Patent Publication Number: US-2023157816-A1

Title: Ventricular stability elements for side-deliverable prosthetic heart valves and methods of delivery

Description:
CROSS-REFERENCE TO RELATED APPLICATIONS 
     This application is a continuation of International Patent Application No. PCT/US2021/013570, filed Jan. 15, 2021, entitled “Ventricular Stability Elements for Side-Deliverable Prosthetic Heart Valve and Methods of Delivery,” which claims priority to and the benefit of U.S. Provisional Patent Application Ser. No. 62/962,902, filed Jan. 17, 2020, entitled “Ventricular Stability Tab for Side-Delivered Transcatheter Heart Valve and Methods of Delivery,” the disclosures of which are incorporated herein by reference in their entireties. 
    
    
     BACKGROUND 
     Embodiments are described herein that relate to prosthetic heart valves, and devices and methods for use in the delivery and deployment of such valves. 
     Prosthetic heart valves can pose challenges for delivery and deployment within a heart, particularly for delivery by catheters through the patient&#39;s vasculature rather than through a surgical approach. Delivery of traditional transcatheter prosthetic valves generally includes compressing the valve in a radial direction and loading the valve into a delivery catheter such that a central annular axis of the valve is parallel to the lengthwise axis of the delivery catheter. The valves are deployed from the end of the delivery catheter and expanded outwardly in a radial direction from the central annular axis. The expanded size (e.g., diameter) of traditional valves, however, can be limited by the internal diameter of the delivery catheter. The competing interest of minimizing delivery catheter size presents challenges to increasing the expanded diameter of traditional valves (e.g., trying to compress too much material and structure into too little space). 
     Some transcatheter prosthetic valves can be configured for orthogonal delivery, which can have an increased expanded diameter relative to traditional valves. In orthogonal delivery, for example, the valve is compressed and loaded into a delivery catheter such that a central annular axis of the valve is substantially orthogonal to the lengthwise axis of the delivery catheter, which can allow the valve to be compressed laterally and extended longitudinally (e.g., in a direction parallel to the lengthwise axis of the delivery catheter). With traditional and/or orthogonally delivered transcatheter prosthetic valves, it is also desirable to provide one or more ways of anchoring, securing, and/or stabilizing the valve in the native annuls without substantially increasing a compressed size of the valve. 
     Accordingly, a need exists for prosthetic valves with one or more anchoring and/or stabilizing features while maintaining a relatively small compressed size that allows for transcatheter delivery of the valve. 
     SUMMARY 
     The embodiments described herein relate generally to transcatheter prosthetic valves and methods for delivering transcatheter prosthetic valves. In some embodiments, a prosthetic heart valve includes a valve frame defining an aperture that extends along a central axis and a flow control component mounted within the aperture. The flow control component is configured to permit blood flow along the central axis in a first direction from an inflow end to an outflow end of the flow control component and block blood flow in a second direction, opposite the first direction. The valve frame includes a distal anchoring element, a proximal anchoring element, and a septal subannular anchoring element. The prosthetic heart valve has a compressed configuration for side-delivery to a heart of a patient via a delivery. The prosthetic heart valve is configured to transition from the compressed configuration to an expanded configuration when released from the delivery catheter. The prosthetic heart valve is configured to be seated in an annulus of a native valve of the heart when in the expanded configuration. The distal, proximal, and septal anchoring elements are configured to be inserted through the annulus of the native valve prior to the prosthetic heart valve being fully seated therein. The septal anchoring element is configured to extend below the annulus and contact ventricular septal tissue to stabilize the prosthetic heart valve in the annulus when the prosthetic heart valve is seated in the annulus. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         FIGS.  1 - 5    are schematic illustrations of a side-deliverable transcatheter prosthetic valve according to an embodiment. 
         FIG.  6    is a side perspective view illustration of a side-deliverable transcatheter prosthetic valve having a valve frame with a septal area stability element, a distal anchoring element, and a proximal anchoring element, according to an embodiment. 
         FIG.  7    is a distal-end side perspective view illustration of a side-deliverable transcatheter prosthetic valve having a valve frame with a septal area stability element, a distal anchoring element, and a proximal anchoring element, according to an embodiment. 
         FIG.  8    is a posterio-anterior underside perspective view illustration of a side-deliverable transcatheter prosthetic valve having a valve frame with a septal area stability element, a distal anchoring element, and a proximal anchoring element, according to an embodiment. 
         FIG.  9    is a topside perspective view illustration of a side-deliverable transcatheter prosthetic valve having a valve frame with a septal area stability element, a distal anchoring element, and a proximal anchoring element, according to an embodiment. 
         FIG.  10    is a side perspective view illustration of a wire frame for a side-deliverable transcatheter prosthetic valve highlighting a septal area stability element, according to an embodiment. 
         FIG.  11    is a side view illustration of a side-deliverable transcatheter prosthetic valve positioned in an annulus of a native tricuspid valve prior to stabilizing and/or anchoring the prosthetic valve according to an embodiment. 
         FIG.  12    is a side view illustration of the prosthetic valve of  FIG.  11    positioned in the annulus of the native tricuspid valve showing a valve frame with at least a distal anchoring element, a septal area stability element, and an anterior anchoring element engaging native tissue to stabilize and/or anchor the prosthetic valve in the annulus. 
         FIG.  13    is a side perspective view illustration of a side-deliverable transcatheter prosthetic valve having a valve frame with a distally located septal area stability element, a distal anchoring element, and a proximal anchoring element, according to an embodiment. 
         FIG.  14    is a side perspective view illustration of a side-deliverable transcatheter prosthetic valve having a valve frame with a proximally located septal area stability element, a distal anchoring element, and a proximal anchoring element, according to an embodiment. 
         FIG.  15    is a side perspective view illustration of a side-deliverable transcatheter prosthetic valve having a valve frame with a shortened centrally located septal area stability element, a distal anchoring element, and a proximal anchoring element, according to an embodiment. 
         FIG.  16    is a side perspective view illustration of a side-deliverable transcatheter prosthetic valve having a valve frame with an extended-depth septal area stability element, a distal anchoring element, and a proximal anchoring element, according to an embodiment. 
         FIG.  17    is a side perspective view illustration of a side-deliverable transcatheter prosthetic valve having a valve frame with an asymmetric-shaped septal area stability element, a distal anchoring element, and a proximal anchoring element, according to an embodiment. 
         FIG.  18    is a side perspective view illustration of a wire-braid framed transcatheter prosthetic valve having a valve frame with a septal area stability element, a distal anchoring element, and a proximal anchoring element, according to an embodiment. 
         FIG.  19    is a side perspective view illustration of a laser-cut framed transcatheter prosthetic valve having a valve frame with a septal area stability element, a distal anchoring element, and a proximal anchoring element, according to an embodiment. 
         FIGS.  20  and  21    are a proximal side view illustration and a distal side view illustration, respectively, of a side-deliverable transcatheter prosthetic valve having a valve frame with a septal area stability element, a distal anchoring element ( FIG.  20   ), and a proximal anchoring element ( FIG.  21   ), according to an embodiment. 
         FIG.  22    is a flowchart illustrating a method of deploying a prosthetic heart valve in an annulus of a native valve of a heart of a patient, according to an embodiment. 
     
    
    
     DETAILED DESCRIPTION 
     Disclosed embodiments are directed to transcatheter prosthetic heart valves and/or components thereof, and methods of manufacturing, loading, delivering, and/or deploying the transcatheter prosthetic valves and/or components thereof. The transcatheter prosthetic heart valves can have a valve frame having at least a septal subannular anchoring element mounted on a septal side of the valve frame and a flow control component mounted within a central lumen or aperture of the valve frame. The flow control component can be configured to permit blood flow in a first direction through an inflow end of the valve and block blood flow in a second direction, opposite the first direction, through an outflow end of the valve. The valves described herein can be compressible and expandable along a long-axis (also referred to as a longitudinal axis) substantially parallel to a lengthwise cylindrical axis of a delivery catheter used to deliver the valves. The valves can be configured to transition between a compressed configuration for introduction into the body using the delivery catheter, and an expanded configuration for implanting at a desired location in the body. 
     In some implementations, the embodiments described herein are directed to a prosthetic heart valve that is a low-profile, side-delivered implantable prosthetic heart valve. The prosthetic heart valves can have at least a ring-shaped or annular valve frame, an inner flow control component (e.g., a 2-leaflet or 3-leaflet sleeve, and/or the like) mounted in the valve frame, a distal anchoring element (e.g., a subannular distal anchoring element, tab, or the like) configured to extend into the right ventricular outflow tract (RVOT), a septal anchoring element configured to extend down the septal wall to pin the septal leaflet away from the coapting leaflets of the prosthetic valve, and a proximal anchoring element (e.g., a subannular proximal anchoring element, tab, or the like) configured to extend into the proximal subannular space, preferably between the septal and the posterior leaflets of the heart. 
     In some embodiments, a prosthetic heart valve includes a valve frame defining an aperture that extends along a central axis and a flow control component mounted within the aperture. The flow control component is configured to permit blood flow along the central axis in a first direction from an inflow end to an outflow end of the flow control component and block blood flow in a second direction, opposite the first direction. The valve frame includes a distal anchoring element, a proximal anchoring element, and a septal subannular anchoring element. The prosthetic heart valve has a compressed configuration for side-delivery to a heart of a patient via a delivery. The prosthetic heart valve is configured to transition from the compressed configuration to an expanded configuration when released from the delivery catheter. The prosthetic heart valve is configured to be seated in an annulus of a native valve of the heart when in the expanded configuration. The distal, proximal, and septal anchoring elements are configured to be inserted through the annulus of the native valve prior to the prosthetic heart valve being fully seated therein. The septal anchoring element is configured to extend below the annulus and contact ventricular septal tissue to stabilize the prosthetic heart valve in the annulus when the prosthetic heart valve is seated in the annulus. 
     In some implementations, the distal anchoring element is configured to engage, for example, ventricular tissue distal to the annulus, the proximal anchoring element is configured to engage, for example, ventricular tissue proximal to the annulus, and the septal anchoring element is configured to engage, for example, at least one of a native septal wall or a native septal leaflet when the prosthetic heart valve is seated in the annulus. In some implementations, the septal anchoring element can stabilize the valve against any intra-annular rolling forces and/or any intra-annular twisting forces that might affect a desired location or positioning of the prosthetic valve within the annulus, (e.g., tilted, angled, twisted, rolled, etc.). 
     In some embodiments, a prosthetic heart valve includes a valve frame having a transannular section and a supra-annular section (e.g., an atrial collar) attached around a top edge of the transannular section, a distal anchoring element coupled to the transannular section, a proximal anchoring element coupled to the transannular section, a septal anchoring element coupled to the transannular section, and a flow control component mounted within the valve frame. The flow control component is configured to permit blood flow in a first direction from an inflow end to an outflow end of the prosthetic heart valve and to block blood flow in a second direction, opposite the first direction. The prosthetic heart valve has a compressed configuration for introduction into a heart of a patient via a delivery catheter and an expanded configuration when the prosthetic heart valve is released from the delivery catheter into the heart. The prosthetic heart valve is configured to be seated in an annulus of a native valve of the heart when in the expanded configuration. When the prosthetic heart valve is seated in the annulus of the native valve, the distal anchoring element is configured to be disposed in a ventricular outflow tract, he proximal anchoring element is configured to be disposed in a proximal subannular area of the heart, and the septal anchoring element is configured to extend below the annulus and contact at least one of a native septal wall or a native septal leaflet. 
     In some embodiments, a side-deliverable transcatheter prosthetic heart valve includes (i) a self-expanding annular support frame, said annular support frame with an outer perimeter wall having at least a distal side, a proximal side, and a septal side and circumscribing a central channel extending along a central vertical axis in an expanded configuration; (ii) a flow control component mounted within the annular support frame and configured to permit blood flow in a first direction through an inflow end of the valve and block blood flow in a second direction, opposite the first direction, through an outflow end of the valve; (iii) a distal subannular anchoring element mounted on the distal side of the annular support frame; (iv) a proximal subannular anchoring element mounted on the proximal side of the annular support frame; and (v) a septal subannular anchoring element or tab mounted on the septal side of the annular support frame. The valve is compressible to a compressed configuration for introduction into the body using a delivery catheter. The valve in the compressed configuration has a height of 8-12 mm, a width of 8-12 mm, and a length of 25-80 mm. A horizontal axis of the valve in the compressed configuration is substantially parallel to a lengthwise cylindrical axis of the delivery catheter. The valve in the expanded configuration has a height of about 5-60 mm and a diameter of about 25-80 mm. In some implementations, the valve in the compressed configuration can be oriented such that the horizontal axis is at an intersecting angle of between 45-135 degrees to the central vertical axis. In some implementations, the valve in the expanded configuration can be oriented such that the horizontal axis is at an intersecting angle of between 45-135 degrees to the central vertical axis. 
     Any of the prosthetic heart valves described herein can be configured to transition between an expanded configuration and a compressed configuration. For example, any of the embodiments described herein can be a balloon-inflated prosthetic heart valve, a self-expanding prosthetic heart valve, and/or the like. 
     Any of the prosthetic heart valves described herein can be compressible—into the compressed configuration—in a lengthwise or orthogonal direction relative to the central axis of the flow control component that can allow a large diameter valve (e.g., having a height of about 5-60 mm and a diameter of about 20-80 mm) to be delivered and deployed from the inferior vena cava directly into the annulus of a native mitral or tricuspid valve using, for example, a 24-36Fr delivery catheter and without delivery and deployment from the delivery catheter at an acute angle of approach. 
     Any of the prosthetic heart valves described herein can have a central axis when in a compressed configuration that is co-axial or at least substantially parallel with blood flow direction through the valve. In some embodiments, the compressed configuration of the valve is orthogonal to the blood flow direction. In some embodiments, a long-axis is oriented at an intersecting angle of between 45-135 degrees to the first direction when in the compressed configuration and/or the expanded configuration. 
     In some embodiments, the annular support frame is a compressible wire frame including one of braided-wire cells, laser-cut wire cells, photolithography produced wire cells, 3D printed wire cells, wire cells formed from intermittently connected single strand wires in a wave shape, a zig-zag shape, or spiral shape, and combinations thereof. 
     Any of the prosthetic heart valves described herein can include a septal anchoring element extending from a lower septal side of a frame of the prosthetic heart valve, which can be used, for example, as a septal tissue and/or leaflet anchoring and/or stabilization element or tab. The septal anchoring element can include and/or can be formed from a wire loop or wire frame, an integrated frame section, and/or a stent, extending from the frame (e.g., about 10-40 mm away from the frame). 
     Any of the prosthetic heart valves described herein can include a distal anchoring element extending from a lower distal side of the frame of the prosthetic heart valve, which can be used, for example, as a ventricular outflow tract tab. The distal anchoring element can include and/or can be formed from a wire loop or wire frame, an integrated frame section, and/or a stent, extending from the frame (e.g., about 10-40 mm away the tubular frame). 
     Any of the prosthetic heart valves described herein can include a proximal anchoring element extending from a lower proximal side of the frame of the prosthetic heart valve, which can be used, for example, as a proximal tissue and/or area anchoring and/or stabilization tab. The proximal anchoring element can include and/or can be formed from a wire loop or wire frame, an integrated frame section, and/or a stent, extending away from the frame (e.g., about 10-40 mm away from the frame). The proximal anchoring element can be one of a fixed anchoring element or an anchoring element configured to transition from a first (e.g., compressed) configuration to a second (e.g., expanded) configuration after the prosthetic heart valve is seated in an annulus of a native heart valve. For example, the proximal anchoring element can be moveable from a first stowed position (e.g., held against an outer perimeter wall of the frame) while the prosthetic heart valve is being positioned in the native annulus to a second deployed position that extends away from the outer perimeter wall to provide a proximal subannular anchor. 
     Any of the prosthetic heart valves described herein can include (i) an upper anchoring element attached to a distal upper edge of the tubular frame, the upper anchoring element can include or be formed from a wire loop or wire frame extending from about 2-20 mm away from the tubular frame, and (ii) a lower anchoring element (e.g., used as a RVOT tab) extending from a distal side of the tubular frame, the lower anchoring element can include and/or can be formed from a wire loop or wire frame extending from about 10-40 mm away from the tubular frame. 
     Any of the prosthetic heart valves described herein can include a distal lower anchoring element configured to be positioned into the RVOT of the right ventricle, a proximal lower anchoring element configured to be positioned into a subannular position in contact with and/or adjacent to subannular tissue of the right ventricle on a proximal side of the annulus, and a septal subannular anchoring tab mounted on the septal side of the annular support frame and configured to be positioned into a subannular position in contact with and/or in contact with septal wall tissue and/or native septal leaflets. The prosthetic heart valve can also include a distal upper anchoring element configured to be positioned into a supra-annular position in contact with and/or adjacent to supra-annular tissue of the right atrium. The distal upper anchoring element can provide a supra-annular downward force in the direction of the right ventricle and the distal and proximal lower anchoring elements can provide a subannular upward force in the direction of the right atrium. The septal anchoring element similarly can provide an upward force in the direction of the right atrium and/or can stabilize the valve against any intra-annular rolling forces and/or any intra-annular twisting forces that might affect a desired location or positioning of the prosthetic valve within the annulus, (e.g., tilted, angled, twisted, rolled, etc.). 
     Any of the prosthetic valves and/or components thereof may be fabricated from any suitable biocompatible material or combination of materials. For example, an outer valve frame, an inner valve frame (e.g., of an inner flow control component), and/or components thereof may be fabricated from biocompatible metals, metal alloys, polymer coated metals, and/or the like. Suitable biocompatible metals and/or metal alloys can include stainless steel (e.g., 316 L stainless steel), cobalt chromium (Co—Cr) alloys, nickel-titanium alloys (e.g., Nitinol®), and/or the like. Moreover, any of the outer or inner frames described herein can be formed from superelastic or shape-memory alloys such as nickel-titanium alloys (e.g., Nitinol®). Any of the prosthetic valves and/or components thereof can include any suitable coating, covering, and/or the like. Suitable polymer coatings can include, for example, polyethylene vinyl acetate (PEVA), poly-butyl methacrylate (PBMA), translute Styrene Isoprene Butadiene (SIBS) copolymer, polylactic acid, polyester, polylactide, D-lactic polylactic acid (DLPLA), polylactic-co-glycolic acid (PLGA), and/or the like. Some such polymer coatings may form a suitable carrier matrix for drugs such as, for example, Sirolimus, Zotarolimus, Biolimus, Novolimus, Tacrolimus, Paclitaxel, Probucol, and/or the like. 
     Additional biocompatible synthetic material(s) can include, for example, polyesters, polyurethanes, elastomers, thermoplastics, thermoplastic polycarbonate urethane, polyether urethane, segmented polyether urethane, silicone polyether urethane, polyetheretherketone (PEEK), silicone-polycarbonate urethane, polypropylene, polyethylene, low-density polyethylene (LDPE), high-density polyethylene (HDPE), ultra-high density polyethylene (UHDPE), polyolefins, polyethylene-glycols, polyethersulphones, polysulphones, polyvinylpyrrolidones, polyvinylchlorides, other fluoropolymers, polyesters, polyethylene-terephthalate (PET) (e.g., Dacron), Poly-L-lactic acids (PLLA), polyglycolic acid (PGA), poly(D, L-lactide/glycolide) copolymer (PDLA), silicone polyesters, polyamides (Nylon), polytetrafluoroethylene (PTFE) (e.g., Teflon), elongated PTFE, expanded PTFE, siloxane polymers and/or oligomers, polylactones, and/or the like or block co-polymers using the same. For example, where a thin, durable synthetic material is contemplated (e.g., for a covering), synthetic polymer materials such expanded PTFE or polyester (or any of the other materials described herein) may optionally be used. 
     Any of the outer valve frames, inner valve frames (e.g., of the flow control components), and/or portions or components thereof can be internally or externally covered, partially or completely, with a biocompatible material such as pericardium. A valve frame may also be optionally externally covered, partially or completely, with a second biocompatible material such as polyester or Dacron®. Disclosed embodiments may use tissue, such as a biological tissue that is a chemically stabilized pericardial tissue of an animal, such as a cow (bovine pericardium), sheep (ovine pericardium), pig (porcine pericardium), or horse (equine pericardium). Preferably, the tissue is bovine pericardial tissue. Examples of suitable tissue include that used in the products DuraGuard®, Peri-Guard®, and Vascu-Guard®, all products currently used in surgical procedures, and which are marketed as being harvested generally from cattle less than 30 months old. Alternatively, disclosed embodiments may use and/or may be covered, partially or completely, with a biocompatible synthetic such as any of those described above. 
     Any method for delivering prosthetic heart valves described herein can include side/orthogonal delivery of the prosthetic heart valve to a desired location in the body that includes advancing a delivery catheter to the desired location in the body and delivering the prosthetic heart valve in a compressed configuration to the desired location in the body by releasing the valve from the delivery catheter. The valve transitions to an expanded configuration when released from the delivery catheter. 
     Any method for delivering prosthetic heart valves described herein can include attaching a pulling/pushing wire (e.g., a rigid elongated rod, draw wire, and/or the like) to a sidewall or an anchoring element (e.g., a distal anchoring element) of the prosthetic heart valve. Such methods can include releasing the valve from the delivery catheter by one of (i) pulling the valve out of the delivery catheter using the pulling/pushing wire, wherein advancing the pulling/pushing wire away from a distal end of the delivery catheter pulls the compressed valve out of the delivery catheter, or (ii) pushing the valve out of the delivery catheter using the pulling/pushing wire, wherein advancing the pulling/pushing wire through and/or out of a distal end of the delivery catheter pushes the compressed valve out of the delivery catheter. 
     Any method for delivering prosthetic heart valves described herein can include orthogonal delivery of the prosthetic heart valve to a native annulus of a human heart that includes at least one of (i) advancing the delivery catheter to the tricuspid valve or pulmonary artery of the heart through the inferior vena cava (IVC) via the femoral vein, (ii) advancing to the tricuspid valve or pulmonary artery of the heart through the superior vena cava (SVC) via the jugular vein, or (iii) advancing to the mitral valve of the heart through a trans-atrial approach (e.g., fossa ovalis or lower), via the IVC-femoral or the SVC jugular approach; and (iv) delivering prosthetic heart valve to the native annulus by releasing the valve from the delivery catheter. 
     In some embodiments, a prosthetic heart valve has a valve frame with a distal anchoring element, a proximal anchoring element, a septal anchoring element, and a flow control component mounted within the valve frame. In some implementations, a method of deploying the prosthetic heart valve in an annulus of a native valve of a heart of a patient includes disposing in the atrium of the heart a distal end of a delivery catheter having disposed in a lumen thereof the prosthetic heart valve in a compressed configuration. The prosthetic heart valve is released from the lumen of the delivery catheter such that the prosthetic heart valve transitions from the compressed configuration to an expanded configuration. At least a portion of the prosthetic heart valve is seated in the annulus of the native valve. The septal anchoring element is placed in contact with at least one of a native septal wall or a septal leaflet area to stabilize the prosthetic heart valve in the annulus when the prosthetic heart valve is seated in the annulus. 
     Any method for delivering prosthetic heart valves described herein can include releasing the valve from a delivery catheter while increasing blood flow during deployment of the valve by partially releasing the valve from the delivery catheter to establish blood flow around the partially released valve and blood flow through the flow control component; (ii) completely releasing the valve from the delivery catheter while maintaining attachment to the valve to transition to a state with increased blood flow through the flow control component and decreased blood flow around the valve; (iii) deploying the valve into a final mounted position in a native annulus to transition to a state with complete blood flow through the flow control component and minimal or no blood flow around the valve; and (iv) disconnecting and withdrawing a positioning catheter, pulling or pushing wire or rod, and/or the delivery catheter. 
     In some embodiments, a method of delivering a prosthetic heart valve to an annulus of a native valve between an atrium and a ventricle of a heart of a patient includes disposing adjacent to the annulus of the native valve a distal end of a delivery catheter having disposed in a lumen thereof the prosthetic heart valve. The prosthetic heart valve includes a valve frame with a septal anchoring element configured to extend down the septal wall to pin the septal leaflet away from the coapting leaflets of the prosthetic heart valve, a distal anchoring element and a proximal anchoring element, and a flow control component mounted within the valve frame. The prosthetic heart valve is in a compressed configuration within the lumen of the delivery catheter. The prosthetic heart valve is released from the lumen of the delivery catheter. The prosthetic heart valve is configured to transition from the compressed configuration to an expanded configuration in response to being released. A portion of the distal anchoring element is placed on the ventricle side of the annulus of the native valve. The prosthetic heart valve is seated in the annulus when the proximal anchoring element is in a first configuration and the proximal anchoring element is transitioned from the first configuration to a second configuration after the prosthetic heart valve is seated in the annulus. 
     In some embodiments, the septal anchoring element is transitioned from a first stowed or folded position to a second expanded position. For example, the septal anchoring element can be formed from a shape-memory alloy or the like that can transition between two or more configurations. In some implementations, the transition can be actuated and/or initiated when the valve is sufficiently released from the delivery catheter. In some implementations, the transition can be actuated and/or initiated by releasing a tensile element. In some implementations, the transition can be actuated and/or initiated by a secondary catheter tool that folds the septal anchoring element down from a first stowed position and into the second expanded, subannular position. Similarly, in some embodiments, the proximal anchoring element is transitioned from a first stowed or folded position to a second expanded position. In such embodiments, the seating of the proximal anchoring element includes releasing the proximal anchoring element from a compressed pre-release configuration to an expanded post-release configuration with the proximal anchoring element extending into the proximal subannular anchoring area. 
     The terminology used herein is for the purpose of describing particular embodiments only and is not intended to limit the full scope of the claims. Unless defined otherwise, all technical and scientific terms used herein have the same meanings as commonly understood by one of ordinary skill in the art. 
     As used herein, the singular forms “a,” “an,” and “the” are intended to include the plural forms as well, unless the context clearly indicates otherwise. With respect to the use of substantially any plural and/or singular terms herein, those having skill in the art can translate from the plural to the singular and/or from the singular to the plural as is appropriate to the context and/or application. The various singular/plural permutations may be expressly set forth herein for sake of clarity. 
     In general, terms used herein, and especially in the appended claims (e.g., bodies of the appended claims) are generally intended as “open” terms (e.g., the term “including” should be interpreted as “including but not limited to,” the term “having” should be interpreted as “having at least,” etc.). Similarly, the terms “comprises” and/or “comprising,” when used in this specification, specify the presence of stated features, integers (or fractions thereof), steps, operations, elements, and/or components, but do not preclude the presence or addition of one or more other features, integers (or fractions thereof), steps, operations, elements, components, and/or groups thereof. As used in this document, the term “comprising” means “including, but not limited to.” 
     As used herein the term “and/or” includes any and all combinations of one or more of the associated listed items. It should be understood that any suitable disjunctive word and/or phrase presenting two or more alternative terms, whether in the description, claims, or drawings, contemplate the possibilities of including one of the terms, either of the terms, or both/all terms. For example, the phrase “A or B” will be understood to include the possibilities of “A” or “B” or “A and B.” 
     All ranges disclosed herein also encompass any and all possible subranges and combinations of subranges thereof unless expressly stated otherwise. Any listed range should be recognized as sufficiently describing and enabling the same range being broken down into at least equal subparts unless expressly stated otherwise. As will be understood by one skilled in the art, a range includes each individual member. 
     The term “valve prosthesis,” “prosthetic heart valve,” and/or “prosthetic valve” can refer to a combination of a frame and a leaflet or flow control structure or component, and can encompass both complete replacement of an anatomical part (e.g., a new mechanical valve replaces a native valve), as well as medical devices that take the place of and/or assist, repair, or improve existing anatomical parts (e.g., the native valve is left in place). 
     Prosthetic valves disclosed herein can include a member (e.g., a frame) that can be seated within a native valve annulus and can be used as a mounting element for a leaflet structure, a flow control component, or a flexible reciprocating sleeve or sleeve-valve. It may or may not include such a leaflet structure or flow control component, depending on the embodiment. Such members can be referred to herein as an “annular support frame,” “tubular frame,” “wire frame,” “valve frame,” “flange,” “collar,” and/or any other similar terms. 
     The term “flow control component” can refer in a non-limiting sense to a leaflet structure having 2-, 3-, 4-leaflets of flexible biocompatible material such a treated or untreated pericardium that is sewn or joined to an annular support frame, to function as a prosthetic heart valve. Such a valve can be a heart valve, such as a tricuspid, mitral, aortic, or pulmonary, that is open to blood flowing during diastole from atrium to ventricle, and that closes from systolic ventricular pressure applied to the outer surface. Repeated opening and closing in sequence can be described as “reciprocating.” The flow control component is contemplated to include a wide variety of (bio)prosthetic artificial heart valves and/or components. For example, such (bio)prosthetics can include ball valves (e.g., Starr-Edwards), bileaflet valves (St. Jude), tilting disc valves (e.g., Bjork-Shiley), stented pericardium heart-valve prosthesis&#39; (bovine, porcine, ovine) (Edwards line of bioprostheses, St. Jude prosthetic valves), as well as homograft and autograft valves. Bioprosthetic pericardial valves can include bioprosthetic aortic valves, bioprosthetic mitral valves, bioprosthetic tricuspid valves, and bioprosthetic pulmonary valves. 
     The terms “anchoring element” or “tab” or “arm” refer to structural elements extending from a portion of the valve or valve frame (e.g., extending away from a valve sidewall or body or collar) to provide an anchoring or stabilizing function to the valve. When used in conjunction with the terms distal, proximal, septal, and/or anterior, it should be understood that the anchoring or stabilizing element so described is attached to and/or integral with the valve at a distal, proximal, septal, and/or anterior location, respectively. A distal location on a valve refers to a portion of the valve furthest from the practitioner which exits the delivery catheter first, and which can be placed at or near distal subannular native tissue such as the ventricular outflow tract. A proximal location on a valve refers to a portion of the valve closest to the practitioner which exits the delivery catheter last, and which can be placed at or near proximal subannular native tissue such as tissue closest to the inferior vena cava. A septal location on a valve refers to a portion of the valve at a point between a proximal and a distal location, and which can be placed at or near septal subannular native tissue such as the septal leaflet or septal wall. An anterior location on a valve refers to a portion of the valve at a point between a proximal and a distal location, and which can be placed at or near anterior tissue opposite the septal tissue. When used in conjunction with the term “lower,” it should be understood that the anchoring or stabilizing element so described is attached to and/or integral with the valve sidewall or body at or along subannular region of the valve. Conversely, when used in conjunction with the term “upper,” it should be understood that the anchoring or stabilizing element so described is attached to and/or integral with the valve at or along a supra-annular region, collar, or atrial cuff of the valve. 
     Any of the disclosed valve embodiments may be delivered by a transcatheter approach. The term “transcatheter” is used to define the process of accessing, controlling, and/or delivering a medical device or instrument within the lumen of a catheter that is deployed into a heart chamber (or other desired location in the body), as well as an item that has been delivered or controlled by such as process. Transcatheter access is known to include cardiac access via the lumen of the femoral artery and/or vein, via the lumen of the brachial artery and/or vein, via lumen of the carotid artery, via the lumen of the jugular vein, via the intercostal (rib) and/or sub-xiphoid space, and/or the like. Moreover, transcatheter cardiac access can be via the inferior vena cava (IVC), superior vena cava (SVC), and/or via a trans-atrial (e.g., fossa ovalis or lower). Transcatheter can be synonymous with transluminal and is functionally related to the term “percutaneous” as it relates to delivery of heart valves. As used herein, the term “lumen” can refer to the inside of a cylinder or tube. 
     The mode of cardiac access can be based at least in part on a “body channel,” used to define a blood conduit or vessel within the body, and the particular application of the disclosed embodiments of prosthetic valves can determine the body channel at issue. An aortic valve replacement, for example, would be implanted in, or adjacent to, the aortic annulus. Likewise, a tricuspid or mitral valve replacement would be implanted at the tricuspid or mitral annulus, respectively. While certain features described herein may be particularly advantageous for a given implantation site, unless the combination of features is structurally impossible or excluded by claim language, any of the valve embodiments described herein could be implanted in any body channel. 
     The term “expandable” as used herein may refer to a prosthetic heart valve or a component of the prosthetic heart valve capable of expanding from a first, delivery size or configuration to a second, implantation size or configuration. An expandable structure, therefore, is not intended to refer to a structure that might undergo slight expansion, for example, from a rise in temperature or other such incidental cause, unless the context clearly indicates otherwise. Conversely, “non-expandable” should not be interpreted to mean completely rigid or a dimensionally stable, as some slight expansion of conventional “non-expandable” heart valves, for example, may be observed. 
     The prosthetic valves disclosed herein and/or components thereof are generally capable of transitioning between two or more configurations, states, shapes, and/or arrangements. For example, prosthetic valves described herein can be “compressible” and/or “expandable” between any suitable number of configurations. Various terms can be used to describe or refer to these configurations and are not intended to be limiting unless the context clearly states otherwise. For example, a prosthetic valve can be described as being placed in a “delivery configuration,” which may be any suitable configuration that allows or enables delivery of the prosthetic valve. Examples of delivery configurations can include a compressed configuration, a folded configuration, a rolled configuration, and/or similar configuration or any suitable combinations thereof. Similarly, a prosthetic valve can be described as being placed in an “expanded configuration,” which may be any suitable configuration that is not expressly intended for delivery of the prosthetic valve. Examples of expanded configuration can include a released configuration, a relaxed configuration, a deployed configuration, a non-delivery configuration, and/or similar configurations or any suitable combinations thereof. Some prosthetic valves described herein and/or components or features thereof can have a number of additional configurations that can be associated with various modes, levels, states, and/or portions of actuation, deployment, engagement, etc. Examples of such configurations can include an actuated configuration, a seated configuration, a secured configuration, an engaged configuration, and/or similar configurations or any suitable combinations thereof. While specific examples are provided above, it should be understood that they are not intended to be an exhaustive list of configurations. Other configurations may be possible. Moreover, various terms can be used to describe the same or substantially similar configurations and thus, the use of particular terms are not intended to be limiting and/or to the exclusion of other terms unless the terms and/or configurations are mutually exclusive, or the context clearly states otherwise. 
     Any of the disclosed valve embodiments may be delivered via traditional transcatheter delivery techniques or via orthogonal delivery techniques. For example, traditional delivery of prosthetic valves can be such that a central cylinder axis of the valve is substantially parallel to a length-wise axis of a delivery catheter used to deliver the valve. Typically, the valves are compressed in a radial direction relative to the central cylinder axis and advanced through the lumen of the delivery catheter. The valves are deployed from the end of the delivery catheter and expanded outwardly in a radial direction from the central cylinder axis. The delivery orientation of the valve generally means that the valve is completely released from the delivery catheter while in the atrium of the heart and reoriented relative to the annulus, which in some instances, can limit a size of the valve. 
     As used herein the terms “side-delivered,” “side-delivery,” “orthogonal delivery,” “orthogonally delivered,” and/or so forth can be used interchangeably to describe such a delivery method and/or a valve delivered using such a method. Orthogonal delivery of prosthetic valves can be such that the central cylinder axis of the valve is substantially orthogonal to the length-wise axis of the delivery catheter. With orthogonal delivery, the valves are compressed (or otherwise reduced in size) in a direction substantially parallel to the central cylinder axis and/or in a lateral direction relative to the central cylinder axis. As such, a length-wise axis (e.g., a longitudinal axis) of an orthogonally delivered valve is substantially parallel to the length-wise axis of the delivery catheter. In other words, an orthogonally delivered prosthetic valve is compressed and/or delivered at a roughly 90-degree angle compared to traditional processes of compressing and delivering transcatheter prosthetic valves. Moreover, in some instances, the orientation of orthogonally delivered valves relative to the annulus can allow a distal portion of the valve to be at least partially inserted into the annulus of the native heart valve while the proximal portion of the valve, at least in part, remains in the delivery catheter, thereby avoiding at least some of the size constraints faced with some know traditional delivery techniques. 
     Examples of prosthetic valves configured to be orthogonally delivered and processes of delivering such valves are described in detail in U.S. Patent Publication No. 2020/0188097, filed Dec. 11, 2019, entitled “Compressible Bileaflet Frame for Side Delivered Transcatheter Heart Valve” (“the &#39;097 publication”); International Patent Publication No. WO 2020/061331, filed Sep. 19, 2019, entitled “Transcatheter Deliverable Prosthetic Heart Valves and Method of Delivery” (“the &#39;331 WIPO publication”); International Patent Publication No. WO 2020/131978, filed Dec. 18, 2019, entitled “Transcatheter Deliverable Prosthetic Heart Valves and Methods of Delivery” (“the &#39;978 WIPO publication”); International Patent Publication No. WO 2020/154734, filed Jan. 27, 2020, entitled “Collapsible Inner Flow Control Component for Side-Deliverable Transcatheter Heart Valve Prosthesis” (“the &#39;734 WIPO publication”); International Patent Publication No. WO 2020/227249, filed May 4, 2020, entitled “Cinch Device and Method for Deployment of a Side-Delivered Prosthetic Heart Valve in a Native Annulus” (“the &#39;249 WIPO publication”); International Patent Publication No. WO 2021/040996, filed Aug. 6, 2020, entitled “Side-Deliverable Transcatheter Prosthetic Valves and Methods for Delivering and Anchoring the Same” (“the &#39;996 WIPO publication”); and/or International Patent Publication No. WO 2021/035032, filed Aug. 20, 2020, entitled “Delivery and Retrieval Devices and Methods for Side-Deliverable Transcatheter Prosthetic Valves” (“the &#39;032 WIPO publication”), the disclosure of each of which is incorporated herein by reference in its entirety. 
     Mathematically, the term “orthogonal” refers to an intersecting angle of 90 degrees between two lines or planes. As used herein, the term “substantially orthogonal” refers to an intersecting angle of 90 degrees plus or minus a suitable tolerance. For example, “substantially orthogonal” can refer to an intersecting angle ranging from 75 to 105 degrees. 
     The embodiments herein, and/or the various features or advantageous details thereof, are explained more fully with reference to the non-limiting embodiments that are illustrated in the accompanying drawings and detailed in the following description. Descriptions of well-known components and processing techniques are omitted so as to not unnecessarily obscure the embodiments herein. Like numbers refer to like elements throughout. 
     The examples and/or embodiments described herein are intended to facilitate an understanding of structures, functions, and/or aspects of the embodiments, ways in which the embodiments may be practiced, and/or to further enable those skilled in the art to practice the embodiments herein. Similarly, methods and/or ways of using the embodiments described herein are provided by way of example only and not limitation. Specific uses described herein are not provided to the exclusion of other uses unless the context expressly states otherwise. For example, any of the prosthetic valves described herein can be used to replace a native valve of a human heart including, for example, a mitral valve, a tricuspid valve, an aortic valve, and/or a pulmonary valve. While some prosthetic valves are described herein in the context of replacing a native mitral valve or a native tricuspid valve, it should be understood that such a prosthetic valve can be used to replace any native valve unless expressly stated otherwise or unless one skilled in the art would clearly recognize that one or more components and/or features would otherwise make the prosthetic valve incompatible for such use. Accordingly, specific examples, embodiments, methods, and/or uses described herein should not be construed as limiting the scope of the inventions or inventive concepts herein. Rather, examples and embodiments are provided so that this disclosure will be thorough and complete, and will fully convey the scope of the inventive concepts to those skilled in the art. 
       FIGS.  1 - 5    are various schematic illustrations of a side-deliverable transcatheter prosthetic heart valve  100  (also referred to herein as “prosthetic valve” or simply “valve”) according to an embodiment. The prosthetic valve  100  is configured to be deployed in a desired location within a body (e.g., of a human patient) and to permit blood flow in a first direction through a flow control component from an inflow end of the prosthetic valve  100  to an outflow end of the prosthetic valve  100  and to block blood flow in a second direction, opposite the first direction. For example, the prosthetic valve  100  can be configured to be deployed within the annulus of a native tricuspid valve or native mitral valve of a human heart to supplement and/or replace the functioning of the native valve. 
     The prosthetic valve  100  is compressible and expandable between an expanded configuration ( FIGS.  1 ,  3 , and  5   ) for implanting at a desired location in a body (e.g., a human heart) and a compressed or delivery configuration ( FIGS.  2  and  4   ) for introduction into the body using a delivery catheter. For example, the prosthetic valve  100  can be compressible and expandable in at least one direction relative to a long-axis  102  of the valve  100  (also referred to herein as “horizontal axis,” “longitudinal axis,” or “lengthwise axis”). In some embodiments, the prosthetic valve  100  can be compressible and expandable in at least two directions relative to the long-axis  102  of the valve  100 . 
     In some embodiments, the valve  100  (and/or at least a portion thereof) may be heat-shaped and/or otherwise formed into any desired shape such as, for example, a roughly tubular shape, a roughly hourglass shape, and/or the like. In some embodiments, the valve  100  can include an upper atrial cuff or flange for atrial sealing, a lower ventricle cuff or flange for ventricular sealing, and a transannular section or region (e.g., a body section, a tubular section, a cylindrical section, etc.) disposed therebetween. The transannular region can have an hourglass cross-section for about 60-80% of the circumference to conform to the native annulus along the posterior and anterior annular segments while remaining substantially vertically flat along 20-40% of the annular circumference to conform to the septal annular segment. While the valve  100  is shown in  FIGS.  1 - 5    as having a given shape, it should be understood that the size and/or shape of the valve  100  (and/or at least a portion thereof) can be based on a size and/or shape of the anatomical structures of the native tissue. 
     For example, the valve  100  can be centric (e.g., radially symmetrical relative to a central y-axis  104 ) or eccentric (e.g., radially asymmetrical relative to the central y-axis axis  104 ). In some eccentric embodiments, the valve  100 , or an outer frame thereof, may have a complex shape determined by the anatomical structures where the valve  100  is being mounted. For example, in some instances, the valve  100  may be deployed in an annulus of a native tricuspid valve having a circumference in the shape of a rounded ellipse with a substantially vertical septal wall, which is known to enlarge in disease states along an anterior-posterior line. In some instances, the valve  100  may be deployed in an annulus of a native mitral valve (e.g., near the anterior leaflet) having a circumference in the shape of a rounded ellipse with a substantially vertical septal wall, which is known to enlarge in disease states. As such, the valve  100  can have a complex shape that determined, at least in part, by the native annulus and/or a disease state of the native valve. By way of example, the valve  100  or the outer frame thereof may have a D-shape (viewed from the top) so the flat portion can be matched to the anatomy in which the valve  100  will be deployed (e.g., a substantially vertical septal wall). In some embodiments, the valve  100  or the outer frame thereof can have a circumference in the shape of a rounded ellipse, such as a hyperbolic paraboloid, to account for the positions of native septal, anterior, and/or posterior leaflets, and/or the native septal wall; to avoid native electrical bundles such as the atrioventricular (A-V) node and/or A-V node-related structures like the Triangle of Koch, AV bundle, etc.; to avoid interference with coronary blood flow such as the coronary sinus; to accommodate variances in the septal wall that is known to be substantially vertical but that enlarges along the Anterior-Posterior axis toward the free wall in disease states. 
     As shown, the valve  100  generally includes an annular support frame  110  and a flow control component  150  mounted within the annular support frame  110 . In addition, the valve  100  and/or at least the annular support frame  110  of the valve  100  can include, couple to, and/or otherwise engage a delivery system  180 . In some implementations, the valve  100  and/or aspects or portions thereof can be similar to and/or substantially the same as the valves (and/or the corresponding aspects or portions thereof) described in detail in the &#39;097 publication, the &#39;331 WIPO publication, the &#39;978 WIPO publication, the &#39;734 WIPO publication, the &#39;249 WIPO publication, the &#39;996 WIPO publication, and/or the &#39;032 WIPO publication incorporated by reference hereinabove. Accordingly, certain aspects, portions, and/or details of the valve  100  may not be described in further detail herein. 
     The annular support frame  110  (also referred to herein as “tubular frame,” “valve frame,” “wire frame,” “outer frame,” or “frame”) can have a supra-annular region  120 , a subannular region  130 , and a transannular region  112 , disposed and/or coupled therebetween. In some embodiments, the frame  110  can be monolithically and/or unitarily constructed. In some embodiments, one or more of the supra-annular region  120 , the subannular region  130 , and/or the transannular region  112  can be separate, independent, and/or modular components that are coupled to collectively form the frame  110 . For example, in some embodiments, the supra-annular region  120  can be, for example, an atrial collar or cuff coupled to a top, upper, and/or supra-annular edge of the transannular region  112  and the subannular region  130  can be a bottom, lower, and/or subannular portion or section of the transannular region  112  of the fame  110 . 
     In some implementations, a modular and/or at least partially modular configuration can allow the frame  110  to be adapted to a given size and/or shape of the anatomical structures where the valve  100  is being mounted. For example, one or more of the supra-annular region(s)  120 , the subannular region  130 , and/or the transannular region  112  can be designed and/or adapted so that that the support frame  110  has any desirable height, outer diameter, and/or inner diameter such as any of those described above. Moreover, such a modular configuration can allow the frame  110  to bend, flex, compress, fold, roll, and/or otherwise reconfigure without plastic or permanent deformation thereof. For example, the frame  110  is compressible to a compressed or delivery configuration for delivery and when released it is configured to return to its original shape (uncompressed, expanded, or released configuration) substantially without plastic or permanent deformation. 
     The support frame  110  and/or the supra-annular region  120 , subannular region  130 , and/or transannular region  112  can be formed from or of any suitable material. In some embodiments, the frame  110  and/or one or more portions or regions thereof can be formed from or of a shape-memory or superelastic metal, metal alloy, plastic, and/or the like. For example, the frame  110  (e.g., one or more of the supra-annular region  120 , the subannular region  130 , and the transannular region  112 ) can be formed from or of Nitinol or the like. In some embodiments, the frame  110  (and/or any of the regions thereof) can be laser cut from a Nitinol sheet or tube. In other embodiments, the frame  110  (and/or any of the regions thereof) can be formed of or from a Nitinol wire that is bent, kink, formed, and/or manipulated into a desired shape. In still other embodiments, the frame  110  (and/or any of the regions thereof) can be formed of or from a desired material using any suitable additive or subtractive manufacturing process such as those described above. Moreover, the frame  110  and/or one or more of the supra-annular region  120 , the subannular region  130 , and the transannular region  112  can be formed of or from a metal or other structural frame material, which in turn, is covered by a biocompatible material such as, for example, pericardium tissue (e.g., DuraGuard®, Peri-Guard®, Vascu-Guard®, etc.), polymers (e.g., polyester, Dacron®, etc.), and/or the like, as described above. 
     The supra-annular region  120  of the frame  110  can be and/or can form, for example, a cuff or collar that can be attached or coupled to an upper edge or upper portion of the transannular region  112 . When the valve  100  is deployed within a human heart, the supra-annular region  120  can be an atrial collar that is shaped to conform to the native deployment location. In a tricuspid and/or mitral valve replacement, for example, the supra-annular region  120  (e.g., atrial collar) can have various portions configured to conform to the native valve and/or a portion of the atrial floor surrounding the tricuspid and/or mitral valve, respectively. In some implementations, the supra-annular region  120  can be deployed on the atrial floor to direct blood from the atrium into the flow control component  150  of the valve  100  and to seal against blood leakage (perivalvular leakage) around the frame  110 . 
     In some embodiments, the supra-annular region  120  can be a wire frame that is laser cut out of any suitable material. In some embodiments, the supra-annular region  120  can be formed from a tube or sheet of a shape-memory or superelastic material such as, for example, Nitinol and, for example, heat-set into a desired shape and/or configuration. In some embodiments, forming the supra-annular region  120  in such a manner can allow the supra-annular region  120  to bend, flex, fold, compress, and/or otherwise reconfigure substantially without plastically deforming and/or without fatigue that may result in failure or breaking of one or more portions thereof. Moreover, the wire frame of the supra-annular region  120  can be covered by any suitable biocompatible material such as any of those described above. 
     The supra-annular region  120  includes a distal portion and a proximal portion. In some embodiments, the distal portion can be and/or can include a distal supra-annular anchoring element and/or the like that can engage supra-annular native tissue on a distal side of the annulus as the prosthetic valve  100  is seated into the annulus. In some embodiments, the proximal portion can be and/or can include a proximal supra-annular anchoring element and/or the like that can engage supra-annular native tissue on a proximal side of the annulus as the prosthetic valve  100  is seated in the annulus. In some embodiments, the distal portion and/or the distal supra-annular anchoring element can be sized and/or shaped to correspond to a size and/or shape of the distal portion of the atrial floor of the heart in which the prosthetic valve  100  is disposed. Similarly, the proximal portion and/or the proximal supra-annular anchoring element can be sized and/or shaped to correspond to a size and/or shape of a proximal portion of the atrial floor of the heart. 
     Although not shown in  FIGS.  1 - 5   , the supra-annular region  120  can be shaped and/or formed to include any number of features configured to engage native tissue and/or one or more other portions of the valve  100 , the delivery system  180 , and/or the like. For example, in some embodiments, the supra-annular region  120  can include and/or can form an outer portion and an inner portion that is suspended from and/or coupled to the outer portion. In some implementations, the outer portion can be sized and/or shaped to engage native tissue, the inner portion can provide structure for mounting the flow control component  150  to the support frame  110 , and one or more coverings, spacers, struts, splines, and/or structures can be disposed therebetween. In some implementations, a portion of the supra-annular region  120  can be at least temporarily coupled to and/or can at least temporarily receive a portion of the delivery system  180 , at least a portion of an actuator, at least a portion of a guidewire, and/or the like. 
     The transannular region  112  of the support frame  110  is coupled to the supra-annular region  120  and extends from the supra-annular region  120  and at least partially through the annulus of the native valve when the prosthetic valve  100  is seated therein. In some embodiments, the transannular region  112  can be coupled to the supra-annular region  120  such that a desired amount of movement and/or flex is allowed therebetween (e.g., welded, bonded, sewn, bound, and/or the like). For example, in some implementations, the transannular region  112  and/or portions thereof can be sewn to the supra-annular region  120  (and/or portions thereof). 
     The transannular region  112  can be shaped and/or formed into a ring, a cylindrical tube, a conical tube, D-shaped tube, and/or any other suitable annular shape. In some embodiments, the transannular region  112  may have a side profile of a flat-cone shape, an inverted flat-cone shape (narrower at top, wider at bottom), a concave cylinder (walls bent in), a convex cylinder (walls bulging out), an angular hourglass, a curved, graduated hourglass, a ring or cylinder having a flared top, flared bottom, or both. Moreover, the transannular region  112  can form and/or define an aperture or central channel  114  that extends along the central axis  104  (e.g., the y-axis). The central channel  114  (e.g., a central axial lumen or channel) can be sized and configured to receive the flow control component  150  across at least a portion of a diameter of the central channel  114 . In some embodiments, the transannular region  112  can have a shape and/or size that is at least partially based on a size, shape, and/or configuration of the supra-annular region  120  (and/or subannular region  130 ) and/or the native annulus in which it is configured to be deployed. For example, the transannular region  112  can have an outer circumference surface for engaging native annular tissue that may be tensioned against an inner aspect of the native annulus to provide structural patency to a weakened native annular ring. 
     In some embodiments, the transannular region  112  can be a wire frame that is laser cut out of any suitable material. For example, the transannular region  112  can be formed from a tube or sheet of a shape-memory or superelastic material such as, for example, Nitinol and, for example, heat-set into a desired shape and/or configuration. Although not shown in  FIGS.  1 - 5   , in some embodiments, the transannular region  112  can include and/or can be formed with two laser cut halves that can be formed into a desired shape and/or configuration and coupled together to form the transannular region  112 . The transannular region  112  can be formed to include a set of compressible wire cells having an orientation and/or cell geometry substantially orthogonal to the central axis  104  ( FIG.  1   ) to minimize wire cell strain when the transannular region  112  is in a vertical compressed configuration, a rolled and compressed configuration, or a folded and compressed configuration. In some embodiments, forming the transannular region  112  in such a manner can allow the transannular region  112  to bend, flex, fold, deform, and/or otherwise reconfigure (substantially without plastic deformation and/or undue fatigue) in response to lateral folding along or in a direction of a lateral axis  106  ( FIG.  3   ) and/or vertical compression along or in a direction of the central axis  104  ( FIG.  4   ), as described in further detail herein. 
     As described above with reference to the supra-annular region  120 , the wire frame of the transannular region  112  can be covered by any suitable biocompatible material such as any of those described above. In some implementations, the wire frame of at least the supra-annular region  120  and transannular region  112  can be flexibly coupled (e.g., sewn) to form a wire frame portion of the support frame  110 , which in turn, is covered in the biocompatible material. Said another way, at least the supra-annular region  120  and the transannular region  112  can be covered with the biocompatible material prior to being coupled or after being coupled. In embodiments in which the wire frames are covered after being coupled, the biocompatible material can facilitate and/or support the coupling therebetween. 
     The subannular region  130  of the frame  110  can be and/or can form, for example, a cuff or collar along an end of the transannular region  112  opposite the supra-annular region  120 . In some embodiments, the subannular region  130  is a lower or subannular portion of the transannular region  112  (e.g., the transannular region  112  and the subannular region  130  are monolithically and/or unitarily formed). Said another way, a lower or subannular portion of the transannular region  112  can form and/or include the subannular annular region  130 . In other embodiments, the subannular region  130  is a separate and/or independent component that can be attached or coupled to a lower edge or portion of the transannular region  112 , as described above with reference to the supra-annular region  120 . In such embodiments, for example, the subannular region  130  can be a wire frame that is laser cut out of any suitable material such as a shape-memory or superelastic material like Nitinol, heat-set into a desired shape and/or configuration, covered by any suitable biocompatible material, and attached to a lower edge of the transannular region  112 , as described above with reference to the supra-annular region. In some implementations, forming the subannular region  130  in such a manner can allow the subannular region  130  to bend, flex, fold, compress, and/or otherwise reconfigure substantially without plastically deforming and/or without fatigue that may result in failure or breaking of one or more portions thereof. 
     When the valve  100  is deployed within a human heart, the subannular region  130  can be and/or can form a ventricular collar that is shaped to conform to the native deployment location. In a tricuspid and/or mitral valve replacement, for example, the subannular region  130  or collar can have various portions configured to conform to the native valve and/or a portion of the ventricular ceiling surrounding the tricuspid and/or mitral valve, respectively. In some implementations, the subannular region  130  or at least a portion thereof can engage the ventricular ceiling surrounding the native annulus to secure the valve  100  in the native annulus, to stabilize the valve  100  in the annulus, to prevent dislodging of the valve  100 , to sandwich or compress the native annulus or adjacent tissue between the supra-annular region  120  and the subannular region  130  (or lower portion of the transannular region  112 ), and/or to seal against blood leakage (perivalvular leakage and/or regurgitation during systole) around the frame  110 . 
     The subannular region  130  of the frame  110  can be shaped and/or formed to include any number of features configured to engage native tissue, one or more other portions of the valve  100 , one or more portions of the delivery system  180 , one or more actuators (not shown), and/or the like. For example, as shown in  FIG.  1   , the subannular region  130  can include and/or can form a distal portion having a distal anchoring element  132 , a proximal portion having a proximal anchoring element  134 , and a septal portion having a septal stability and/or anchoring element. In some embodiments, the subannular region  130  can include and/or can form any number of additional anchoring elements (not shown in  FIGS.  1 - 5   ). In some embodiments, the anchoring elements  132 ,  134 , and/or  136  are integrally and/or monolithically formed with the subannular region  130  and/or the lower or subannular portion of the transannular region  112 . The distal anchoring element  132  and the proximal anchoring element  134  can be any suitable shape, size, and/or configuration such as any of those described in detail in the &#39;097 publication, the &#39;331 WIPO publication, the &#39;978 WIPO publication, the &#39;734 WIPO publication, the &#39;249 WIPO publication, the &#39;996 WIPO publication, and/or the &#39;032 WIPO publication incorporated by reference hereinabove, and/or any of those described herein with respect to specific embodiments. Accordingly, portions, aspects, and/or features of the distal anchoring element  132  and/or the proximal anchoring element  134  may not be described in further detail herein. 
     In some embodiments, the distal anchoring element  132  can optionally include a guidewire coupler  133  configured to selectively engage and/or receive a portion of a guidewire or a portion of a guidewire assembly (not shown). The guidewire coupler  133  is configured to allow a portion of the guidewire to extend through an aperture of the guidewire coupler  133 , thereby allowing the valve  100  to be advanced over or along the guidewire during delivery and deployment. In some embodiments, the guidewire coupler  133  can selectively allow the guidewire to be advanced therethrough while blocking or preventing other elements and/or components such as a pusher or the like. 
     The distal anchoring element  132  is configured to engage a desired portion of the native tissue on a distal side of the native annulus to facilitate the seating, mounting, and/or deploying of the valve  100  in the annulus of the native valve. For example, in some implementations, the distal anchoring element  132  can be a projection or protrusion extending from the frame  110  (e.g., the subannular region  130  and/or the lower portion of the transannular region  112 ) and into a distal subannular position relative to the annulus (e.g., the RVOT for tricuspid valve replacement, and/or the like). In such implementations, the distal anchoring element  132  can be shaped and/or biased such that the distal anchoring element  132  exerts a force on the subannular tissue operable to at least partially secure, stabilize, and/or anchor the distal end portion of the valve  100  in the native annulus. In some embodiments, the distal anchoring element  132  can extend from the distal portion of the subannular region  130  (or lower portion of the transannular region  112 ) by about 10-40 mm. 
     The proximal anchoring element  134  is configured to engage subannular tissue on a proximal side of the native annulus to facilitate the seating, mounting, and/or deploying of the valve  100  in the annulus. In some embodiments, the proximal anchoring element  134  can be an anchoring element having a substantially fixed configuration. In such embodiments, the proximal anchoring element  134  can be flexible and/or movable through a relatively limited range of motion but otherwise has a single configuration. In some such embodiments, the proximal anchoring element  134  can extend from the proximal portion of the subannular region  130  (or lower portion of the transannular region  112 ) by about 10-40 mm. 
     In other embodiments, the proximal anchoring element  134  can be configured to transition, move, and/or otherwise reconfigure between two or more configurations. For example, the proximal anchoring element  134  can be transitioned between a first configuration in which the proximal anchoring element  134  extends from the subannular region  130  a first amount or distance and a second configuration in which the proximal anchoring element  134  extends from the subannular region  130  a second amount or distance, different from the first amount or distance. For example, in some embodiments, the proximal anchoring element  134  can have a first configuration in which the proximal anchoring element  134  is in a compressed, contracted, retracted, undeployed, folded, and/or restrained state (e.g., in a position that is near, adjacent to, and/or in contact with the transannular region  112  and/or the supra-annular region  120  of the frame  110 ), and a second configuration in which the proximal anchoring element  134  is in an expanded, extended, deployed, unfolded, and/or unrestrained state (e.g., extending away from the transannular region  112 ). In some implementations, the proximal anchoring element  134  in the expanded or deployed configuration (e.g., the second configuration) can extend from the transannular region  112  by about 10-40 mm and in the compressed or undeployed configuration (e.g., the first configuration) can be in contact with the transannular region  112  or can extend from the transannular region  112  by less than about 10 mm. Moreover, in some implementations, the proximal anchoring element  134  can be transitioned from the first configuration to the second configuration in response to actuation of an actuator, tensile member, portion of the delivery system  180 , and/or the like, as described in further detail herein. 
     The frame  110  also includes the septal stability and/or anchoring element  136  (also referred to herein as “septal anchoring element”). The septal anchoring element  136  can be any suitable shape, size, and/or configuration such as any of those described herein with respect to specific embodiments. In some embodiments, for example, the septal anchoring element  136  can be, for example, integrally formed with the lower sidewall portion  130  of the frame  110  (e.g., can be a portion of the wireframe or laser-cut frame portion). In some embodiments, the septal anchoring element  136  can be formed at least in part by a wire-braid frame, a wire loop, an integrated frame section, a stent, and/or the like and can extend away from the transannular region  112  and/or the supra-annular region  120  (e.g., downward and outward). 
     The septal anchoring element  136  can be positioned along the septal side of the subannular region  130  (or lower portion of the transannular region  112 ) at any suitable position. For example, in some embodiments, the septal anchoring element  136  can be a wire frame or the like have a U-shape, an inverted parabolic shape, and/or the like such that a local minima of the septal anchoring element  136  is substantially centered along the septal side of the subannular region  130 . In other embodiments, the septal anchoring element  136  can have the U-shape, the inverted parabolic shape, and/or the like but can be shifted in a proximal direction or in a distal direction (e.g., closer to the proximal anchoring element  132  and further from the distal anchoring element  134 , or vice versa). In some embodiments, the septal anchoring element  136  can be substantially symmetric relative to an anteroposterior (AP) plane. In other embodiments, the septal anchoring element  136  can be asymmetric relative to the AP plane. In some embodiments, the septal anchoring element  136  can have an irregular or an at least semi-irregular shape that can be based, for example, on the anatomy of the heart in which the valve  100  is disposed. In some embodiments, the septal anchoring element  136  can extend from the septal portion of the subannular region  130  (or lower portion of the transannular region  112 ) by about 10-40 mm. 
     In some implementations, the septal anchoring element  136  is a lower anchoring element configured to engage subannular tissue of the ventricle to aid in the stability, anchoring, and/or securement of the valve  100  in the annulus. More specifically, the septal anchoring element  136  can be configured to engage subannular septal tissue, septal leaflet tissue, and/or any other suitable tissue at, near, and/or along the septum of the heart. In some implementations, when the valve  100  is at least partially inserted into the annulus, the septal anchoring element  136  can extend down the septal wall to pin the native septal leaflet away from, for example, the coapting leaflets of the prosthetic valve  100 . In some implementations, the septal anchoring element can stabilize the valve against any intra-annular rolling forces and/or any intra-annular twisting forces that might affect a desired location or positioning of the prosthetic valve within the annulus, (e.g., tilted, angled, twisted, rolled, etc.). In some embodiments, the septal anchoring element  136  can be size, shaped, and/or configured for treating specific anatomical structures, avoiding interference with native electrical tissue or with the coronary sinus return, avoiding excessive cutting effect on the ventricular tissue, blocking native tissue from interfering with the functioning of the prosthetic valve  100  (e.g., leaflets of the flow control component  150 ), providing additional ventricular stability to prevent unwanted movement of the prosthetic valve  100  prior to in-growth, such as rolling, tilting, twisting or other unwanted migration of the implant, and/or the like. 
     As described above with reference to the proximal anchoring element  134 , the septal anchoring element  136  can be an anchoring element that has a substantially fixed configuration or can be an anchoring element that can be reconfigurable between any number of configurations. For example, in some embodiments, the septal anchoring element  136  can be configured to transition, move, and/or otherwise reconfigure between a first configuration in which the septal anchoring element  136  extends from the subannular region  130  a first amount or distance and a second configuration in which the septal anchoring element  136  extends from the subannular region  130  a second amount or distance, different from the first amount or distance. In some implementations, the septal anchoring element  136  can be compressed, contracted, retracted, undeployed, folded, and/or restrained when in the first configuration (e.g., in a position that is near, adjacent to, and/or in contact with the transannular region  112  and/or the supra-annular region  120  of the frame  110 ), and can be expanded, extended, deployed, unfolded, actuated, and/or unrestrained when in the second configuration (e.g., extending away from the transannular region  112 ). Moreover, in some implementations, the septal anchoring element  136  can be transitioned from the first configuration to the second configuration in response to actuation of an actuator, tensile member, portion of the delivery system  180 , and/or the like, as described in further detail herein. 
     Although not shown in  FIGS.  1 - 5   , the frame  110  may also have and/or form additional functional elements (e.g., loops, anchors, etc.) for attaching accessory components such as biocompatible covers, tissue anchors, releasable deployment and retrieval controls (e.g., an actuator, a tensile member, a portion of the delivery system  180 , and/or other suitable guides, knobs, attachments, rigging, etc.) and so forth. In some implementations, the frame  110  (or aspects and/or portions thereof) can be structurally and/or functionally similar to the frames (or corresponding aspects and/or portions thereof) described in detail in the &#39;097 publication, the &#39;331 WIPO publication, the &#39;978 WIPO publication, the &#39;734 WIPO publication, the &#39;249 WIPO publication, the &#39;996 WIPO publication, and/or the &#39;032 WIPO publication incorporated by reference hereinabove. 
     The flow control component  150  can refer in a non-limiting sense to a device for controlling fluid flow therethrough. In some embodiments, the flow control component  150  can be a leaflet structure having two, three, four, or more leaflets, made of flexible biocompatible material such a treated or untreated pericardium. The leaflets can be sewn or joined to a support structure such as an inner frame, which in turn, can be sewn or joined to the outer frame  110 . The leaflets can be configured to move between an open and a closed or substantially sealed state to allow blood to flow through the flow control component  150  in a first direction through an inflow end of the valve  100  and block blood flow in a second direction, opposite to the first direction, through an outflow end of the valve  100 . For example, the flow control component  150  can be configured such that the valve  100  functions, for example, as a heart valve, such as a tricuspid valve, mitral valve, aortic valve, or pulmonary valve, that can open to blood flowing during diastole from atrium to ventricle, and that can close from systolic ventricular pressure applied to the outer surface. Repeated opening and closing in sequence can be described as “reciprocating.” 
     The inner frame and/or portions or aspects thereof can be similar in at least form and/or function to the outer frame  110  and/or portions or aspects thereof. For example, the inner frame can be a laser cut frame formed from or of a shape-memory material such as Nitinol. Moreover, the inner frame can be compressible for delivery and configured to return to its original (uncompressed) shape when released (e.g., after delivery). In some embodiments, the inner frame can include and/or can form any suitable number of compressible, elastically deformable diamond-shaped or eye-shaped wire cells, and/or the like. The wire cells can have an orientation and cell geometry substantially orthogonal to an axis of the flow control component  150  to minimize wire cell strain when the inner frame is in a compressed configuration. 
     In some embodiments, the flow control component  150  and/or the inner frame thereof can have a substantially cylindrical or tubular shape when the valve  100  is in the expanded configuration (see e.g.,  FIG.  3   ) and can be configured to elastically deform when the valve  100  is placed in the compressed configuration (see e.g.,  FIGS.  2  and  4   ). Although not shown in  FIGS.  1 - 5   , in some embodiments, the inner frame of the flow control component  150  can include and/or can be formed with two halves that can be coupled together to allow the inner frame to elastically deform in response to lateral compression or folding along or in a direction of the lateral axis  106  ( FIG.  3   ), as described in further detail herein. 
     As shown in  FIGS.  1 - 4   , the flow control component  150  is mounted within the central channel  114  of the frame  110 . More specifically, the flow control component  150  is mounted and/or coupled to the supra-annular region  120  (e.g., an inner portion thereof) and is configured to extend into and/or through the central channel  114  formed and/or defined by the transannular region  112 . In some embodiments, the flow control component  150  can be coupled to the supra-annular region  120  via tissue, a biocompatible mesh, one or more woven or knitted fabrics, one or more superelastic or shape-memory alloy structures, which is sewn, sutured, and/or otherwise secured to a portion supra-annular region  120 . In some embodiments, the flow control component  150  can be coupled to the supra-annular region  120  such that a portion of the flow control component  150  is disposed above and/or otherwise extends beyond the supra-annular region  120  (e.g., extends away from the annulus in the direction of the atrium). In some embodiments, the portion of the flow control component  150  extending above and/or beyond the supra-annular region  120  can form a ridge, ledge, wall, step-up, and/or the like. In some implementations, such an arrangement can facilitate ingrowth of native tissue over the supra-annular region  120  without occluding the flow control component  150 . 
     The flow control component  150  can be at least partially disposed in the central channel  114  such that the axis of the flow control component  150  that extends in the direction of blood flow through the flow control component  150  is substantially parallel to the central axis  104  of the frame  110 . In some embodiments, the arrangement of the support frame  110  can be such that the flow control component  150  is centered within the central channel  114 . In other embodiments, the arrangement of the support frame  110  can be such that the flow control component  150  is off-centered within the central channel  114 . In some embodiments, the central channel  114  can have a diameter and/or perimeter that is larger than a diameter and/or perimeter of the flow control component  150 . Although not shown in  FIGS.  1 - 5   , in some embodiments, the valve  100  can include a spacer or the like that can be disposed within the central channel  114  adjacent to the flow control component  150 . In other embodiments, a spacer can be a cover, or the like coupled to a portion of the frame  110  and configured to cover a portion of the central channel  114 . In some instances, the spacer can be used to facilitate the coupling of the flow control component  150  to the frame  110 . 
     In some embodiments, the flow control component  150  (or portions and/or aspects thereof) can be similar to, for example, any of the flow control components described in the &#39;734 WIPO publication. Thus, the flow control component  150  and/or aspects or portions thereof are not described in further detail herein. 
     Referring back to  FIG.  1   , the valve  100  includes and/or is coupled to the delivery interface  180 . In some embodiments, the valve  100  can also include an actuator and/or other suitable member, mechanism, and/or device configured to actuate at least a portion of the valve  100 . For example, in some embodiments, the actuator can be configured to at least temporarily couple to the supra-annular region  120  of the support frame  110  and can be configured to actuate one or more portions of the valve  100  such as, for example, the proximal anchoring element  134  or the septal anchoring element  136 . In some implementations, the actuator can include one or more cables, tethers, linkages, joints, connections, tensile members, etc., that can exert a force (or can remove an exerted force) on a portion of the proximal or septal anchoring elements  134  and/or  136  operable to transition the anchoring elements  134  and/or  136  between the first and second configuration. 
     The delivery system  180 , shown in  FIG.  1   , can include any number of components having any suitable shape, size, and/or configuration. In some implementations, the delivery system  180  can be and/or can include, for example, at least a delivery catheter such as, for example, a 12-34 Fr delivery catheter with any suitable corresponding internal lumen diameter(s) sufficient to receive the prosthetic valve  100  in the compressed configuration, as described, for example, in any of the &#39;097 publication, the &#39;331 WIPO publication, the &#39;978 WIPO publication, the &#39;734 WIPO publication, the &#39;249 WIPO publication, the &#39;996 WIPO publication, and/or the &#39;032 WIPO publication incorporated by reference hereinabove. In some embodiments, at least portion of the actuator or the like can extend through one or more lumens of the delivery catheter, thereby allowing a user (e.g., a doctor, surgeon, technician, etc.) to manipulate a distal end of the actuator and thus one or more portions of the valve  100 . In some embodiments, a guidewire and/or guidewire assembly can similarly extend through one or more lumens of the delivery catheter. As described above, the distal anchoring element  132  can include a guidewire coupler  133  that can be coupled to and/or receive at least a portion of the guidewire and/or guidewire assembly and thus, the valve  100  can be advanced along the guidewire and/or guidewire assembly through the delivery system and into a desired position within the heart (e.g., the annulus of a native heart valve). 
     As described above, the valve  100  is compressible and expandable between the expanded configuration ( FIGS.  1  and  2   ) and the compressed configuration ( FIGS.  3  and  4   ). The valve  100  can have a first height or size along the central axis  104  when in the expanded configuration and can have a second height or size, less than the first height or size, along the central axis  104  when in the compressed configuration. The valve  100  can also be compressed in additional directions. For example, the valve  100  can be compressed along the lateral axis  106  that is perpendicular to both the longitudinal axis  102  and the central axis  104  (see e.g.,  FIGS.  2  and  3   ). 
     The valve  100  is compressed during delivery of the valve  100  and is configured to expand once released from the delivery catheter. More specifically, the valve  100  is configured for transcatheter orthogonal delivery to the desired location in the body (e.g., the annulus of a native valve), in which the valve  100  is compressed in an orthogonal or lateral direction relative to the dimensions of the valve  100  in the expanded configuration (e.g., along the central axis  104  and/or the lateral axis  106 ). During delivery, the longitudinal axis  102  of the valve  100  is substantially parallel to a longitudinal axis of the delivery catheter, as described in the &#39;331 WIPO publication. 
     The valve  100  is in the expanded configuration prior to being loaded into the delivery system  180  and after being released from the delivery catheter and deployed or implanted (or ready to be deployed or implanted) at the desired location in the body. When in the expanded configuration shown in  FIGS.  1 ,  2 , and  5   , the valve  100  has an extent in any direction orthogonal or lateral to the longitudinal axis  102  (e.g., along the central axis  104  and/or the lateral axis  106 ) that is larger than a diameter of the lumen of the delivery catheter used to deliver the valve  100 . For example, in some embodiments, the valve  100  can have an expanded height (e.g., along the central axis  104 ) of 5-60 mm. In some embodiments, the valve  100  can have an expanded diameter length (e.g., along the longitudinal axis  102 ) and width (e.g., along the lateral axis  106 ) of about 20-80 mm, or about 40-80 mm. 
     When in the compressed configuration shown in  FIGS.  3  and  4   , the valve  100  has an extent in any direction orthogonal or lateral to the longitudinal axis  102  (e.g., along the central axis  104  and/or the lateral axis  106 ) that is smaller than the diameter of the lumen of the delivery catheter, allowing the valve  100  to be delivered therethrough. For example, in some embodiments, the valve  100  can have a compressed height (e.g., along the central axis  104 ) and a compressed width (e.g., along the lateral axis  106 ) of about 6-15 mm, about 8-12 mm, or about 9-10 mm. The valve  100  can be compressed by compressing, rolling, folding, and/or any other suitable manner, or combinations thereof, as described in detail in the &#39;097 publication, the &#39;331 WIPO publication, the &#39;978 WIPO publication, the &#39;734 WIPO publication, the &#39;249 WIPO publication, the &#39;996 WIPO publication, and/or the &#39;032 WIPO publication incorporated by reference hereinabove. It is contemplated in some embodiments that the length of the valve  100  (e.g., along the longitudinal axis  102 ) is not compressed for delivery. Rather, in some embodiments, the length of the valve  100  can be increased in response to compression of the valve  100  along the central axis  104  and/or the lateral axis  106 . 
     As shown in  FIG.  5   , the valve  100  can be delivered, for example, to an atrium of the human heart (or any other space or chamber of the human heart) and disposed within an annulus of a native valve such as, for example, the pulmonary valve (PV), the mitral valve (MV), the aortic valve (AV), and/or the tricuspid valve (TV). As described above, the valve  100  can be in the compressed configuration and delivered to the annulus via the delivery system  180  and can be released from the delivery system  180  and allowed to expand to the expanded configuration. For example, the valve  100  can be delivered to the atrium of the human heart and released from the delivery catheter (not shown) via any of the delivery systems, devices, and/or methods described in detail in the &#39;097 publication, the &#39;331 WIPO publication, the &#39;978 WIPO publication, the &#39;734 WIPO publication, the &#39;249 WIPO publication, the &#39;996 WIPO publication, and/or the &#39;032 WIPO publication incorporated by reference hereinabove. 
     In some implementations, the delivery of the valve  100  can include advancing a guidewire into the atrium of the human heart, through the native valve, and to a desired position within the ventricle (e.g., the RVOT). After positioning the guidewire, the delivery catheter can be advanced along and/or over the guidewire and into the atrium (e.g., via the IVC, the SVC, and/or a trans-septal access). In some embodiments, a guidewire coupler  133  of the valve  100  (e.g., included in or on the distal anchoring element  132 ) can be coupled to a proximal end portion of the guidewire and the valve  100  can be placed in the compressed configuration, allowing the valve  100  to be advanced along the guidewire and through a lumen of the delivery catheter, and into the atrium. 
     The deployment of the valve  100  can include placing the distal anchoring element  132  of the subannular region  130  in the ventricle (RV, LV) below the annulus while the remaining portions of the valve  100  are in the atrium (RA, LA). In some instances, the distal anchoring element  132  can be advanced over and/or along the guidewire to a desired position within the ventricle such as, for example, an outflow tract of the ventricle. For example, in some implementations, the valve  100  can be delivered to the annulus of the native tricuspid valve (TV) and at least a portion of the distal anchoring element  132  can be positioned in the RVOT. In other implementations, the valve  100  can be delivered to the annulus of the native mitral valve (MV) and at least a portion of the distal anchoring element  132  can be positioned in a subannular position distal to the annulus and/or in any other suitable position in which the distal anchoring element  132  can engage native tissue, leaflets, chordae, etc. 
     In some implementations, the prosthetic valve  100  can be temporarily maintained in a partially deployed state. For example, the valve  100  can be partially inserted into the annulus and held at an angle relative to the annulus to allow blood to flow from the atrium to the ventricle partially through the native valve annulus around the valve  100 , and partially through the valve  100 , which can allow for assessment of the valve function. 
     The valve  100  can be placed or seated in the annulus (PVA, MVA, AVA, and/or TVA) of the native valve (PV, MV, AV, and/or TV) such that the subannular region  130  (e.g., a ventricular collar) is disposed in a subannular position, the transannular region  112  of the valve frame  110  extends through the annulus, and the supra-annular region  120  (e.g., an atrial collar) remains in a supra-annular position. For example, in some embodiments, the delivery system  180 , the actuator, and/or any other suitable member, tool, etc. can be used to push at least the proximal end portion of the valve  100  into the annulus. In addition, the septal anchoring element  136  can be at least partially inserted through the annulus prior to the valve  100  being fully seated in the annulus. In some implementations, the septal anchoring element  136  can be in contact with, for example, subannular septal tissue (e.g., the native septal wall, a native septal leaflet, and/or the like) as the valve  100  is seated in the annulus, thereby providing stability during the seating process (e.g., rolling, twisting, rotating, and/or spinning about a distal-proximal axis of the valve  100  and/or about an axis associated with, for example, the guidewire or guidewire assembly extending along the longitudinal length of the valve  100 . 
     In some implementations, the proximal anchoring element  134  can be maintained in its first configuration as the valve  100  is seated in the annulus. For example, as described above, the proximal anchoring element  134  can be in a compressed, contracted, and/or retracted configuration in which the proximal anchoring element  134  is in contact with, adjacent to, and/or near the transannular region  112  and/or the supra-annular region  120  of the frame  110 , which in turn, can limit an overall circumference of the subannular region  130  of the frame  110 , thereby allowing the subannular region  130  and the transannular region  112  of the frame  110  to be inserted into and/or through the annulus. 
     Once seated, the proximal anchoring element  134  can be transitioned from its first configuration to its second configuration, as described in detail in the &#39;978 WIPO publication. For example, in some implementations, a user can manipulate a portion of the delivery system to actuate the actuator. In some implementations, actuating the actuator can release and/or reduce an amount of tension within or more tethers, cables, connections, and/or portions of the actuator, thereby allowing the proximal anchoring element  134  to transition. Accordingly, once the valve  100  is seated in the annulus, the proximal anchoring element  134  can be placed in its second configuration in which the proximal anchoring element  134  contacts, engages, and/or is otherwise disposed adjacent to subannular tissue. In some embodiments, the septal anchoring element  136  similarly can be transitioned from a first configuration to a second configuration. In some implementations, placing at least one of the proximal anchoring element  134  and/or the septal anchoring element  136  can reduce an extent (e.g., size or diameter) of the subannular region  130  or lower portion of the transannular region  112  to allow the valve  100  to be inserted into and at least partially through the annulus. In such implementations, once the valve  100  is at least partially seated in the annulus, the proximal anchoring element  134  and/or the septal anchoring element  136  can then be transitioned from the first (e.g., compressed) configuration(s) to the second (e.g., extended) configuration(s) to stabilize, anchor, and/or secure the valve  100  in the annulus of the native valve. 
     Although not shown in  FIGS.  1 - 5   , in some embodiments, any of the distal anchoring element  132 , the proximal anchoring element  134 , and/or the septal anchoring element  136  can be configured to selectively engage native tissue, chordae, trabeculae, annular tissue, leaflet tissue, and/or any other anatomic structures to aid in the securement of the valve  100  in the native annulus. For example, one or more of the anchoring elements  132 ,  134 , and/or  136  can include any suitable feature, surface, member, etc. configured to facilitate the engagement between the anchoring elements  132 ,  134 , and/or  136  and the native tissue. In some implementations, such features and/or members can engage and/or otherwise become entangled in the native tissue, chordae, trabeculae, annular tissue, leaflet tissue, and/or any other anatomic structures, thereby enhancing and/or facilitating the securement of the valve  100  in the annulus. 
     As described above, the distal anchoring element  132  can be configured to engage native tissue on a distal side of the annulus, the proximal anchoring element  134  can be configured to engage native tissue on a proximal side of the annulus (e.g., when in the second or expanded configuration), and the septal anchoring element  136  can be configured to engage native tissue of a septal side of the annulus (e.g., the septal wall or native septal leaflet tissue), thereby securely seating the valve  100  in the native annulus, as shown in  FIG.  5   . In some implementations, any other or additional portions of the valve  100  can similarly engage native tissue to securely seat the valve  100  in the native annulus and/or to form a seal between the support frame  110  and the tissue forming the native annulus (e.g., an anterior anchoring element can engage subannular tissue on an anterior side of the annulus, or the supra-annular region  120  can include any number of supra-annular anchoring elements for engaging supra-annular tissue (not shown in  FIGS.  1 - 5   )). 
       FIG.  6    is a side perspective view illustration of a side-deliverable transcatheter prosthetic valve  200  (also referred to herein a “prosthetic valve” or simply “valve”) according to an embodiment. The valve  200  can be any suitable shape, size, and/or configuration. For example, in some embodiments, the valve  200  can be similar in at least form and/or function to the valve  100  described above with reference to  FIGS.  1 - 5   . 
     As shown, the valve  200  generally includes an annular support frame  210  and a flow control component  250 . In addition, the valve  200  and/or at least the annular support frame  210  of the valve  200  includes one or more anchoring element. For example, the annular support frame  210  can include at least a septal stability and/or anchoring element  236 , a distal anchoring element  232  and a proximal anchoring element  234 . In some implementations, the septal stability and/or anchoring element  236 , the distal anchoring element  232  and the proximal anchoring element  234  can all be lower anchoring elements. In other embodiments, the valve  200  and/or the annular support frame  210  can include a distal upper anchoring element and a proximal upper anchoring element for atrial anchoring. 
     The annular support frame  210  (also referred to herein as “tubular frame,” “valve frame,” “wire frame,” or “frame”) can have or can define an aperture  214  that extends along a central axis. The aperture  214  (e.g., a central axial lumen) can be sized and configured to receive the flow control component  250  across a diameter of the aperture  214 . The frame  210  may have an outer circumferential surface for engaging native annular tissue that may be tensioned against an inner aspect of the native annulus to provide structural patency to a weakened native annular ring. 
     The frame  210  includes a cuff or collar  220  (e.g., a supra-annular region) and a tubular or transannular section  212 . The cuff or collar  220  (referred to herein as “collar”) can be attached to and/or can form an upper edge of the frame  210 . When the valve  200  is deployed within a human heart, the collar  220  can be an atrial collar. The collar  220  can be shaped to conform to the native deployment location. In a mitral replacement, for example, the collar  220  will be configured with varying portions to conform to the native valve. In one embodiment, the collar  220  will have a distal and proximal upper collar portion. The distal collar portion can be larger than the proximal upper collar portion to account for annular geometries, supra-annular geometries, and/or subannular geometries. 
     The frame  210  may optionally have a separate atrial collar attached to the upper (atrial) edge of the frame  210 , for deploying on the atrial floor that is used to direct blood from the atrium into the flow control component  250  and to seal against blood leakage (perivalvular leakage) around the frame  210 . The frame  210  may also optionally have a separate ventricular collar (e.g., a subannular region) attached to the lower (ventricular) edge of the frame  210 , for deploying in the ventricle immediately below the native annulus that is used to prevent regurgitant leakage during systole, to prevent dislodging of the valve  200  during systole, to sandwich or compress the native annulus or adjacent tissue against the atrial collar or collar  220 , and/or optionally to attach to and support the flow control component  250 . Some embodiments may have both an atrial collar and a ventricular collar, whereas other embodiments either include a single atrial collar, a single ventricular collar, or have no additional collar structure. 
     The frame  210  can be a ring, or cylindrical or conical tube, but may also have a side profile of a flat-cone shape, an inverted flat-cone shape (narrower at top, wider at bottom), a concave cylinder (walls bent in), a convex cylinder (walls bulging out), an angular hourglass, a curved, graduated hourglass, a ring or cylinder having a flared top, flared bottom, or both. The frame  210  may have a height in the range of about 5-60 mm, may have an outer diameter dimension, R, in the range of about 20-80 mm, and may have an inner diameter dimension in the range of about 21-79 mm, accounting for the thickness of the frame  210  (e.g., a wire material forming the frame  210 ). 
     The frame  210  is compressible for delivery and when released it is configured to return to its original (uncompressed) shape. The frame  210  may be compressed for transcatheter delivery and may be expandable using a transcatheter expansion balloon. In other implementations, the frame  210  can include and/or can be formed of a shape-memory element allowing the frame  210  to be self-expanding. In some instances, suitable shape-memory materials can include metals and/or plastics that are durable and biocompatible. For example, the frame  210  can be made from super elastic metal wire, such as a Nitinol wire or other similarly functioning material. The frame  210  may be constructed as a braid, wire, or laser cut wire frame. The frame  210  may also have and/or form additional functional elements (e.g., loops, anchors, etc.) for attaching accessory components such as biocompatible covers, tissue anchors, releasable deployment and retrieval control guides, knobs, attachments, rigging, and so forth. 
     As described above, the frame  210  and/or the valve  200  can include at least the distal anchoring element  232  and the proximal anchoring element  234 . The distal and proximal anchoring elements  232  and  234  can be, for example, lower anchoring elements (e.g., coupled to and/or included in a lower portion or subannular region of the frame  210 ). In some embodiments, the frame  210  and/or the valve  200  can also optionally include one or more of a distal upper anchoring element and a proximal upper anchoring element. The anchoring elements  232  and  234  of the valve  200  can be configured to engage a desired portion of the annular tissue to mount the frame  210  to the annulus of the native valve in which the valve  200  is deployed, as described in further detail herein. The anchoring elements  232  and  234  of the valve  200  and/or the frame  210  can be any suitable shape, size, and/or configuration. Moreover, certain aspects, features, and/or configurations of at least the distal and proximal anchoring elements  232  and  234  are described below reference to specific embodiments. 
     The frame  210  can also include the septal stability and/or anchoring element  236  (also referred to herein as “septal anchoring element”). The septal anchoring element  236  can be any suitable shape, size, and/or configuration such as any of those described herein with respect to specific embodiments. In some embodiments, for example, the septal anchoring element  236  can be, for example, integrally formed with the lower sidewall portion  230  of the frame  210  (e.g., can be a portion of the wireframe or laser-cut frame portion). In some implementations, the septal anchoring element  236  (e.g., leaflet brace or the like) is a lower anchoring element configured to engage subannular tissue of the ventricle to aid in the securement of the valve  200  in the annulus. More specifically, the septal anchoring element  236  can be configured to engage subannular septal tissue, septal leaflet tissue, and/or any other suitable tissue at, near, and/or along the septum of the heart. 
     In some implementations, the proximal anchoring element  234  can be configured to transition between a first configuration in which the proximal anchoring element  234  is maintained in a compressed, undeployed, and/or restrained state, to a second configuration in which the proximal anchoring element  234  is expanded, extended, deployed, and/or unrestrained. More specifically, the proximal anchoring element  234  when in the first configuration can be maintained in a first position that is in contact with, adjacent to, and/or otherwise near the transannular section  250  of the valve frame  210 , and when in the second configuration, can be released to a second position that extends away from the transannular section  250  of the frame  210 . Said another way, the second position proximal anchoring element  234  can be further from the transannular section  250  than the first position of the proximal anchoring element  234 . 
     In some embodiments, the valve  200  and/or the frame  210  can include a feature, member, mechanism, etc. configured to at least temporarily retain the proximal anchoring element  234  in the first configuration. For example, as shown in  FIG.  6   , the valve  200  and/or the frame  210  can include a tensile member configured to selectively engage the proximal anchoring element  234  to temporarily maintain the proximal anchoring element  234  in the first configuration. The tensile member can be any suitable shape, size, and/or configuration. For example, the tensile member can be an anchor, loop, tab, latch, hook, tether, elastomeric band, threaded coupler, ball and cup mechanism, and/or any other suitable removable attachment. The tensile member can removably couple to a portion of the proximal anchoring element  234  and can exert a force (e.g., a tensile or compression force) operable in maintaining the proximal anchoring element  234  in the first configuration. The tensile member can be reconfigurable allowing the tensile member to be disengaged from the proximal anchoring element  234 , which in turn, can allow the proximal anchoring element  234  to transition from its first configuration to its second configuration, as described in further detail herein with reference to specific embodiments. 
     The flow control component  250  can refer in a non-limiting sense to a device for controlling fluid flow therethrough. In some embodiments, the flow control component  250  can be a leaflet structure having two, three, four, or more leaflets made of flexible biocompatible material such a treated or untreated pericardium. The flow control component  250  with leaflets can be sewn or joined to a support structure and/or can be sewn or joined to the frame  210 . The flow control component  250  can be mounted within the frame  210  and configured to permit blood flow in a first direction through an inflow end of the valve and block blood flow in a second direction, opposite the first direction, through an outflow end of the valve. For example, the flow control component  250  can be configured such that the valve  200  functions, for example, as a heart valve, such as a tricuspid valve, mitral valve, aortic valve, or pulmonary valve, that can open to blood flowing during diastole from atrium to ventricle, and that can close from systolic ventricular pressure applied to the outer surface. Repeated opening and closing in sequence can be described as “reciprocating.” 
     The flow control component  250  is contemplated to include a wide variety of (bio)prosthetic artificial valves, including ball valves (e.g., Starr-Edwards), bileaflet valves (St. Jude), tilting disc valves (e.g., Bjork-Shiley), stented pericardium heart-valve prosthesis&#39; (bovine, porcine, ovine) (Edwards line of bioprostheses, St. Jude prosthetic valves), as well as homograft and autograft valves. Bioprosthetic pericardial valves can include bioprosthetic aortic valves, bioprosthetic mitral valves, bioprosthetic tricuspid valves, and bioprosthetic pulmonary valves. In some implementations, a suitable commercially available valve (flow control component  250 ) can be received or accepted by and/or otherwise mounted in the frame  210 . Commercially available valves (flow control components  250 ) may include, for example, a Sapien, Sapien 3, or Sapien XT from Edwards Lifesciences, an Inspiris Resilia aortic valve from Edwards Lifesciences, a Masters HP 15 mm valve from Abbott, a Lotus Edge valve from Boston Scientific, a Crown PRT leaflet structure from Livanova/Sorin, a valve from the Carbomedics family of valves from Sorin, or other flow control component(s), or a flexible reciprocating sleeve or sleeve-valve. 
     In one embodiment,  FIG.  6    is an illustration of a plan view of valve  200  with a septal anchoring or stability element  236  (e.g., arm, tab, extension, etc.), a distal anchoring element  232  (e.g., arm, tab, extension, etc.), and a proximal anchoring element  234  (e.g., arm, tab, extension, etc.), according to the invention. A guidewire coupler  233  is attached at the distal end of the distal anchor element  232  and provides one method of mounting and/or receiving the guidewire. The outer frame  210  is shown as an elliptic cylinder having the upper collar portion  220  (e.g., the supra-annular region), the lower sidewall portion  230  (e.g., the subannular region), and the transannular portion or region  212  disposed therebetween. The flow control component  250  (with leaflets mounted therein) is shown occupying a 25-35 mm diameter space within the elliptic cylinder of the outer frame  210  with a spacer panel  221  filling in the remaining space. In some embodiments, a catheter guide (not shown) can be attached at a proximal side of the upper collar portion  220  of the outer frame  210 . The proximal anchoring element  234  is shown attached to a proximal end of the lower sidewall portion  230  of the outer frame  210 . The septal anchoring element  236  is shown attached to a mid-point of the lower sidewall portion  230  of the outer frame  210  and extends in a septal direction or extends along the septal side of the lower sidewall portion  230  in a subannular direction. 
       FIG.  7    is a side perspective view illustration of a side-deliverable transcatheter prosthetic valve  300  (also referred to herein a “prosthetic valve” or simply “valve”) according to an embodiment. The valve  300  has an outer frame  310 , which is shown as an elliptic cylinder having an upper collar portion  320  (e.g., a supra-annular region) and a lower sidewall portion  330  (e.g., a subannular region). A flow control component  350  with prosthetic leaflets is shown occupying a portion (e.g., a 25-35 mm diameter space) within the elliptic cylinder of the outer frame  310  with a spacer panel  321  filling in the remaining space. The frame  310  is shown with a septal anchoring element  336 , a distal anchoring element  332 , and a proximal anchoring element  334  attached to a lower sidewall portion  330  of a transannular region  312  of the frame  310  (also referred to as a subannular region). A guidewire coupler  333  is attached at the distal end of the distal anchoring element  332  and provides one method of mounting and/or receiving a guidewire (not shown). In some embodiments, a catheter guide (not shown) can be attached at a proximal side of the upper collar portion  320  of the outer frame  310 . The proximal anchoring element  334  is shown attached to the lower proximal sidewall portion  330  of the outer frame  310  and extends in a proximal direction. The septal anchoring element  336  is shown attached to a mid-point of the lower sidewall portion  330  and extends in a septal direction or extends along the septal side of the lower sidewall portion  330  in a subannular direction. 
       FIG.  8    is an underside view illustration of a side-deliverable transcatheter prosthetic valve  400  (also referred to herein a “prosthetic valve” or simply “valve”) according to an embodiment. The valve  400  has an outer frame  410 , which is shown as an elliptic cylinder having an upper collar portion  420  (e.g., a supra-annular region) and a lower sidewall portion  430  (e.g., a subannular region). A flow control component  450  is mounted within an aperture  414  defined by an interior of the frame  410 . The flow control component  450  has leaflets  456  that are shown mounted on an inner leaflet frame  451 . The frame  410  is shown with a septal anchoring element  436 , a distal anchoring element  432 , and a proximal anchoring element  434 . A guidewire coupler  433  is attached at the distal end of the distal anchor element  432  and provides one method of mounting and/or receiving a guidewire (not shown). Another method of mounting the guidewire is configuring the distal anchor element  432  as a hollow tubular element. In some embodiments, a catheter guide (not shown) can be attached at a proximal side of the upper collar portion  420  (e.g., a supra-annular region) of the outer frame  410 . The proximal anchoring element  434  is shown attached to the lower proximal sidewall portion  430  of the outer frame  410  and extends in a proximal direction. The septal anchoring element  436  is shown attached to a mid-point of the lower sidewall portion  430  and extends in a septal direction or extends along the septal side of the lower sidewall portion  430  in a subannular direction. 
       FIG.  9    is a top view illustration of a side-deliverable transcatheter prosthetic valve  500  (also referred to herein a “prosthetic valve” or simply “valve”) according to an embodiment. The valve  500  has an outer frame  510 , which is shown as an elliptic cylinder. A flow control component  550  with prosthetic leaflets is shown occupying a portion (e.g., a 25-35 mm diameter space) within the elliptic cylinder of the outer frame  510  with a spacer panel  521  filling in the remaining space. The frame  510  is shown with a septal anchoring element  536 , a distal anchoring element  532 , and a proximal anchoring element  534 . In some embodiments, frame  510  can also include an anterior anchoring element  538  disposed on an anterior side of the frame  510  opposite the septal anchoring element  536 . In some embodiments, a catheter guide (not shown) can be attached at a proximal side of an upper collar portion  520  (e.g., a supra-annular region) of the outer frame  510 . 
       FIG.  10    is a side perspective view illustration of a wire frame  610  for a side-deliverable transcatheter prosthetic valve highlighting a septal stability and/or anchoring element  636 , according to an embodiment.  FIG.  10    shows an upper collar  620  (e.g., a supra-annular region) and a transannular frame sidewall  612  (e.g., a transannular region) of the wire frame  610 . The septal stability and/or anchoring element  636  is shown abutting, for example, native septal tissue, septal side annular tissue, and/or septal leaflet tissue, which in turn, is blocked from interfering with the functioning of the leaflets of a flow control component (not shown) disposed in the valve frame  610 . 
       FIGS.  11  and  12    are side view illustrations of a side-deliverable transcatheter prosthetic valve  700  (also referred to herein as “prosthetic valve” or simply “valve”) according to an embodiment.  FIG.  11    shows the prosthetic valve  700  positioned in an annulus of a native tricuspid valve prior to stabilizing and/or anchoring the prosthetic valve  700 .  FIG.  12    shows the prosthetic valve  700  with at least a distal anchoring element  732  that can anchor at least a distal portion of the valve  700  (e.g., in or at a ventricular outflow tract and/or the like). The prosthetic valve  700  is further shown with a septal anchoring element  736 , and an anterior stability and/or anchoring element  738  engaging native septal tissue and native anterior tissue, respectively, to stabilize and/or anchor the prosthetic valve  700  in the annulus. 
       FIG.  13    is a side perspective view illustration of a side-deliverable transcatheter prosthetic valve  800  (also referred to herein as “prosthetic valve” or simply “valve”) according to an embodiment. The valve  800  has an outer frame  810 , which is shown as an elliptic cylinder having an upper collar portion  820  (e.g., a supra-annular region) and a lower sidewall portion  830  (e.g., a subannular region). A flow control component  850  with prosthetic leaflets is shown occupying a portion (e.g., a 25-35 mm diameter space) within the elliptic cylinder of the outer frame  810  with a spacer panel  821  filling in the remaining space. The frame  810  is shown having a distally located septal anchoring element  836 , a distal anchoring element  832 , and a proximal anchoring element  834 . In some implementations, the distally located septal anchoring element  836  (e.g., a brace and/or the like) may be indicated for treating specific anatomical structures. 
       FIG.  14    is a side perspective view illustration of a side-deliverable transcatheter prosthetic valve  900  (also referred to herein as “prosthetic valve” or simply “valve”) according to an embodiment. The valve  900  has an outer frame  910 , which is shown as an elliptic cylinder having an upper collar portion  920  (e.g., a supra-annular region) and a lower sidewall portion  930  (e.g., a subannular region). A flow control component  950  with prosthetic leaflets is shown occupying a portion (e.g., a 25-35 mm diameter space) within the elliptic cylinder of the outer frame  910  with a spacer panel  921  filling in the remaining space. The frame  910  is shown having a proximally located septal anchoring element  936 , a distal anchoring element  932 , and a proximal anchoring element  934 . In some implementations, the proximally located septal anchoring element  936  may be indicated for avoiding interference with native electrical tissue or with the coronary sinus return. 
       FIG.  15    is a side perspective view illustration of a side-deliverable transcatheter prosthetic valve  1000  (also referred to herein as “prosthetic valve” or simply “valve”) according to an embodiment. The valve  1000  has an outer frame  1010 , which is shown as an elliptic cylinder having an upper collar portion  1020  (e.g., a supra-annular region) and a lower sidewall portion  1030  (e.g., a subannular region). A flow control component  1050  with prosthetic leaflets is shown occupying a portion (e.g., a 25-35 mm diameter space) within the elliptic cylinder of the outer frame  1010  with a spacer panel  1021  filling in the remaining space. The frame  1010  is shown having a shortened (relatively shallow) centrally located septal anchoring element  1036 , a distal anchoring element  1032 , and a proximal anchoring element  1034 . In some implementations, the shallow septal anchoring element  1036  (e.g., a brace and/or the like) may be indicated for avoiding excessive cutting effect on the ventricular tissue. 
       FIG.  16    is a side perspective view illustration of a side-deliverable transcatheter prosthetic valve  1100  (also referred to herein as “prosthetic valve” or simply “valve”) according to an embodiment. The valve  1100  has an outer frame  1110 , which is shown as an elliptic cylinder having an upper collar portion  1120  (e.g., a supra-annular region) and a lower sidewall portion  1130  (e.g., a subannular region). A flow control component  1150  with prosthetic leaflets is shown occupying a portion (e.g., a 25-35 mm diameter space) within the elliptic cylinder of the outer frame  1110  with a spacer panel  1121  filling in the remaining space. The frame  1110  is shown having an extended-depth, centrally located septal anchoring element  1136 , a distal anchoring element  1132 , and a proximal anchoring element  1134 . In some implementations, the extended septal anchoring element  1136  (e.g., a brace and/or the like) may be indicated in treatment to block additional tissue from interfering with the functioning of the prosthetic valve  1100  and/or to provide additional ventricular stability to prevent unwanted movement of the prosthetic valve  1100  prior to in-growth, such as rolling, tilting, or other unwanted migration of the implant. 
       FIG.  17    is a side perspective view illustration of a side-deliverable transcatheter prosthetic valve  1200  (also referred to herein as “prosthetic valve” or simply “valve”) according to an embodiment. The valve  1200  has an outer frame  1210 , which is shown as an elliptic cylinder having an upper collar portion  1220  (e.g., a supra-annular region) and a lower sidewall portion  1230  (e.g., a subannular region). A flow control component  1250  with prosthetic leaflets is shown occupying a portion (e.g., a 25-35 mm diameter space) within the elliptic cylinder of the outer frame  1210  with a spacer panel  1221  filling in the remaining space. The frame  1210  is shown having an asymmetric-shaped septal anchoring element  1236 , a distal anchoring element  1232 , and a proximal anchoring element  1234 . In some implementations, the asymmetrical septal anchoring element  1236  (e.g., a brace and/or the like) may be indicated for avoiding interference with native electrical tissue or with the coronary sinus return. 
       FIG.  18    is a side perspective view illustration of a side-deliverable transcatheter prosthetic valve  1300  having a wire-braid frame  1310 , a septal anchoring element  1336 , a distal anchoring element  1332 , and a proximal anchoring element  1334 , according to an embodiment. In some embodiments, the septal anchoring element  1336  can be formed by a portion of the wire-braid frame  1310  and can extend away from an atrial collar  1320  (e.g., a supra-annular region) of the frame  1310 . The septal anchoring element  1336  can have any suitable configuration indicated, in some implementations, for treating specific anatomical structures, avoiding interference with native electrical tissue or with the coronary sinus return, avoiding excessive cutting effect on the ventricular tissue, blocking native tissue from interfering with the functioning of the prosthetic valve  1300  (e.g., leaflets of a flow control component), providing additional ventricular stability to prevent unwanted movement of the prosthetic valve  1300  prior to in-growth, such as rolling, tilting, or other unwanted migration of the implant, and/or the like. 
       FIG.  19    is a side perspective view illustration of a side-deliverable transcatheter prosthetic valve  1400  having a laser-cut frame  1410 , a septal anchoring element  1436 , a distal anchoring element  1432 , and a proximal anchoring element  1434 , according to an embodiment. A tensile member  1435  is shown, which can be used to release and/or to otherwise facilitate the release of the proximal anchoring element  1434  from its compressed (first) configuration to its expanded (second) configuration. In some embodiments, the septal anchoring element  1436  can be formed by a portion of the wire-braid frame  1410  and can extend away from an atrial collar  1420  (e.g., a supra-annular region) of the frame  1410 . The septal anchoring element  1436  can have any suitable configuration indicated, in some implementations, for treating specific anatomical structures, avoiding interference with native electrical tissue or with the coronary sinus return, avoiding excessive cutting effect on the ventricular tissue, blocking native tissue from interfering with the functioning of the prosthetic valve  1400  (e.g., leaflets of a flow control component), providing additional ventricular stability to prevent unwanted movement of the prosthetic valve  1400  prior to in-growth, such as rolling, tilting, or other unwanted migration of the implant, and/or the like. 
       FIGS.  20  and  21    are a distal side view illustration and a proximal side view illustration, respectively, of a side-deliverable transcatheter prosthetic valve  1500  (also referred to herein as “prosthetic valve” or simply “valve”) according to an embodiment. The valve  1500  has an outer frame  1510 , which is shown as an elliptic cylinder having an upper collar portion  1520  (e.g., a supra-annular region) and a lower sidewall portion  1530  (e.g., a subannular region). A flow control component with prosthetic leaflets (not shown) can be mounted within the elliptic cylinder of the outer frame  1510 . The frame  1510  is shown having a septal anchoring element  1536 , a distal anchoring element  1532 , and a proximal anchoring element  1534 .  FIG.  20    shows the distal anchoring element  1532  extending away from an annular support frame  1510  of the valve  1500 . The distal anchoring element  1532  is shown with a guidewire coupler  1533  configured to at least temporarily couple to and/or otherwise receive a guidewire to facilitate delivery of the valve  1500  into an annulus of a native valve. 
       FIG.  21    shows the proximal anchoring element  1534  having an upper parabolic arch support member and a lower parabolic arch support member, with a flexible spacer fabric or structured-fabric stretched between the upper and lower arch supports. The lower arch support can rotate about its end portions, whereby in a stowed, or up position, the lower arch support is coextensive with the upper arch support (i.e., both lie atop one another with the parabolic opening facing down). A tensile member (not shown) can be used to hold the lower arch support in a stowed, upper position until the tensile member is released (e.g., holds the proximal anchoring element  1534  in its compressed (first) configuration). When the tensile member is released, the lower arch support rotates downward from shape-memory effect, pulling the flexible structured fabric taut and placing the proximal anchoring element  1534  in its expanded (second) configuration such that the lower arch support lays under the native annulus and the taut fabric substantially form fits the native annular and/or subannular tissue. 
       FIG.  21    further shows the septal anchoring element  1536  configured as an integrated tab, arm, extension, and/or the like of the frame  1510 . The septal anchoring element  1536  is disposed along a septal side of the lower sidewall portion  1530  and adjacent to and/or otherwise near the proximal anchoring element  1534 . Said another way, the septal anchoring element  1536  is proximally located. 
     Referring now to  FIG.  22   , a flowchart is shown illustrating a method  10  of deploying a prosthetic heart valve in an annulus of a native valve of a heart of a patient, according an embodiment. The prosthetic heart valve can be, for example, a side-deliverable transcatheter prosthetic heart valve such as any of those described herein. The prosthetic heart valve is transitionable between a first, compressed configuration for side-delivery via a delivery catheter and a second, expanded configuration for deployment into the annulus of the native valve. As described above, the native valve can be any of the valves of the heart. In some implementations, for example, the native valve is one of the tricuspid valve or the mitral valve. In some embodiments, for example, the prosthetic heart valve can include a frame and a flow control component mounted within a central channel of the frame. The flow control component is configured to permit blood flow in a first direction through the prosthetic heart valve from an inflow end to an outflow end and to block blood flow in a second direction, opposite the first direction. The frame can include, for example, at least a supra-annular region or collar and a transannular region coupled to the supra-annular region and extending in a perpendicular relative to a plane associated with and/or at least partially across the supra-annular region. In some implementations, a lower portion of the transannular region can form and/or include a subannular region of the frame. In some implementations, the subannular region is separate from the transannular region and coupled thereto in a manner similar to the coupling of the transannular region to the supra-annular region. The subannular region of the frame includes, forms, and/or is coupled to at least a distal anchoring element, a proximal anchoring element, and a septal anchoring element. In some embodiments, each of the distal anchoring element, the proximal anchoring element, and the septal anchoring element can be at least one of a wire loop, a wire frame, a laser cut frame, an integrated frame section, or a stent, and can extend from the subannular region a desired distance (e.g., about 10-40 mm). 
     The method  10  includes disposing in the atrium of the heart a distal end of a delivery catheter having disposed in a lumen thereof the prosthetic heart valve in the compressed configuration, at  11 . For example, for tricuspid valve or pulmonary valve replacement, the atrium can be accessed, for example, through the inferior vena cava (IVC) via the femoral vein or through the superior vena cava (SVC) via the jugular vein. As another example, for mitral valve the atrium can be accessed through a trans-atrial approach (e.g., fossa ovalis or lower), via the IVC-femoral or the SVC jugular approach. When the distal end of the delivery catheter is disposed in a desired position in the atrium of the heart, the prosthetic valve in the compressed configuration can be advanced (e.g., along a guidewire) through the lumen of the delivery catheter. As described above, the prosthetic heart valve can be a side-deliverable prosthetic heart valve such that an axis extending through the inflow end and the outflow end of the prosthetic heart valve is substantially orthogonal to a lengthwise axis extending through the lumen of the delivery catheter. Said another way a longitudinal axis extending through the prosthetic valve is substantially parallel to the lengthwise axis extending through the lumen of the delivery catheter, as described in detail above with reference to the valve  100 . 
     The prosthetic heart valve is released from the lumen of the delivery catheter such that the prosthetic heart valve transitions from the compressed configuration to the expanded configuration, at  12 . In some implementations, the prosthetic heart valve can be advanced through the delivery catheter such that the distal anchoring element is distal to the remaining portions of the valve and thus, is first released from the distal end of the delivery catheter. As the prosthetic valve is further advances, the valve and/or at least the valve frame is allowed to expand (e.g., it is no longer constrained by the inner surface of the delivery catheter. In some implementations, the prosthetic valve can be in its expanded configuration when the prosthetic valve is completely released or otherwise outside of the delivery catheter (e.g., disposed in the atrium of the heart). 
     In some implementations, at least a portion of the prosthetic valve can be inserted into the annulus of the native valve while portions of the prosthetic valve are still being released from the delivery catheter. For example, for tricuspid valve replacement, the distal anchoring element can be inserted through the annulus and into a right ventricular outflow track (RVOT) as the prosthetic valve is released from the delivery catheter. As another example, for mitral valve replacement, the distal anchoring element can be inserted through the annulus and into a subannular position distal to the annulus as the prosthetic valve is released from the delivery catheter. 
     At least a portion of the prosthetic heart valve is seated in the annulus of the native valve, at  13 . In some implementations, the seating of the prosthetic valve in the annulus can include inserting the proximal anchoring element and the septal anchoring element into and/or through the annulus prior to or as the prosthetic valve is being seated in the annulus. In addition, the method  10  includes placing the septal anchoring element in contact with at least one of a native septal wall or a septal leaflet area to stabilize the prosthetic heart valve in the annulus when the prosthetic heart valve is seated in the annulus, at  14 . For example, the septal anchoring element can stabilize the prosthetic heart valve against at least one of intra-annular rolling forces or intra-annular twisting forces within the annulus during deployment or seating of the valve in the annulus or after the valve is deployed and/or secured in the annulus. 
     In some implementations, seating the prosthetic valve in the annulus is such that the proximal anchoring element is placed in contact with subannular tissue on the proximal side of the annulus. In some implementations, the proximal anchoring element is configured to transition from a first configuration to a second configuration after seating the prosthetic heart valve in the annulus to contact the proximal subannular tissue. In some implementations, the proximal anchoring element is transitioned from the first configuration to the second configuration by manipulating a tensile member coupled to the valve frame. 
     In some implementations, the septal anchoring element similarly can be configured to transition from a first configuration to a second configuration after the prosthetic valve in the annulus. In other implementations, the septal anchoring element can be an anchoring element having a single or substantially fixed configuration. The septal anchoring element can have any suitable configuration indicated, in some implementations, for treating specific anatomical structures, avoiding interference with native electrical tissue or with the coronary sinus return, avoiding excessive cutting effect on the ventricular tissue, blocking native tissue from interfering with the functioning of the prosthetic valve (e.g., leaflets of a flow control component), providing additional ventricular stability to prevent unwanted movement of the prosthetic valve prior to in-growth, such as rolling, tilting, or other unwanted migration of the implant, and/or the like, as described above with reference to the septal anchoring elements described above with reference to specific embodiments. 
     While various embodiments have been described above, it should be understood that they have been presented by way of example only, and not limitation. Likewise, it should be understood that the specific terminology used herein is for the purpose of describing particular embodiments and/or features or components thereof and is not intended to be limiting. Various modifications, changes, and/or variations in form and/or detail may be made without departing from the scope of the disclosure and/or without altering the function and/or advantages thereof unless expressly stated otherwise. Functionally equivalent embodiments, implementations, and/or methods, in addition to those enumerated herein, will be apparent to those skilled in the art from the foregoing descriptions and are intended to fall within the scope of the disclosure. 
     Where schematics and/or embodiments described above indicate certain components arranged in certain orientations or positions, the arrangement of components may be modified. Although various embodiments have been described as having particular features and/or combinations of components, other embodiments are possible having a combination of any features and/or components from any of embodiments described herein, except mutually exclusive combinations. The embodiments described herein can include various combinations and/or sub-combinations of the functions, components, and/or features of the different embodiments described. 
     Where methods described above indicate certain events occurring in certain order, the ordering of certain events may be modified. Additionally, certain of the events may be performed concurrently in a parallel process when possible, as well as performed sequentially as described above. While methods have been described as having particular steps and/or combinations of steps, other methods are possible having a combination of any steps from any of methods described herein, except mutually exclusive combinations and/or unless the context clearly states otherwise.