Tricuspid regurgitation control devices for orthogonal transcatheter heart valve prosthesis

[0001] This application is a continuation of International Patent Application Serial No. PCT/US2020/021300, filed Mar. 5, 2020, entitled “Tricuspid Regurgitation Control Devices for Orthogonal Transcatheter Heart Valve Prosthesis,” which claims priority to and the benefit of U.S. Provisional Patent Application Ser. No. 62/813,770, filed Mar. 5, 2019, entitled “Tricuspid Regurgitation Control Devices for Orthogonal Transcatheter Heart Valve Prosthesis,” the disclosure of each of which is incorporated herein by reference in its entirety.

[0002] The invention relates to an access and occluder device, and in particular a heart valve regurgitation drum and optional closure disk and/or tubular stent to manage and provide levels of intentional regurgitation within a transcatheter heart valve replacement (A61F2/2412).

[0003] 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.

[0004] 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.

[0005] 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 die 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.

[0006] 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.

[0007] 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.

[0008] 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.

[0009] The present invention is directed to an access and occluder device, and in particular a heart valve regurgitation drum and optional closure component and/or a perforated tubular stent to manage and provide levels of intentional regurgitation within a transcatheter heart valve replacement, and in particular, within an orthogonally (length-wise, along z-axis) delivered transcatheter prosthetic heart valve.

[0010] In a preferred embodiment, a heart valve regurgitation drum with an optional closure component and/or tubular stent for an orthogonally delivered transcatheter prosthetic heart valve comprises a first inner flow control component/valve, a second inner regurgitation control component, and an outer annular support frame having compressible wire cells that facilitate folding flat along the z-axis and compressing the valve vertically along the y-axis, or orthogonally to the central axis of the flow control component, allowing a very large diameter valve to be delivered and deployed to the tricuspid valve from the inferior vena cava or superior vena cava, or trans-septally (transatrially, across fossa ovalis or adjacent tissue) to the mitral valve, the valve having 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.

[0011] In another preferred embodiment, the invention provides device to manage and provide grades of intentional regurgitation within an orthogonally delivered transcatheter prosthetic heart valve, comprising: an orthogonally delivered transcatheter prosthetic heart valve having (i) a first inner flow control component, (ii) a second inner regurgitation control component, and (iii) an outer annular support frame, the second inner regurgitation control component having a foldable and compressible frame, a tissue cover attached to the frame, and an flow modifier mounted within a reinforcement ring mounted on the tissue cover, the flow modifier selected from a occluder, a tubular stent, and a tubular stent having an occluder within a lumen of the tubular stent, said tissue cover having one or more radio-opaque markers, and said second inner regurgitation control component mounted within the outer support frame of the prosthetic heart valve, the self-expanding annular outer support frame having a central channel, an outer perimeter wall circumscribing a central vertical axis in an expanded configuration, an atrial collar mounted along a top edge of the perimeter wall, a distal anchoring tab mounted on a distal side of the outer annular support frame, and a proximal anchoring tab mounted on a proximal side of the outer annular support frame, the first inner flow control component mounted within the outer annular support frame adjacent to the second inner regurgitation control component, said first inner flow control component 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 first inner flow control component having leaflet frame with 2-4 flexible leaflets mounted thereon, wherein each of said foldable and compressible frame of the second inner regurgitation control component, said leaflet frame of the first inner flow control component, and said outer support frame are each foldable along a horizontal z-axis from a cylindrical configuration to a flattened cylinder configuration and compressible along a vertical y-axis to a shortened configuration, wherein the prosthetic heart 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 that is substantially parallel to a length-wise cylindrical axis of the delivery catheter, said horizontal x-axis oriented at an intersecting angle of between 45-135 degrees to the central vertical y-axis, and expandable to an expanded configuration having the horizontal x-axis at an intersecting angle of between 45-135 degrees to the central vertical y-axis, wherein the valve has a height of about 5-60 mm and a diameter of about 25-80 mm.

[0012] In another preferred embodiment, the invention provides a valve wherein the annular outer 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.

[0013] In another preferred embodiment, the invention provides a valve wherein the distal anchoring tab, the proximal anchoring tab, or both, are comprised of wire loop, a wire frame, a laser cut frame, an integrated frame section, or a stent, and extend from about 10-40 mm away from the side of the annular outer support frame.

[0014] In another preferred embodiment, the invention provides a valve further comprising 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 outer support frame.

[0015] In another preferred embodiment, the invention provides a valve comprising at least one tissue anchor connected to the annular outer support frame for engaging native tissue.

[0016] In another preferred embodiment, the invention provides a valve wherein the annular outer 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.

[0017] In another preferred embodiment, the invention provides a valve wherein the annular outer support frame is covered on an outer surface with a pericardium tissue, a polyester material or similar biocompatible material.

[0018] In another preferred embodiment, the invention provides a method of providing intentional regurgitation in an implanted transcatheter prosthetic heart valve, comprising the steps: cutting or perforating a section of the tissue cover within the reinforcement ring of the second inner regurgitation control component of claim 1 to form an aperture by deploying a catheter cutting tool to the implanted valve of claim 1, where the valve of claim 1 is implanted as a prosthetic heart valve in a patient.

[0019] In another preferred embodiment, the invention provides a method, comprising an additional step of deploying into the aperture a flow modifier selected from an occluder, a tubular stent, and a tubular stent having an occluder within a lumen of the tubular stent.

[0020] In another preferred embodiment, the invention provides a method of controlling or modifying regurgitation in a patient having an orthogonally delivered transcatheter prosthetic heart valve, comprising the steps: Step 1. providing a foldable, compressible prosthetic tricuspid valve according to claim 1; Step 2. loading the valve sideways into a delivery catheter; Step 3. advancing the valve to a tricuspid valve of a heart of the patient via an inferior vena cava (IVC) or superior vena cava (SVC) over a pre-placed guidewire that is threaded onto a subannular distal tab; Step 4. partially expelling the valve to position the distal subannular tab and to allow valve leaflets to begin functioning; Step 5. completing deployment of the valve into the native annulus; and Step 6. advancing a cutting tool or balloon tool through the delivery catheter to the deployed valve and creating a 1-5 mm opening in the tissue covering of the inner regurgitation control component.

[0021] In another preferred embodiment, the invention provides a method of controlling or modifying regurgitation, further comprising: Step 7. advancing a pacemaker wire set through the opening in the in the tissue covering of the inner regurgitation control component and attaching the pacemaker wire(s) at or near the target conduction nodes.

[0071] The invention is directed to a dual-tab transcatheter 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, an elongated sub-annular distal anchoring tab extending into the right ventricular outflow tract, an elongated sub-annular proximal anchoring tab extending into the proximal sub-annular space, preferably between the anterior and the posterior leaflets.

[0072] 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.

[0073] 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.

[0074] 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.

[0075] 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.

[0076] As used in this document, the term “comprising” means “including, but not limited to.”

[0077] 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.

[0078] 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.

[0079] 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.”

[0080] 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.

[0081] 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.

Orthogonal

[0082] In the description and claims herein, the term “orthogonal” is 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. 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 in a manner akin to pushing a closed umbrella out of a sleeve. The valves of the present invention are compressed and delivered in a sideways manner. 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.

[0083] 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, e.g., 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

[0084] 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.

[0085] In preferred embodiments of the invention, the transcatheter approach includes (i) advancing to the tricuspid valve or pulmonary artery of the heart through the inferior vena cava via the femoral vein, (ii) advancing to the tricuspid 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

[0086] 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 sleeve or sleeve-valve.

[0087] 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.

[0088] 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.

[0089] This front wall portion can be further defined as having a front upper collar portion and a front lower body portion, and the back wall portion can be further defined as having a back upper collar portion and a back lower body portion.

[0090] The annular 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.

[0091] Since the frame is preferably made of superelastic metal or alloy such as Nitinol, the frame is compressible. Preferably, the frame is constructed 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 when configured in a vertical compressed configuration, a rolled compressed configuration, or a folded compressed configuration.

Annular Support Frame Structure

[0092] 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.

[0093] 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 tricuspid annulus may have a complex shape determined by the anatomical structures where the valve is being mounted. For example, in the tricuspid annulus, the circumference of the tricuspid valve may be a rounded ellipse, the septal wall is known to be substantially vertical, and the tricuspid is known to enlarge in disease states along the anterior-posterior line. 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

[0094] 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

[0095] 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

[0096] 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

[0097] 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

[0098] 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.

[0099] 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

[0100] 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.

[0101] 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

[0102] 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

[0103] 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 an inner annular support frame (referred to as an “inner leaflet frame” or “leaflet frame”) mounted within an outer 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.”

Regurgitation Drum or Inner Regurgitation Control Component

[0104] In the description and claims herein, the term “regurgitation drum” or “inner regurgitation control component” refers to a second inner annular support frame mounted within the outer annular support frame next to the first inner annular support frame. The “regurgitation drum” or “inner regurgitation control component” has a foldable and compressible frame, a tissue cover attached to the frame, and a flow modifier mounted within a reinforcement ring mounted on the tissue cover, the flow modifier selected from a channel, an occluder, a tubular stent, and a tubular stent having an occluder within a lumen of the tubular stent, said tissue cover having one or more radio-opaque markers. This “regurgitation drum” or “inner regurgitation control component” can be pre-perforated before the valve is loaded into the delivery catheter, it can be perforated using a catheter tool after the valve has been deployed into the native annulus, the perforation can be reinforced using a stent tube, and the perforation or stent tube can be sealed off using a closure device such as a polyester disk, a nitinol disk, a nitinol disk having a polyester cover, a double-disk (button on each side) closure device, or functionally similar device similar to the devices used to treat patent foramen ovale but modified for use in accessing and closing a, e.g., 1-2 mm perforation in, a regurgitation drum.

Reinforcement Ring

[0105] The term reinforcement ring refers to a ring of material such as pericardium, polymer, or biocompatible material, that is mounted on the top surface of the tissue cover of the “regurgitation drum” or “inner regurgitation control component.” In a preferred embodiment, the reinforcement ring circumscribes the target area for the perforation and prevent the perforation from tearing or losing patency. In another preferred embodiment, the radio-opaque markers, that are used to guide the catheter cutting/balloon tool, may be mounted on top of or within the reinforcement ring.

Radio-Opaque Marker

[0106] The term “radio-opaque marker” refers to a material that allows visibility during fluoroscopy or other radiologic imaging. Examples of radio-opaque marker materials include nitinol, gold, platinum, and combinations or mixtures thereof. Radio-opaque materials may also include powdered or particulate metals that are encompassed within a polymer, glass, or ceramic matrix. The invention contemplates the use of one or more markers, e.g., from 1-10, or from 3-5 markers. The invention contemplates the use of markers mounted in a specific pattern or orientation to provide not only targeting of a perforation location, but also positioning information for the valve itself. For example, use of a three marker pattern provides a central targeting area, but can also provide information on whether the valve is oriented correctly, such as having the septal-collar portion of the prosthetic valve aligned with the septal side of the tricuspid valve.

Tissue Anchor

[0107] 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 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

[0108] 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.

[0109] 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.

[0110] The term “lumen” refers to the inside of the cylinder tube. The term “bore” refers to the inner diameter.

[0111] Displacement—The volume of fluid displaced by one complete stroke or revolution.

[0112] 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).

[0113] As used herein, the terms “proximal” and “distal” are to be taken as relative to a user (e.g., a surgeon or an interventional cardiologist) of the disclosed delivery devices. “Proximal” is to be understood as relatively close to the user and “distal” is to be understood as relatively farther away from the user.

[0114] 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

[0115] 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 tricuspid valves, and bioprosthetic pulmonary valves.

Tethers

[0116] 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

[0117] 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.

[0118] 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

[0119] 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

[0120] In one preferred embodiment, the conduit may optionally be made from a synthetic material such a polyurethane or polytetrafluoroethylene.

[0121] 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)

[0122] 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

[0123] 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

[0124] 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

[0125] 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

[0126] 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

[0127] 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.

[0128] 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.

[0129] 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.

[0130] 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.

[0131] 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.

[0132] 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.

[0133] 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 valve is deployed about the tricuspid or 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 tricuspid valve.

[0134] In another preferred embodiment of the invention, there is provided a method for orthogonal delivery of implantable prosthetic heart valve in the body, the method comprising the steps: (i) advancing a distal end of a guide wire to a distal location, wherein the distal location is a pulmonary artery or a left ventricle of a heart, wherein the guide wire starts outside of a patient using femoral vein access or brachiocephalic vein access, and extends through an inferior vena cava or a superior vena cava to a right atrium, and extends from the right atrium through the tricuspid valve to the pulmonary artery or extends from the right atrium across the atrial septum in a transseptal access through the mitral valve and into a left ventricle; (ii) advancing a delivery catheter over the guide wire to a target location, where the target location is a right atrium of the tricuspid valve or a left atrium of the mitral valve; (iii) advancing and delivering an orthogonally compressed self-expandable prosthetic heart valve to the target location in the body, wherein a compressed configuration of the valve has a long x-axis substantially parallel to a length-wise cylindrical axis of the delivery catheter, wherein the expanded configuration of the valve has a height of about 5-60 mm and a diameter of about 25-80 mm, wherein the valve comprises an annular support frame having a collapsible 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, the collapsible (inner) flow control component having leaflet frame with 2-4 flexible leaflets mounted thereon, the leaflet frame foldable along a z-axis from a cylindrical configuration to a flattened cylinder configuration and compressible along a vertical axis (y-axis) to a shortened configuration, a distal anchoring tab is mounted on a distal side of the annular support frame, the distal anchoring tab having a length of 10-40 mm and a width of 2-10 mm, wherein the guide wire is threaded through a threading aperture on or within the distal anchoring tab, at least one proximal anchoring tab is mounted on a proximal side of the annular support frame, the proximal anchoring tab having a length of 2-25 mm and a width of 2-10 mm, and a valve advancing tool comprising an elongated sheath wherein the guide wire is within a lumen of the sheath, wherein the outer diameter of the sheath is larger than the inner diameter of the threading aperture on the distal anchoring tab, wherein when the sheath is advanced over the guide wire in a distal direction, and a distal end of the sheath contacts a proximal surface of the threading aperture, the valve is advanced distally through the delivery catheter by the distally-directed pulling force that the sheath imparts to the distal anchoring tab; (iv) partially releasing the valve from the delivery catheter by advancing the sheath over the guide wire, and positioning the distal anchoring tab at a desired anchoring area of the target location, wherein the desired anchoring area is selected from a right ventricular outflow tract (RVOT) of a right ventricle, and a sub-annular area below an A₁-P₁ antero-lateral commissure of a mitral valve, wherein positioning the distal anchoring tab holds the valve at a raised angle of at least 30 degrees to a localized annular plane relative to the horizontal axis of the valve and the delivery catheter, wherein partially releasing the valve permits blood to flow partially around the prosthetic valve and through the native leaflets, and partially through the flow control component of the prosthetic valve to provide a gradual blood flow transition from flow through native leaflets to complete flow through the prosthetic valve; (v) completing release of the entire valve from the delivery catheter by advancing the sheath over the guide wire, seating the valve in the native annulus by applying a downward force in the direction of the ventricle; and (vi) seating the at least one proximal anchoring tab at a second desired anchoring area.

[0135] In another preferred embodiment of the invention, there is provided a method for orthogonal delivery of implantable prosthetic heart valve to a desired location in the body, including the tricuspid valve locations, the method comprising the steps: advancing a delivery catheter to the desired location in the body and delivering an expandable prosthetic heart valve to the desired location in the body by releasing the valve from the delivery catheter, wherein the valve comprises an annular support frame having a collapsible 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, the collapsible (inner) flow control component having leaflet frame with 2-4 flexible leaflets mounted thereon, the leaflet frame foldable along a z-axis from a cylindrical configuration to a flattened cylinder configuration and compressible along a vertical axis (y-axis) to a shortened configuration, a distal anchoring tab mounted on a distal side of the annular support frame, and a proximal anchoring tab mounted on a proximal side 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 having a long-axis oriented at an intersecting angle of between 45-135 degrees to the first direction, and expandable to an expanded configuration having a long-axis oriented at an intersecting angle of between 45-135 degrees to the first direction, wherein the long-axis of the compressed configuration of the valve is substantially parallel to a length-wise cylindrical axis of the delivery catheter, wherein the compressed configuration, wherein the valve has a height of about 5-60 mm and a diameter of about 25-80 mm.

[0136] 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.

[0137] The method of delivery may also include the additional step of anchoring one or more tissue anchors attached to the valve into native tissue.

[0138] The method of delivery may also include the additional step of positioning the distal anchoring tab of the heart valve prosthesis into the right ventricular outflow tract of the right ventricle.

[0139] The method of delivery may also include the additional steps of positioning the distal anchoring tab of the heart valve prosthesis into the right ventricular outflow tract of the right ventricle, and positioning an upper distal anchoring tab into a supra-annular position, and the upper distal anchoring tab providing a supra-annular downward force in the direction of the ventricle and distal anchoring tab providing a sub-annular upward force in the direction of the atrium.

[0140] The method of delivery may also include the additional step of rotating the heart valve prosthesis using a steerable catheter along an axis parallel to the plane of the valve annulus.

[0141] In another preferred embodiment of the invention, there is provided a method for orthogonally loading an implantable prosthetic heart valve into a delivery catheter, the method comprising the steps: loading an implantable prosthetic heart valve into a tapering fixture or funnel attached to a delivery catheter, wherein the valve comprises a annular support frame having 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, a distal anchoring tab mounted on a distal side of the annular support frame, and a proximal anchoring tab mounted on a proximal side of the annular support frame, wherein said loading is perpendicular or substantially orthogonal to the first direction, 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 having a long x-axis oriented at an intersecting angle of between 45-135 degrees to the first direction, and expandable to an expanded configuration having a long x-axis oriented at an intersecting angle of between 45-135 degrees to the first direction, wherein the long x-axis of the compressed configuration of the valve is substantially parallel to a length-wise cylindrical axis of the delivery catheter, wherein the valve has a height of about 5-60 mm and a diameter of about 25-80 mm.

[0142] In another preferred embodiment of the invention, there is provided a method for loading, wherein the step of loading includes attaching a loading accessory to a valve sidewall, to a valve cuff, to the distal anchoring tab, to the proximal anchoring tab, or a combination thereof, wherein the loading accessory is pushing rod or a pulling wire, and wherein the tapering fixture or funnel has a compression element on an inner surface of the tapering fixture or funnel to facilitate compression, iris-ing, or spiraling of the uncompressed valve.

[0143] In another preferred embodiment of the invention, there is provided a method for improving hemodynamic flow during implantation of a transcatheter prosthetic heart valve, comprising: advancing a delivery catheter to the desired location in the body and delivering the valve of claim 1 to the desired location in the body; partially releasing the valve from the delivery catheter to establish blood flow around the partially released valve and establish blood flow through the flow control component; completely releasing the valve from the delivery catheter while maintaining attachment to the valve with a positioning catheter or wire to transition to increased blood flow through the flow control component and decreasing blood flow around the valve; and deploying the valve into a final mounted position to transition to complete blood flow through the flow control component and minimal or no blood flow around the valve, and disconnecting and withdrawing the positioning catheter or wire from the valve.

[0144] In another preferred embodiment of the invention, there is provided a method for improving flow, wherein the distal anchoring tab is an RVOT tab positioned in the RVOT during the transition from partial release of the valve to complete release of the valve.

[0145] In a preferred embodiment the invention includes a process for manufacturing an orthogonally delivered transcatheter prosthetic heart valve frame, comprising: (i) using additive or subtractive metal or metal-alloy manufacturing to produce a self-expanding annular support frame, wherein the additive metal or metal-alloy manufacturing is 3D printing or direct metal laser sintering (powder melt), and wherein the subtractive metal or metal-alloy manufacturing is photolithography, laser sintering/cutting, CNC machining, electrical discharge machining.

[0146] In another preferred embodiment, there is provided a process for manufacturing an orthogonally 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.

[0147] 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; (i) 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.

[0148] Referring now to the drawings, FIG. 1 is an illustration of a side perspective view of an orthogonally deliverable transcatheter heart valve 100 with inner regurgitation control component 137 mounted within the annular outer support frame 102, a collapsible flow control component 130 mounted within the annular outer support frame 102 (also referred to as “outer frame”), distal tab 268 and proximal tab 270, according to the invention.

[0149] The inner regurgitation control component 137 is comprised of tissue cover 141, reinforcement ring 143, radio-opaque markers 144, and drum channel 135.

[0150] The collapsible (inner) flow control component 130 has an inner leaflet frame 231 (also referred to herein as “leaflet frame”) with 2-4 flexible leaflets 258 mounted thereon, the inner leaflet frame 231 foldable along a z-axis 109 from a cylindrical configuration to a flattened cylinder configuration and compressible along a vertical axis 108 (y-axis) to a shortened configuration.

[0151] 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 104 and an outer perimeter wall 106 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.

[0152] 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 of the valve 100 and block blood flow in a second direction, opposite the first direction, through an outflow end of the valve 100.

[0153] The inner regurgitation control component 137, like the inner flow control component 130 and the outer 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.

[0154] 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 109 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 108, to minimize the number of wire cells, which make up the outer frame 102 and the inner leaflet frame 231, that are damaged by forces applied during folding and/or compression necessary for loading into the delivery catheter.

[0155] The inner regurgitation control component 137, 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 100 structure to fit within the inner diameter of a delivery catheter (not shown in this Figure). By folding in the z-axis 109 and vertically compressing in the y-axis 108, the valve structure is permitted to maintain a very large dimension along the horizontal, or x-axis 140. For example, a 60 mm or larger diameter valve can be delivered via transcatheter techniques. The length of the long axis of the valve 100, 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.

[0156] FIG. 1 also shows a distal anchoring tab 268 mounted on the distal side 118 of the annular outer support frame 102, and a proximal anchoring tab 270 mounted on the proximal side 114 of the annular outer support frame 102.

[0157] In a preferred embodiment, the horizontal x-axis 140 of the valve 100 is at an intersecting angle of between 45-135 degrees to the central vertical y-axis 108 when in an expanded configuration.

[0158] In a preferred embodiment, the horizontal x-axis 140 of the compressed configuration of the valve 100 is substantially parallel to a length-wise cylindrical axis of the delivery catheter.

[0159] In another preferred embodiment, the valve 100 has a height of about 5-60 mm and a diameter of about 25-80 mm.

[0160] FIG. 1 also shows guide wire sheath 310, and guide wire 311. A lumen or guide ball 266 is shown mounted on the distal end of the distal tab 268 and having the guide wire 311 threaded through the lumen 266. Although large enough in internal diameter to permit the guide wire 311 to extend through, the lumen 266 is not large enough in internal diameter to permit the sheath 310 to extend through. This allows sheath 310 to be advanced along the guide wire 311 until it runs up against the proximal side of the lumen 266, wherein continued application of a pushing force on the sheath 310 pushes against the lumen, and allows the valve 100 to be pulled by the distal tab 268 out of the delivery catheter, and to the target location for deploying the valve 100.

[0161] FIG. 2 is an illustration of a side perspective view of an exploded view of an embodiment having inner regurgitation component 137 with radio-opaque markers 144, drum channel 135, and reinforcement ring 143. FIG. 2 also shows three leaflets 258 (leaflet cusps or pockets) mounted within a foldable and compressible inner wire frame 231 (also referred to herein as “leaflet frame” and/or “inner leaflet frame”), with distal hinge point 120 (or fold area) and proximal hinge point 116 (or fold area), the inner leaflet frame 231 is mounted within an annular outer support frame 102 (also referred to herein as “outer wire frame,” or “outer frame”) which has a collar component 103 attached circumferentially at a top edge 107 of the outer frame 102, a dual tab component having a distal (RVOT) tab 268 and a proximal tab 270, and an optional mesh component of biocompatible material that may be used to cover the inner regurgitation control component 137, to cover the collar 103, to cover the inner and outer aspect of the outer frame 102, and/or to cover the anchoring tabs 268, and 270, according to the invention.

[0162] Atrial collar 103 is shaped to conform to the native deployment location. In a tricuspid 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 right ventricular outflow tract (RVOT) subannular area.

[0163] FIG. 3 is an illustration of a side perspective view of an orthogonally deliverable transcatheter heart valve 100 with an open regurgitation frame 139 having radio-opaque markers 144. In this embodiment, the drum channel 135 may have a predetermined interior diameter depending on the grade of regurgitation desired by the physician.

[0164] FIG. 3 also shows a collapsible flow control component 130 mounted within the annular outer support frame 102, the collapsible (inner) flow control component 130 having leaflet frame 231 with 2-4 flexible leaflets 258 mounted thereon. The leaflet frame 231 is foldable along a z-axis from a cylindrical configuration to a flattened cylinder configuration and compressible along a vertical axis (y-axis) to a shortened configuration. The valve 100 also has a superelastic wire loop distal tab 269 and a superelastic wire loop proximal tab 271 according to the invention.

[0165] FIG. 4 is an illustration of a side perspective view of an exploded view of an embodiment having an open regurgitation frame 139 having radio-opaque markers 144. FIG. 4 also shows three leaflets 258 (leaflet cusps or pockets) mounted within a foldable and compressible inner wire frame 231 (also referred to as “leaflet frame”), the leaflet frame 231 is mounted within an annular outer support frame 102 (also referred to as “outer wire frame” or “outer frame”) which has a collar component 103 attached circumferentially at a top edge 107 of the outer frame 102, a pair of integrated, independent tab components 269, 271, and a mesh component 226 (also referred to herein as “mesh sidewall cover” or “mesh cover”), according to the invention. Uncovered regurgitation frame 139 provides for controlled regurgitation of the valve. The uncovered regurgitation frame 139 can be later plugged with a later inserted stent or cover or plug once regurgitation is no longer needed by the patient.

[0166] Atrial collar 103 is shaped to conform to the native deployment location. In a tricuspid 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 right ventricular outflow tract (RVOT) subannular area.

[0167] Integrated tabs 269 and 271 are unitary construction with the body of the outer frame 102. The tabs may vary in size and shape. In a preferred embodiment, the RVOT tab, e.g., 269 may be longer to reach into the entry of the pulmonary artery (in the case of a tricuspid replacement).

[0168] FIG. 5 is an illustration of a side perspective view of an orthogonally deliverable transcatheter heart valve 100 in a folded configuration along the z-axis (front to back when viewed from the broader side) according to the invention. FIG. 5 shows a folded (flattened) outer frame 102 with folded/flattened collar 103, hinge points 116, 120. FIG. 5 also shows a folded/flattened inner regurgitation control component 137 with radio-opaque markers 144, and leaflets 258 mounted within a folded/flattened inner leaflet frame 231.

[0169] FIG. 6 is an illustration of a side perspective view of an orthogonally deliverable transcatheter heart valve 100 in a vertically compressed configuration according to the invention. FIG. 6 shows the outer frame 102 folded (z-axis) and compressed vertically (y-axis) with the collar 103 folded (z-axis) and compressed (y-axis), along a fold line between hinge points 116, 120. FIG. 6 also shows an inner regurgitation control component 137, and leaflets 258 mounted within an inner leaflet frame 231.

[0170] FIG. 7 is an illustration of a side perspective view of an orthogonally deliverable transcatheter heart valve 100 partially loaded into a delivery catheter 138, according to the invention. FIG. 7 shows an outer frame 102, a folded collar 103, an inner regurgitation control component 137, and a flow control component 130 having leaflets 258 and an inner leaflet frame 231.

[0171] FIG. 8 is an illustration of an end view of the delivery catheter 138 showing the loaded valve 100 with outer frame 102 and collar 103 visible, according to the invention.

[0172] FIG. 9 is an illustration of a top view of the folded, compressed valve 100 being expelled from the delivery catheter 138, in a partial position to allow expansion of the leaflets 258, the collar 103, and the inner leaflet frame 231 prior to seating in the native annulus.

[0173] FIG. 10 is an illustration of a top perspective view of a valve 100 without a collar having an inner regurgitation control component 137 removed for viewing, with a tissue cover 141, a reinforcement ring 143 and a drum channel 135 shown. FIG. 10 also shows an outer frame 102 with a mesh sidewall cover 226, an inner leaflet frame 231, and leaflets 258 sewn into the inner leaflet frame 231, according to the invention.

[0174] FIG. 11 is an illustration of a top perspective view of a valve 100 without a collar having markers 144, and an inner regurgitation control component 137 mounted on the top edge 107 of the outer frame 102, the outer frame 102 also having a mesh sidewall cover 226, an inner leaflet frame 231, and leaflets 258 sewn into the inner leaflet frame 231, according to the invention.

[0175] FIG. 12 is an illustration of a bottom perspective view of a valve 100 without a collar having an inner regurgitation control component 137 mounted on the top edge 107 of the outer frame 102, the outer frame 102 also having a mesh sidewall cover 226, an inner leaflet frame 231, and leaflets 258 sewn into the inner leaflet frame 231, according to the invention.

[0176] FIG. 13 is an illustration of an exploded view of a valve without a collar having an inner regurgitation control component 137 comprising a tissue cover 141 and a regurgitation frame 139. FIG. 13 also shows an outer frame 102, the outer frame 102 having a mesh sidewall cover 226, an inner leaflet frame 231, and leaflets 258 mounted on a structural band 257 (also referred to herein as “band”) and sewn into the inner leaflet frame 231, according to the invention.

[0177] FIG. 14 is an illustration of a top perspective view of an inner leaflet frame 231 (or a regurgitation frame), in a cylinder configuration, shown at the beginning of a process permitting folding and compression of the inner leaflet frame, according to the invention.

[0178] FIG. 15 is an illustration of a top perspective view of an inner leaflet frame 231 (or a regurgitation frame) in a partially folded configuration with the wireframe sidewalls rotating or hinging at their lateral connection points 116, 120 (also referred to as “hinge points”), shown as a partial first step in a process permitting folding and compression of the inner leaflet frame 231, according to the invention.

[0179] FIG. 16 is an illustration of a side view of an inner leaflet frame 231 (or a regurgitation frame) in a completely folded configuration 208 with the wireframe sidewalls rotated or hinged at their lateral connection points, shown as a completed first step in a process permitting folding and compression of the inner leaflet frame 231, according to the invention.

[0180] FIG. 17 is an illustration of a side view of an inner leaflet frame 231 (or a regurgitation frame) in a folded and vertically compressed configuration 210 with the wireframe sidewalls vertically compressed in a pleated or accordion configuration, shown as a second step in a process permitting folding and compression of the inner leaflet frame 231, according to the invention.

[0181] FIG. 18 is an illustration of a side view of an inner leaflet frame 231 (or a regurgitation frame) as a linear wireframe sheet 202 before further assembly into a cylinder structure, according to the invention.

[0182] FIG. 19 is an illustration of a side perspective view of an inner leaflet frame 231 in a cylinder or cylinder-like (conical, etc.) configuration, according to the invention.

[0183] FIG. 20 is an illustration of a side perspective view of a band of pericardial tissue 257 (also referred to herein as a “structural band”) that is configured in a cylinder shape with leaflets 258 (also referred to herein as “leaflet pockets”) sewn into the structural band 257, according to the invention.

[0184] FIG. 21 is an illustration of a side view of a band of pericardial tissue 257 with leaflet pockets 258 sewn into the structural band 257, before assembly into a cylindrical leaflet component and mounting on an inner leaflet frame to form a collapsible (foldable, compressible) flow control component, according to the invention.

[0185] FIG. 22 is an illustration of a bottom view of a band of pericardial tissue 257 with leaflet pockets 258 sewn into the structural band 257, before assembly into a cylindrical leaflet component and mounting on an inner leaflet frame to form a collapsible (foldable, compressible) flow control component, according to the invention.

[0186] FIG. 23 is an illustration of a side perspective view of part of a band of pericardial tissue 257 with a single leaflet pocket 258 sewn into the structural band 257, showing partial coaptation of the leaflet pocket 258 with open edge 261 extending out and a sewn edge 259 as a closed top parabolic edge providing attachment, according to the invention.

[0187] FIG. 24 is an illustration of a bottom view of a cylindrical leaflet component showing complete coaptation, to form a closed fluid-seal, according to the invention.

[0188] FIGS. 25A-25E are illustrations of a process whereby a valve having a pre-perforated drum inner is orthogonally delivered within the catheter, expelled from the catheter, and deployed into the native annulus. FIG. 25A shows a compressed and folded orthogonal valve within a delivery catheter and moving along a guide wire through a native annulus. FIG. 25B shows an orthogonal being partially expelled into the native annulus, with the delivery catheter able to torque or position the valve, as necessary. FIG. 25C shows a fully expelled valve with a RVOT tab extending subannularly to help anchor the valve and the valve held up at an angle to allow for washing and coaptation to be implemented/commenced. FIG. 25D is a top view showing the pre-perforated drum and regurgitation channel located within the perimeter of the radio-opaque markers. FIG. 25E is a side perspective view and shows the pre-perforated drum and regurgitation channel located within the perimeter of the radio-opaque markers, the inner regurgitation control component mounted within the outer support frame, adjacent the inner flow control component (leaflets and frame).

[0189] FIG. 26 is an illustration of an outer frame 102 (also referred to as “outer wire frame”).

[0190] FIG. 27 is an illustration of a top perspective view of a partially folded configuration of the outer wireframe 102 with sidewalls rotating or hinging at their lateral connection points 116, 120 (hinge points), shown as a partial first step in a process permitting folding and compression of the outer frame 102, according to the invention.

[0191] FIG. 28 is an illustration of a side view of an outer frame 102 in a completely folded, flat configuration 208 with the wireframe sidewalls rotated or hinged at their lateral connection points 116, 120 (hinge points), shown as a completed first step in a process permitting folding and compression of the outer frame 102, according to the invention.

[0192] FIG. 29 is an illustration of a side view of an outer frame 102 in a folded and vertically compressed configuration 210 with the wireframe sidewalls vertically compressed in a pleated or accordion configuration, shown as a second step in a process permitting folding and compression of the outer frame 102, according to the invention.

[0193] FIG. 30 is an illustration of a top perspective view of an assembled valve 100 with an inner regurgitation control component 137 having markers and a reinforcing ring, an outer frame 102, a flow control component 130 having an inner leaflet frame 231 and three leaflets 258 (leaflet pockets/cusps), an inner spacer frame 139, and a tissue cover 141 over the spacer frame 139, fold-line 109 is shown as a dashed line, according to the invention.

[0194] FIG. 31 is an illustration of a top perspective view of an assembled valve 100 with an inner regurgitation control component 137 having markers, an outer frame 102, a first sub-annular anchoring/positioning tab 268 mounted on the outer frame 102 adjacent the flow control component 130, a second sub-annular anchoring/positioning tab 270 mounted on the outer frame 102 in a different location, the flow control component 130 having an inner leaflet frame and three leaflets 258 (leaflet pockets/cusps), an inner spacer frame 139, and a tissue cover 141 over the spacer frame 139, fold-line 109 is shown as a dashed line and crosses the tissue cover 141, according to the invention.

[0195] FIG. 32 is an illustration of a bottom perspective view of an assembled valve 100 with an outer frame 102, a first sub-annular anchoring/positioning tab 268 mounted on the outer frame 102 adjacent the flow control component 130, a second sub-annular anchoring/positioning tab 270 mounted on the outer frame 102 in a different location, the flow control component 130 having an inner leaflet frame 231 and three leaflets 258 (leaflet pockets/cusps), an inner spacer frame 139 and a tissue cover 141 over the spacer frame 139, fold-line 109 is shown as a dashed line, and hemodynamic washing cavity is shown under the covered inner spacer frame 139, according to the invention.

[0196] FIG. 33 is an illustration of a top view of an assembled valve 100 with an inner regurgitation control component 137, an outer frame 102, a flow control component 130 having an inner leaflet frame 231 and three leaflets 258 (leaflet pockets/cusps), an inner spacer frame 139, and a tissue cover 141 over the spacer frame 139, according to the invention.

[0197] FIG. 34 is an illustration of a top view of an assembled valve 100 with an inner regurgitation control component 137 having reinforcement ring, an outer frame 102, a first sub-annular anchoring/positioning tab 268 mounted on the outer frame 102 adjacent the flow control component 130, a second sub-annular anchoring/positioning tab 270 mounted on the outer frame 102 in a different location, the flow control component 130 having an inner leaflet frame 231 and three leaflets 258 (leaflet pockets/cusps), an inner spacer frame 139, and a tissue cover 141 over the spacer frame 139, according to the invention.

[0198] FIGS. 35A-35E is an illustration of a step by step process where the tissue drum is perforated prior to loading the valve orthogonally into the delivery catheter. FIG. 35A shows a step of providing an orthogonal prosthetic valve as described herein (foldable, compressible for sideways delivery with RVOT tab, guide wire lumen, atrial collar, and proximal tab). FIG. 35B shows a step of creating an opening by cutting or using a balloon device. FIG. 35C shows a step of folding the valve flat to prepare for loading into the delivery catheter. FIG. 35D shows a step of vertically compressing the valve to prepare for loading the valve into the delivery catheter.

[0199] FIG. 35E shows a step of loading the orthogonal valve sideways into the delivery catheter.

[0200] FIGS. 36A-36C is an illustration of a step by step process where the tissue drum is perforated after the valve is expelled orthogonally from the delivery catheter, and deployed into the native annulus. FIG. 36A shows a step of expelling the valve into the native annulus, approaching horizontally at a slightly raise angle to position the RVOT tab into the subannular space leading to the right (pulmonary) valve outflow tract. FIG. 36B shows a step of locating the radio-opaque markers using fluoroscopy. FIG. 36C shows a step of creating an opening by cutting or using a balloon device.

[0201] FIG. 37 is an illustration of how a user can match the size of the aperture to the amount of regurgitation desired, e.g., a range from 0.5-2.0 grades of regurgitation. Radio-opaque markers can be used to aide in measuring how large of a perforation to make.

[0202] FIG. 38 is an illustration of how a user can match the size of the lumen of a tubular stent that can be deployed into the aperture to match the amount of regurgitation desired, e.g., a range from 0.5-2.0 grades of regurgitation.

[0203] FIG. 39 is an illustration of a side septal plan view of a valve 100 with sub-annular anchoring and/or positioning tab 268 extending towards a distal side, and second sub-annular tab 270 extending away to a proximal side, and with foldable and compressible wireframe construction visible (outer frame 102), including inner leaflet frame 231, leaflets 258, and inner regurgitation control component 137, according to the invention.

[0204] FIGS. 40A-40F is an illustration of a closure device used to close a perforation in an inner regurgitation control component. FIG. 40A shows a step of providing an orthogonal prosthetic valve as described herein (foldable, compressible for sideways delivery with RVOT tab, guide wire lumen, atrial collar, and proximal tab) that has an inner regurgitation control component in need of sealing off. FIG. 40B shows a step of accessing the perforation using a catheter tool.

[0205] FIG. 40C shows a step of expanding a first disk or button on the distal, underside of the perforation. FIG. 40D shows a step of expanding a second disk or button on the proximal, top-side of the perforation. FIG. 40E shows a step of cinching the two disks/buttons together, creating a seal to stop the regurgitation that was engineered in the, e.g., 1-2 mm perforation. FIG. 40F shows a step of withdrawing the catheter tool.

[0206] FIG. 41 is an illustration of a top view of a valve 100 partially expelled from a delivery catheter 138, with a distal tab 268 leading the valve 100 (along guide wire not shown) to the deployment location, with distal flow control component 130 beginning to open and showing two of three leaflets 258 opening from a folded, lie-flat configuration with the third leaflet opening from a folded configuration where it is folded back on itself when in the delivery catheter 138.

[0207] FIG. 42 is an illustration of a top view of a valve compressed 136 (orthogonally loaded) within a delivery catheter 138 with an outer frame 102 having a first tab 268 extending forward along an x-axis and a second trailing tab 270 extending backwards along the x-axis.

[0208] FIG. 43 is an illustration of a top view of a valve 100 having an outer frame 102, an off-center inner flow control component 130 (leaflet in frame) and an irregularly shaped spacer/support frame 139A, according to the invention.

[0209] FIG. 44 is an illustration of a top view of a valve 100 having an outer frame 102, a centrally located inner flow control component 130 (leaflet in frame) and a pair of irregularly shaped spacer/support frames 139A, 139B on opposing sides of the inner flow control component 130, according to the invention.

[0210] FIG. 45 is an illustration of a top view of a valve 100 having an outer frame 102, and an inner flow control component 130 (leaflet in frame) and a plurality of sewn attachment points 129 where the inner flow control component 130 is sewn to the outer frame 102, according to the invention.

[0211] FIG. 46 is an illustration of a top view of a valve 100 having an inner regurgitation control component 137 with a pacemaker and lead wire set 145 extending through a perforation. FIG. 46 also shows an outer frame 102, an off-center inner flow control component 130 having an inner leaflet frame 231 and leaflets 258, and an inner spacer frame 139, all three structures foldable along the same x-axis 109, according to the invention.

[0212] FIG. 47 is an illustration of a top view of a valve 100 having an outer frame 102, a centrally positioned inner flow control component 130 having an inner leaflet frame 231 and leaflets 258, and a pair of smaller cylindrical inner regurgitation control components 137, 147 mounted on opposing sides of the inner flow control component 130 to provide support within the interior dimension of the outer frame 102, all four structures foldable along the same x-axis 109, according to the invention. Here, the first inner regurgitation control component 137 has a three-leaflet mini-valve mounted adjacent next to the main flow control component 130, and the second inner regurgitation control component 147 has an un-perforated tissue cover, which may later provide an opportunity for a practitioner to add additional regurgitation as necessary.

[0213] FIG. 48 is an illustration of a top view of a valve 100 having a distal side inner regurgitation control component 137, an outer frame 102, and a proximally located off-set inner flow control component 130 having an inner leaflet frame 231 and leaflets 258, all three structures foldable along the same x-axis 109, according to the invention.

[0214] FIG. 49 shows orthogonal delivery steps: (1) provide a foldable, compressible prosthetic tricuspid valve; (2) load the valve sideways into a delivery catheter 138; (3) advance the valve to the heart via the IVC or the SVC over a pre-placed guidewire that is threaded onto a subannular distal tab; (4) partially expel the valve to position the distal subannular tab and to allow the valve leaflets to begin functioning; (5) complete deployment of the valve into the native annulus. (6) Optionally: if the regurgitation drum was not opened prior to loading into the delivery catheter, a cutting tool or balloon tool can be advanced, and a 1-2 mm opening is made in the tissue covering of the drum frame. (7) Optionally: a pacemaker wire set can be advanced through the opening in the regurgitation drum and the pacemaker wire(s) attached at or near the target nodes.

[0215] 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.

• [0216] 100 Dual-tab orthogonally delivered transcatheter prosthetic heart valve.
• [0217] 102 Self-expanding annular (outer) support frame.
• [0218] 103 Collar structure.
• [0219] 104 Central channel.
• [0220] 106 Outer perimeter wall.
• [0221] 107 Top edge of outer support frame.
• [0222] 108 Central vertical axis.
• [0223] 109 Z-axis, front to back, fold line axis.
• [0224] 110 Front wall portion of perimeter wall.
• [0225] 112 Back wall portion of perimeter wall.
• [0226] 114 Proximal side.
• [0227] 116 Proximal fold area.
• [0228] 117 Secondary proximal fold areas.
• [0229] 118 Distal side.
• [0230] 120 Distal fold area.
• [0231] 121 secondary distal fold areas.
• [0232] 122 Front upper collar portion.
• [0233] 124 Front lower body portion of outer frame.
• [0234] 126 Back upper collar portion.
• [0235] 128 Back lower body portion.
• [0236] 129 Sewn attachment points for inner to outer.
• [0237] 130 Flow control component, made of an inner frame having tissue leaflets mounted therein, collapsible (foldable and compressible), the inner mounted within the annular outer support frame and configured to permit blood flow in a first direction through an inflow end and block blood flow in the opposite, second direction, through the outflow end.
• [0238] 132 Inflow end.
• [0239] 134 Outflow end.
• [0240] 135 Drum channel.
• [0241] 136 Compressed configuration
• [0242] 137 Inner regurgitation control component.
• [0243] 138 Delivery catheter.
• [0244] 139 Uncovered regurgitation frame, engineered (therapy) partial regurgitation
• [0245] 140 X-axis, a horizontal axis, parallel to delivery, catheter central axis
• [0246] 141 Tissue cover (plastic deformation).
• [0247] 142 Intersecting angle 45-135 degrees, X-axis to Y-axis.
• [0248] 143 Reinforcement ring.
• [0249] 144 Radio-opaque markers.
• [0250] 146 Length-wise cylindrical axis of delivery catheter.
• [0251] 148 Height of about 5-60 mm.
• [0252] 150 Diameter of about 25-80 mm.
• [0253] 202 Plurality of compressible wire cells—outer frame.
• [0254] 204 Orientation and cell geometry substantially orthogonal to the central vertical axis to minimize wire cell strain when the annular support frame is compressed.
• [0255] 206 Vertical compressed configuration.
• [0256] 208 Folded configuration.
• [0257] 210 Folded and compressed configuration.
• [0258] 212 Inner frame or outer frame shape selected from a funnel, cylinder, flat cone, or circular hyperboloid.
• [0259] 220 Braided matrix.
• [0260] 222 Wire frame matrix.
• [0261] 224 Laser-cut wire frame.
• [0262] 226 Biocompatible material.
• [0263] 227 Flared cuff on inner frame.
• [0264] 228 Side profile of inner frame as a flat cone shape.
• [0265] 229 Non-cylindrical inner frame, e.g., elliptical section.
• [0266] 230 Diameter R of 40-80 mm.
• [0267] 231 Inner frame, for mounting leaflets.
• [0268] 232 Diameter r of 20-60 mm.
• [0269] 233 Set of uniform wire frame cells of inner.
• [0270] 234 Height of 5-60 mm.
• [0271] 235 Non-uniform variable height cells of inner.
• [0272] 236 Interior surface of annular outer support frame.
• [0273] 237 Non-uniform cell geometries, sizes in wire frame.
• [0274] 238 Exterior surface of annular outer support frame.
• [0275] 239 Compressed inner.
• [0276] 240 Pericardial tissue for covering valve surfaces.
• [0277] 241 Diamond or eye-shaped wire cells.
• [0278] 242 Woven synthetic polyester material.
• [0279] 243 Eyelets on inner wire frame, consistent commissure attachment.
• [0280] 244 Outer support frame with an hourglass shape.
• [0281] 245 Laser cut attachment feature on inner frame.
• [0282] 246 Top diameter R1 of 40-80 mm.
• [0283] 248 Bottom diameter R2 of 50-70 mm.
• [0284] 250 Internal diameter r of 20-60 mm.
• [0285] 252 Height of 5-60 mm.
• [0286] 254 Internal diameter of 20-60 mm.
• [0287] 256 Height of 10-40 mm.
• [0288] 257 Leaflet band, mounting band for leaflet pockets.
• [0289] 258 Leaflets, plurality of leaflets, pericardial material.
• [0290] 259 Sewn edge of leaflet.
• [0291] 260 Rounded cylinder at an inflow end.
• [0292] 261 Open edge of leaflet
• [0293] 262 Flat closable aperture at an outflow end.
• [0294] 264 Longitudinal supports in/on flow control component, selected from rigid or semi-rigid posts, rigid or semi rigid ribs, rigid or semi-rigid battons, rigid or semi rigid panels, and combinations.
• [0295] 266 (any) lumen (ball) on distal tab.
• [0296] 268 Distal tab/sub-annular anchoring tab, can be RVOT or other, comprised of wire loop or wire frame, integrated frame section, or stent, extending from about 10-40 mm away from the annular support frame.
• [0297] 269 Independent RVOT tab.
• [0298] 270 Proximal tab/sub-annular anchoring tab.
• [0299] 271 Independent proximal tab.
• [0300] 272 Distal upper edge of the annular support frame.
• [0301] 273 Upper atrial tension arm comprised of wire loop or wire frame extending from about 2-20 mm
• [0302] away from the annular support frame.
• [0303] 274 Lower tension arm comprised of wire loop or wire frame, integrated frame section, or stent, extending from about 10-40 mm away from the annular support frame.
• [0304] 276 Distal side of the annular support frame.
• [0305] 278 Tissue anchors connected to the annular support frame for engaging native tissue.
• [0306] 280 Front wall portion of frame is a first flat panel.
• [0307] 282 Back wall portion of frame is a second flat panel.
• [0308] 284 Sewn seam.
• [0309] 285 Hinge.
• [0310] 286 Flexible fabric span without any wire cells.
• [0311] 287 Fabric panel.
• [0312] 288 Braided-wire cells.
• [0313] 289 Commissure attachment—leaflet to frame.
• [0314] 290 Laser-cut wire cells.
• [0315] 302 Rolling into a compressed configuration.
• [0316] 304 Bilaterally roll compressed configuration.
• [0317] 306 Flattening the annular support frame panels.
• [0318] 308 Compressed annular support frame from top to bottom.
• [0319] 310 Sheath/Rigid elongated pushing rod/draw wire.
• [0320] 311 Guide wire.
• [0321] 312 Steerable catheter for rotating the heart valve prosthesis along an axis parallel to the plane of the valve annulus, wherein an upper tension arm mounted on the valve is conformationally pressure locked against supra-annular tissue, and wherein a lower tension arm mounted on the valve is conformationally pressure locked against sub-annular tissue.

[0322] 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.

[0323] 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.