifications, variations or improvements therein may be subsequently made by those skilled in the art, each of which is also intended to be encompassed by the disclosed embodiments.
Having described embodiments for the invention herein, it is noted that modifications and variations can be made by persons skilled in the art in light of the above teachings. It is therefore to be understood that changes may be made in the particular embodiments of the invention disclosed which are within the scope and spirit of the invention as defined by the appended claims. Having thus described the invention with the details and particularity required by the patent laws, what is claimed and desired protected by Letters Patent is set forth in the appended claims.
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|---|---|---|---|
| 20200289263 A1 | Sep 2020 | US |
| Number | Date | Country | |
|---|---|---|---|
| 62818688 | Mar 2019 | US |
