阅读说明：本技术 心脏瓣膜假体 (Heart valve prosthesis ) 是由 斯科特·罗伯森 埃利奥特·霍华德 于 2016-10-05 设计创作，主要内容包括：本发明公开了用于经皮心脏瓣膜置换的人工心脏瓣膜装置及相关方法。根据此方法配置的经导管的瓣膜假体(100)包括具有瓣膜支持结构(120)和与其耦接的一个或多个支撑臂(140)的框架(100)。当瓣膜假体处于扩张构型时,所述一个或多个支撑臂被配置为从所述瓣膜支持结构的第二端朝向第一端延伸。当在扩张构型中展开时,所述一个或多个支撑臂具有曲线形状,例如大体上S形,至少部分地与天然心脏瓣膜处的组织结合。(Prosthetic heart valve devices for percutaneous heart valve replacement and related methods are disclosed. A transcatheter valve prosthesis (100) configured according to this method includes a frame (100) having a valve support structure (120) and one or more support arms (140) coupled thereto. The one or more support arms are configured to extend from the second end toward the first end of the valve support structure when the valve prosthesis is in the expanded configuration. When deployed in the expanded configuration, the one or more support arms have a curvilinear shape, such as a substantially S-shape, at least partially engaging tissue at the native heart valve.)

1. A heart valve repair device comprising:

a frame, the frame comprising:

a support structure having an upstream portion configured to be positioned proximal to the left atrium, a downstream portion configured to be positioned proximal to the left ventricle, and a first cross-sectional dimension;

a radially extending segment extending from the upstream portion of the support structure and having a second cross-sectional dimension that is greater than the first cross-sectional dimension, wherein the radially extending segment is configured to engage cardiac tissue of the left atrium; and

a support arm extending from the downstream portion of the support structure, wherein the support arm extends radially outward from the downstream portion of the support structure and rearward toward the upstream portion of the support structure when the heart valve repair device is in an expanded configuration; and is

The support arms are configured to extend behind native leaflets of a native mitral valve and engage sub-annular tissue within the left ventricle;

the support arm having a curvilinear shape with opposing first and second arcuate regions longitudinally separated by a substantially linear region extending therebetween;

the first arcuate region extends from the downstream portion of the support structure and curves toward the support structure;

the substantially straight region is angled inwardly toward the support structure about a longitudinal axis of the support structure and joins the first and second arcuate regions;

and the second arcuate region curves outwardly away from the support structure proximal of the upstream portion;

the second arcuate region is configured to atraumatically coapt with sub-annular tissue posterior to the native leaflet.

2. The heart valve repair device of claim 1, wherein the second arcuate region has a land area configured to atraumatically engage sub-annular tissue posterior to the native leaflet, and wherein the land area has a width greater than a width of a remainder of the support arm.

3. The heart valve repair device of claim 1, wherein the first arcuate region, the second arcuate region, and the substantially linear region together form a substantially S-shape.

4. The heart valve repair device of claim 1, wherein the second arc region defines a first curved segment that curves in an outward and upstream direction from a transition point to an apex of the support arm, and wherein the second arc region further defines a second curved segment that extends outward from the apex and curves slightly downward to a free end of the support arm.

5. The heart valve repair device of claim 1, wherein the radially extending section includes a plurality of interconnected struts extending radially outward from the first end of the support structure and away from the support structure in an upstream direction, wherein the radially extending section forms an atraumatic end.

Technical Field

The present technology relates generally to heart valve prostheses and related methods. In particular, several embodiments relate to transcatheter heart valve devices for percutaneous replacement of native heart valves, such as the mitral valve.

Background

The human heart is a four-chamber muscular organ that provides systemic blood circulation during the cardiac cycle. The four main chambers include the right atrium and the right ventricle, which provides the pulmonary circulation, and the left atrium and the left ventricle, which provides oxygenated blood received from the lungs to the rest of the body. To ensure blood flow in one direction of the heart, atrioventricular valves (tricuspid and mitral) are present at the junction of the atria and ventricles, and semilunar valves (pulmonary and aortic) control the exit of the ventricles to the lungs and rest of the body. These valves contain leaflets that open and close in response to changes in blood pressure caused by the contraction and relaxation of the ventricles. The leaflets separate from each other to open and allow blood to flow downstream of the valve and coapt against each other to close and prevent regurgitation or regurgitation in a retrograde fashion.

Diseases associated with heart valves, such as those caused by injury or defect, may include stenosis and valve insufficiency or regurgitation. For example, valvular stenosis causes the valve, which prevents blood flow to the downstream ventricle, to narrow and stiffen, to allow proper flow rates and to cause the heart to work harder to pump blood through the diseased valve. Valve insufficiency or regurgitation occurs when the valve is not fully closed, causing a reversal of blood flow, which results in reduced heart efficiency. Diseased or damaged valves, congenital, age-related, drug-induced or in some cases caused by infection, may lead to enlargement, thickening of the heart, which loses elasticity and efficiency. Some symptoms of heart valve disease include weakness, shortness of breath, dizziness, fainting, palpitations, anemia, and edema, as well as blood clots that increase the likelihood of stroke or pulmonary embolism. Symptoms are often severe enough to be debilitating and/or life threatening.

Prosthetic heart valves have been developed for use in repairing and replacing diseased and/or damaged heart valves. Such valves may be delivered percutaneously by a catheter-based system and deployed at the site of a diseased heart valve. Such prosthetic heart valves can be delivered in a low-profile or compressed/collapsed arrangement such that the prosthetic valve can be housed within a sheath assembly of a delivery catheter and advanced through the vasculature of a patient. Once positioned at the treatment site, the prosthetic valve can be expanded to engage tissue at the diseased heart valve area, for example, to hold the prosthetic valve in place. While these prosthetic valves provide a minimally invasive approach for heart valve repair and/or replacement, challenges remain in providing such a prosthetic valve that prevents leakage between the implanted prosthetic valve and surrounding tissue (paravalvular leakage) and movement and/or migration of the prosthetic valve that may occur during the cardiac cycle. For example, the mitral valve presents many challenges, such as dislodgement or improper placement of the prosthetic valve due to the presence of chordae tendineae (chordae tendineae) and residual leaflets, resulting in impingement of the valve. Additional challenges may include providing a prosthetic valve to resist premature failure of various components that may occur when subjected to the twisting forces imparted by the native anatomy and during the cardiac cycle. Further anatomical challenges associated with mitral valve treatment include providing a prosthetic valve that accommodates ovality or kidney shape. In addition, the kidney-shaped mitral annulus has muscles only along the outer wall of the valve, which has only a thin vessel wall separating the mitral and aortic valves. This anatomical muscle distribution, as well as the high pressures experienced when the left ventricle contracts, can be problematic for mitral valve prostheses.

Disclosure of Invention

Embodiments of the present invention relate to heart valve prostheses and methods of percutaneous implantation thereof. The heart valve prosthesis has a compressed configuration for delivery to a native heart valve of a patient via the vasculature or other body lumen; and an expanded configuration for deployment within the native heart valve. In one embodiment, a heart valve prosthesis may comprise: a frame having a valve support structure configured to retain a prosthetic valve assembly therein; and a plurality of support arms extending from the valve support structure such that the plurality of support arms are configured to extend toward a first end of the valve support structure to engage a subannular surface of the native heart valve when the heart valve prosthesis is in the expanded configuration. One or more of the plurality of support arms comprises a curvilinear support arm formed to have opposing first and second arcuate regions longitudinally separated by a straight line region extending therebetween, wherein the first arcuate region is formed proximate to a downstream portion thereof toward the valve support structure, the straight line region is formed to slope toward the valve support structure when connecting the first and second arcuate regions, and the second arcuate region is formed to curve away from an upstream portion thereof toward the valve support structure.

In another embodiment, a heart valve prosthesis for implantation in a native valve region of a heart includes a valve support structure having an upstream portion and a downstream portion, the valve support structure being configured to retain a prosthetic valve assembly therein and having a plurality of support arms extending from the downstream portion of the valve support structure. Each support arm is configured to extend from the downstream portion toward the upstream portion and has a curvilinear shape including a first curved region having a first radius of curvature, a second curved region having a second radius of curvature, and an elongated region extending between the first curved region and the second curved region when the heart valve prosthesis is in an expanded configuration. In such support arms, the curvilinear shape is configured to absorb twisting forces exerted thereon by the native valve region.

In another embodiment, a heart valve prosthesis for treating a native mitral valve of a patient is disclosed. The heart valve prosthesis includes a cylindrical support structure having an upstream portion, a downstream portion, and a first cross-sectional dimension, wherein the cylindrical support structure is configured to hold a prosthetic valve assembly that inhibits retrograde blood flow. A plurality of S-shaped support arms extend from a downstream portion of the cylindrical support structure such that when the heart valve prosthesis is in an expanded configuration, the S-shaped support arms are configured to extend in an upstream direction to engage heart tissue above or below an annulus (annuus) of the native mitral valve. The radially extending section extends from an upstream portion of the cylindrical support structure and has a second cross-sectional dimension that is greater than the first cross-sectional dimension. The radially-extending segment is configured to engage heart tissue over or upon the native mitral valve such that when the heart valve prosthesis is in an expanded configuration and deployed at the native mitral valve, the annulus is positioned between the upstream curved segment and the radially-extending segment of the S-shaped support arms.

Drawings

The above-described and other features and aspects of the present invention will be better understood from the following description of the embodiments and the accompanying drawings. The accompanying drawings, which are incorporated herein and form a part of the specification, further serve to explain the principles of the present technology. The components in the drawings are not necessarily to scale.

Fig. 1 is a schematic cross-sectional view of a mammalian heart having a native valve structure.

Fig. 2A is a schematic cross-sectional view of the left ventricle of a mammalian heart showing the anatomy and native mitral valve.

Fig. 2B is a schematic cross-sectional view of the left ventricle of a heart having a prolapsed mitral valve in which the leaflets are insufficiently coaptated and suitable for replacement with various embodiments of a prosthetic heart valve in accordance with the present techniques.

Fig. 3 is a schematic diagram of the top view of the mitral valve in isolation from the surrounding cardiac structures and showing the annulus and native leaflets.

Fig. 4A is a side view of a heart valve prosthesis in a deployed or expanded configuration (e.g., a deployed state) in accordance with embodiments of the present technique.

Fig. 4B is a top view of the heart valve prosthesis of fig. 4A, in accordance with embodiments of the present technique.

FIG. 4C is a top view of a heart valve prosthesis taken along line 4C-4C of FIG. 4A and in accordance with embodiments of the present technique.

Fig. 5A illustrates a cross-sectional view of a heart showing a partial side view of a heart valve prosthesis implanted at a native mitral valve, in accordance with embodiments of the present technique.

Fig. 5B is an enlarged cross-sectional view of the heart valve prosthesis of fig. 5A shown in a deployed configuration (e.g., a deployed state) in accordance with embodiments of the present technique.

Fig. 5C is an enlarged cross-sectional view of a portion of a heart valve prosthesis shown in a deployed configuration (e.g., a deployed state) in accordance with another embodiment of the present technique.

Fig. 6A-6C are side views of various support arm configurations in accordance with additional embodiments of the present technique.

Fig. 7 is a partial side view of a heart valve prosthesis illustrating a plurality of flexible regions on a support arm, in accordance with embodiments of the present technique.

Figures 8A-8H are side views of various support arms that bend in response to a twisting force in accordance with other embodiments of the present technology.

Fig. 9 is an enlarged cross-sectional view of the heart valve prosthesis of fig. 5A-5B shown in a delivery configuration (e.g., a low profile or radially compressed state) in accordance with embodiments of the present technique.

FIG. 10 is a cross-sectional view of a heart illustrating steps in a method of implanting a heart valve prosthesis using a transseptal approach in accordance with another embodiment of the present technique.

Detailed Description

Specific embodiments of the present technology are described below with reference to the drawings, wherein like reference numbers indicate identical or functionally similar elements. The terms "distal" and "proximal" are used in the following description with respect to position or orientation relative to a treating clinician or with respect to a prosthetic heart valve device. For example, "distal" or "distally" is a location that is away from, or in a direction away from, the clinician when referring to a delivery procedure or along the vasculature. Likewise, "proximal" or "proximally" is a position near or in a direction toward the clinician. The terms "proximal" and "distal" with respect to a prosthetic heart valve device may refer to a number of partial positions of the device with respect to the direction of blood flow. For example, proximal end may refer to an upstream location or a blood inflow location, and distal end may refer to a downstream location or a blood outflow location.

The following detailed description is merely exemplary in nature and is not intended to limit the technology or the application and uses of the technology. Although the description of the embodiments of the invention is made in the context of the treatment of heart valves, particularly the mitral valve, the present techniques may also be used in any other body passage where it is deemed useful. Furthermore, there is no intention to be bound by any expressed or implied theory presented in the preceding technical field, background, brief summary or the following detailed description.

Embodiments of the present technology as described herein may be combined in many ways to treat one or more of many valves of the body, including heart valves, such as the mitral valve. Embodiments of the present technology may be therapeutically integrated with many known procedures and procedures, for example, such embodiments may be integrated with known methods of accessing heart valves (e.g., mitral valves with anterograde or retrograde access) and combinations thereof.

Fig. 1 is a schematic cross-sectional view of a mammalian heart 10 depicting four heart chambers (right atrium RA, right ventricle RV, left atrium LA, left ventricle LV) and native valve structures (tricuspid valve TV, mitral valve MV, pulmonary valve PV, aortic valve AV). Fig. 2A is a schematic cross-sectional view of the left ventricle LV of a mammalian heart 10 showing the anatomy and the native mitral valve MV. Referring to both fig. 1 and 2A, the heart 10 includes a left atrium LA that receives oxygenated blood from the lungs via the pulmonary veins. During ventricular diastole, the left atrium LA pumps oxygenated blood through the mitral valve MV and into the left ventricle LV. During systole the left ventricle LV contracts and blood flows outwardly through the aortic valve AV into the aorta and the rest of the body.

In a healthy heart, the leaflets LF of the mitral valve MV meet or "coapt" uniformly at the free edges to close and prevent backflow of blood during contraction of the left ventricle LV (fig. 2A). Referring to fig. 2A, the leaflets LF attach to the surrounding cardiac structure via AN annulus of fibrous connective tissue called the annulus (annuus) AN. The flexible leaflet tissue of the mitral valve leaflets LF is connected to papillary muscles PM that extend upwardly from the inferior wall of the left ventricle LV and the interventricular septum IVS via branch tendons called chordae tendineae CT. In a heart 10 having a prolapsed mitral valve MV with leaflets LF insufficiently coapting or meeting, as shown in fig. 2B, leakage from the left ventricle LV into the left atrium LA will occur. Several structural defects can lead to mitral valve leaflet LF prolapse and regurgitation including chordal tendineae CT rupture, papillary muscle PM damage (e.g., due to ischemic heart disease), and enlargement of the heart and/or mitral annulus AN (e.g., arrhythmia).

Fig. 3 is a top view of the mitral valve MV isolated from the surrounding cardiac structures and further illustrates the shape and relative dimensions of the leaflets LF and annulus AN. As shown, the mitral valve MV typically has a "D" shape or a kidney shape. The mitral valve MV comprises an anterior leaflet AL which, when closed, meets the posterior leaflet PL at the junction line. When the anterior and posterior leaflets AL, PL fail to meet, regurgitation may occur at the commissure of the corners (commissure) C between the leaflets AL, PL or between the leaflets.

An embodiment of a prosthetic heart valve device and associated method in accordance with the present technique is described in this section with reference to fig. 4A-10. It should be understood that the particular features, sub-structures, uses, advantages and/or other aspects of the embodiments described herein, as well as with reference to fig. 4A-10, may be interchanged, substituted or otherwise configured as appropriate in accordance with additional embodiments of the present technology.

The present invention provides systems, devices, and methods suitable for use with a prosthetic heart valve that is percutaneously delivered and implanted in a patient's heart. In some embodiments, methods and devices for treating valve disease by minimally invasive implantation of an artificial or prosthetic heart valve are presented. For example, a prosthetic heart valve device according to the described embodiments of the invention may be implanted to replace a diseased or damaged native mitral valve or a previously implanted prosthetic mitral valve in a patient (e.g., a patient with a prolapsed mitral valve as shown in fig. 2A). In further embodiments, the device is suitable for implantation and replacement of other diseased or damaged heart valves or previously implanted prosthetic heart valves, such as tricuspid, pulmonary, and aortic heart valves.

Fig. 4A is a side view of a heart valve prosthesis or prosthetic heart valve device 100 in a radially expanded or deployed configuration (e.g., a deployed state) in accordance with embodiments of the present technique. Fig. 4B is a top view of the heart valve prosthesis 100 as configured in fig. 4A and 4C. Fig. 4C is a top view of the prosthesis 100 taken along line C-C of fig. 4A. Referring to fig. 4A-4C, a heart valve prosthesis 100 includes a frame or stent-like support structure 110 including a tubular portion or structural valve support structure 120 defining a lumen 121 for retaining, retaining and/or securing a prosthetic valve assembly 130 therein. The valve support structure 120 may be generally cylindrical with a support along the valveLongitudinal axis L of holding structure 120_AAn upstream portion 124 at a first end 125 and a downstream portion 126 at a second end 127 of the orientation (fig. 4A). Frame 110 further includes one or more support arms 140 that extend radially outward from valve support structure 120 and generally in an upstream direction of downstream portion 126 of valve support structure 120 (e.g., to behind the native leaflets of the mitral valve and to engage heart tissue in the subannular region (subannular region) within the left ventricle). At least some of the support arms 140 may have a curvilinear shape 141 that is configured to atraumatically engage the native valve annulus and substantially absorb twisting forces such that the prosthesis 100 is supported by the valve annulus when the prosthetic valve assembly 130 is closed during systole.

In some embodiments, as shown in the radially expanded configuration of fig. 4A, the frame 110 further includes a radially extending segment or portion 150 that at least partially surrounds the valve support structure 120 and extends from the upstream portion 124 of the valve support structure 120. The radially extending section 150 may include a plurality of self-expanding struts 152, the plurality of self-expanding struts 152 configured to radially expand when the prosthesis 100 is deployed to an expanded configuration. In some arrangements, the radially extending section 150 may engage the annulus or tissue above the annulus when implanted within the native mitral valve space. In this embodiment, the radially extending segment 150 can hold the valve support structure 120 in a desired position within the native valve region (e.g., between the native leaflets and the annulus of the mitral valve). Referring to fig. 4B, the radially extending section 150 and/or the valve support structure 120 can include a sealing material 160 that can extend around an upper or upstream surface 154 or a lower or downstream surface 155 (fig. 4A) of the radially extending section 150 and/or around an inner or outer wall 122, 123 of the valve support structure 120 to prevent blood leakage (e.g., paravalvular leakage) between the implanted prosthesis 100 and native heart tissue.

Referring to FIG. 4B, the radially extending segment 150 and the valve support structure 120 are shown having a generally circular cross-sectional shape, wherein the cross-sectional dimension D of the radially extending segment 150₁Is larger than the cross-sectional dimension D of the valve support structure 120₂. In some embodiments, the radially extending section 150, the valve support knotThe construct 120 or both may have other cross-sectional shapes to accommodate a D-shaped or kidney-shaped mitral valve. For example, the radially extending segment 150 and/or the valve support structure 120 may expand into an irregular, non-cylindrical, or elliptical configuration for accommodating a mitral valve or other valve. In addition, native valves (e.g., mitral valves, aortic valves) may have unique sizes and/or have other unique anatomical shapes and features that vary from patient to patient, and the prosthesis 100 for replacing or repairing such valves may be adapted to accommodate the size, geometry, and other anatomical features of such native valves. For example, the radially extending segment 150 may expand within the native heart valve region while being flexible so as to conform in shape to the region to which the radially extending segment 150 is engaged.

Fig. 4A and 4B illustrate a radially extending segment 150 having a plurality of struts 152, the struts 152 extending outwardly from the outer wall 123 at the first end 125 of the valve support structure 120. In one embodiment, struts 152 are relatively evenly arranged around the circumference of valve support structure 120, and each strut 152 connects adjacent struts 152 at crowns 156. In one embodiment, crown 156 has atraumatic tip 157, tip 157 preventing damage to cardiac tissue during deployment and passage through the cardiac cycle. Examples of suitable radially extending segments 150 are described in U.S. patent publication No. 2015/0119982, which is incorporated herein by reference in its entirety.

Referring again to fig. 4A and 4C, a plurality of support arms 140 extend from the downstream portion 126 of the valve support structure 120 and are substantially evenly spaced around the circumference of the outer wall 123 of the valve support structure 120 (fig. 4C). In an alternative arrangement not shown, the support arms 140 may be unevenly spaced about the circumference, grouped, irregularly spaced, etc. In a particular example, the support arms 140 may be grouped closer together and extend from the valve support structure 120 at a location that is approximately aligned with the anterior and posterior leaflets of the mitral valve when deployed. The embodiment shown in fig. 4C has twelve support arms 140 evenly spaced around the circumference of the valve support structure 120. In alternative arrangements, the prosthesis 100 may include less than 12 support arms 140, such as two support arms, two to six support arms, more than six support arms, nine support arms, etc., or more than twelve support arms 140.

Referring to fig. 4A, the support arms 140 can extend from the valve support structure 120 at or near the second end 127, and can be described as extending along the outer wall 123 of the valve support structure 120 generally toward the upstream portion 124 or parallel to the outer wall 123 of the valve support structure 120. As shown, the support arm 140 may have a generally curvilinear shape 141 or similar geometry. Curvilinear shape 141 includes opposing curved or bent regions 142, 144, curved or bent regions 142, 144 being longitudinally separated by an angled elongated or straight region 143 extending therebetween. When positioned for use with a native mitral valve, the curved region 142 of the curved support arm 140 can be referred to as the downstream curved segment 142, and the curved region 144 of the curved support arm 140 can be referred to as the upstream curved segment 144.

In some embodiments, the curvilinear shape 141 includes a first arcuate (e.g., curved) region 142 formed to curve toward the outer wall 123 to engage a portion of at least one leaflet of the native heart valve or other structure in the region of the heart valve, such as chordae tendineae (chordae). In one embodiment, the first curved region 142 may extend around the downstream edge of the native valve leaflet. In the middle portion of the support arm 140, the support arm comprises a straight region 143, which straight region 143 is configured to follow the first arc-shaped region 142 and to slope in a direction towards the outer wall 123 at the middle or central portion 170 of the valve support structure 120. At a free end portion of the support arm 140 proximate the first end 125 of the valve support structure 120, the support arm 140 further includes a second arcuate (e.g., curved) region 144 following the linear or elongated region 143 along the curvilinear shape 141, formed to curve in a direction away from the outer wall 123 of the valve support structure 120 and engage tissue at or near the native heart valve when implanted. In one particular example, the second arcuate region 144 can engage the subannular tissue and/or a portion of a heart chamber wall (e.g., a ventricular wall) without trauma. Referring to fig. 4A, in a particular embodiment, the first arcuate region 142 is longitudinally separated from the second arcuate region 144 by a straight or elongated region 143 to form or define a generally S-shaped profile.

In the embodiment shown in fig. 4A and 4C, the second arcuate region 144 on each support arm 140 provides or defines a contact or landing area 145 configured to engage tissue at or near sub-annulus tissue in a atraumatic manner to inhibit tissue erosion and/or resist movement of the prosthesis 100 in an upstream direction during ventricular systole, as described further below. As shown, second arcuate region 144 includes a widened and/or flat portion 446 that forms landing zone 145. As shown in FIG. 4A, the widened portion 446 has a width W that is greater than the first arcuate region 142 of the support arm 140₂First width W of₁. When the prosthesis 100 is deployed and in contact with tissue (e.g., subannular tissue, native leaflets, ventricular wall, etc.) through the widened portion 446, the landing zone 145 effectively distributes native tissue contact over a greater surface area to inhibit tissue erosion and distribute load stresses on the support arms 140. In the embodiment shown in fig. 4A and 4C, the landing zone 145 includes a groove 447 formed along the widened portion 446, which groove 447 can provide an additional barrier to movement of the landing zone 145 relative to the contacted tissue. In alternative arrangements, the landing zone 145 may include raised portions, tabs, cut-outs, and other features that provide additional resistance to movement of the contacting tissue once deployed. In various arrangements, the support arms 140 provide atraumatic contact in a manner that limits or inhibits tissue erosion and/or abrasion after implantation of the prosthesis 100 by resisting movement of the landing zone 145 against the contacted native tissue. In certain embodiments, and as shown in fig. 4A and 4C, the support arm 140 includes arm tips 148 that may be rounded or otherwise prevented from forming a wound to the cardiac tissue engaged by the arm tips 148 during deployment or when fully implanted. In the illustrated embodiment, the arm tip 148 includes a hole 448 for attaching the support arm 140 to a delivery catheter (not shown) in a radially compressed configuration for delivery to a target site. Additionally or alternatively, one or more of the holes 448 can be filled with a secondary material (e.g., tantalum, platinum, gold) to enhance fluoroscopyGuiding visibility during delivery. In alternative arrangements, the support arm 140 may not include the holes 448 and/or other landing zone features (e.g., the grooves 447) without departing from the scope of the present invention.

In some embodiments described herein, to transition or self-expand between an initial compressed configuration (e.g., in a delivery state, not shown) and a deployed configuration (fig. 4A), the frame 110 is formed from a resilient or shape memory material, such as a nickel-titanium alloy (e.g., nitinol), that has a mechanical memory to return to the deployed or expanded configuration. In one embodiment, the frame 110 may be a unitary structure defining the prosthesis 100, the valve support structure 120, and the radially extending segments 150 at the inflow portion of the plurality of support arms 140, and the frame 110 as described may be made of stainless steel, pseudo-elastic metal such as nitinol or nitinol, or so-called super-alloys. In some arrangements, the frame 110 may be formed as a unitary structure, for example, from a laser cut, windowed nitinol or other metal tube. Mechanical memory may be imparted to the structure forming the frame 110 by heat treatment to achieve spring tempering in stainless steel, for example, or to set shape memory in a sensitive metal alloy (e.g., nitinol). The frame 110 may also comprise a polymer or a combination of metals, polymers, or other materials.

In one embodiment, the frame 110 may be a flexible metal frame or support structure having a plurality of ribs and/or struts (e.g., struts 128, 152) geometrically arranged to provide a lattice structure that can be radially compressed (e.g., in a delivery state, not shown) for delivery to a target native valve site and radially expanded (e.g., to a radially expanded configuration shown in fig. 4A) for deployment and implantation at the target native valve site. Referring to the valve support structure 120 as shown in fig. 4A, the ribs and struts 128 may be arranged in a plurality of geometric patterns that can expand or bend and contract while providing sufficient elasticity and strength to maintain the integrity of the prosthetic valve assembly 130 encapsulated therein. For example, the strut 128 may surround the longitudinal axis L_AArranged in a circumferential pattern comprising a series of diamonds, saw-teeth, sinusoids, or other geometric shapesAnd (4) shape.

In other embodiments, the frame 110 may comprise separately manufactured components that are butted, connected, welded, or otherwise mechanically connected to one another to form the frame 110. For example, the radially extending section 150 may dock to the upstream portion 124 of the valve support structure (e.g., at attachment points 129a on the struts 128 defined by the diamond-shaped geometry of the valve support structure 120). Likewise, support arm 140 may be coupled to downstream portion 126 of valve support structure 120 (e.g., at attachment point 129b on strut 128 defined by the diamond-shaped geometry of valve support structure 120). Other arrangements and attachment points are contemplated for interfacing one or more support arms 140 and radially extending segments 150 to the valve support structure 120. In a particular embodiment, as shown in fig. 4A, the support arm 140 can be docked to the valve support structure 120 via an arm post 146. In one embodiment, the arm post 146 may be integral with the frame 110 such that the arm post 146 is an extension of one or more of the struts 128. In another embodiment, the arm posts 146 and the valve support structure 120 may be joined by various methods known in the art, such as welding (welding), bonding (bonding), rivets or other fasteners, mechanical interlocking, or any combination thereof. In one embodiment, the valve support structure 120 can be a balloon-expandable tubular metal stent, and the radially extending segments 150 and support arms 140 of the frame 110 can be formed of materials and methods so as to be self-expanding as described above. In another embodiment related thereto, the support arms 140 may extend from or interface to the middle or central portion 170 of the valve support structure 120 without departing from the scope of the invention.

Referring to fig. 4B-4C, a prosthetic valve assembly 130 can be docked to the inner wall 122 of the valve support structure 120 for controlling blood flow through the heart valve prosthesis 100. For example, the prosthetic valve component 130 can include a plurality of leaflets 132 (shown individually at 132 a-b) that engage and are configured to allow blood to flow through the prosthesis 100 in a downstream direction (e.g., from the first end 125 to the second end 127) and inhibit blood from flowing in an upstream direction (e.g., from the second end 127 to the first end 125). Go toThe vessel prosthetic valve assembly 130 is shown with a mitral valve arrangement, but it should be understood that the prosthetic valve assembly 130 can have three leaflets 132 (tricuspid valve arrangement, not shown) or more than three leaflets 132 for coaptation to close the prosthetic valve assembly 130. In one embodiment, the leaflets 132 may be mounted to the inner wall 122 of the valve support structure 120 from bovine pericardium (or other natural material) (e.g., obtained from human or animal heart valves, aortic root, aortic wall, aortic leaflets, pericardial tissue, such as pericardial patches, bypass grafts, blood vessels, intestinal submucosal tissue, umbilical cord tissue, etc.). In another embodiment, synthetic materials suitable for use as leaflets 132 include:polyester (commercially available from inslot north america, wilmington, telawa), other cloth materials, nylon blends, polymeric materials, and vacuum deposited nitinol solder materials. In yet another embodiment, the leaflets 132 can be made of an ultra-high molecular weight polyethylene material commercially available from imperial, netherlands under the trade name DYNEEMA. For certain leaflet materials, it may be desirable to coat one or both sides of the leaflet with a material that prevents or minimizes overgrowth. It may further be desirable that the leaflet material be durable and not affected by stretching, deformation, or fatigue.

Fig. 5A is a schematic diagram illustrating a partial side view of a prosthesis 100 implanted in the native mitral valve region of the heart 10, in accordance with embodiments of the present technique. The prosthesis 100 shown in fig. 5A, has only two support arms 140 for illustrative purposes only. It will be appreciated that the prosthesis 100 may have more than two support arms 140, such as more than six support arms, and so forth, in some arrangements. Generally, when implanted, the upstream portion 124 of the valve support structure 120 is oriented to receive an inflow of blood from a first heart chamber (e.g., the left atrium LA for mitral valve MV replacement, the left ventricle for aortic valve replacement, etc.), and the downstream portion 126 is oriented to release an outflow of blood to a second heart chamber or structure (e.g., the left ventricle LV for mitral valve MV replacement, the aorta for aortic valve replacement, etc.).

In operation, the heart valve prosthesis 100 can be delivered intravascularly in a radially compressed configuration (not shown) and within a delivery catheter (not shown) to a desired native valve region of the heart 10, such as near the mitral valve MV. Referring to fig. 5A, the prosthesis 100 can be advanced to a position within or downstream of the native mitral annulus AN, wherein the support arms 140 and downstream portion 126 of the valve support structure 120 are released from the delivery catheter. The delivery catheter may then release the upstream portion 124 and the radially extending section 150 of the valve support structure 120 at a location within or upstream of the native mitral valve MV so as to expand toward the radially expanded configuration and engage native tissue in the native heart valve area. Once released from the delivery catheter, the prosthesis 100 may be positioned such that the radially extending segments 150 reside within the left atrium and engage tissue at or near the upper ring region. The prosthesis 100 is further positioned such that the support arms 140 engage the outward facing surface of the native leaflet LF to capture the leaflet between the support arms 140 and the outer wall 123 of the valve support structure 120. As further described herein, the contact or landing zone 145 of each support arm 140 is configured to engage tissue at or near the subannular tissue so as to resist movement of the prosthesis 100 in the upstream direction during ventricular systole.

Fig. 5B is an enlarged cross-sectional view of the heart valve prosthesis 100 of fig. 5A shown in a radially expanded configuration (e.g., a deployed state) and in accordance with embodiments of the present technique. In fig. 5B, the prosthesis 100 is schematically shown at the mitral valve MV on the right side of the illustration. When deployed and implanted, the heart valve prosthesis 100 is configured to position the prosthetic valve assembly 130, which is retained or retained within the valve support structure 120, at a desired location and orientation within the native mitral valve MV. Referring to fig. 5A and 5B concurrently, several features of the prosthesis 100 provide resistance to movement of the prosthesis 100, promote tissue ingrowth, minimize or prevent paravalvular leakage, and/or minimize natural tissue erosion when implanted in a radially expanded configuration. For example, radially extending segment 150 may be positioned to expand within the atrial space above the mitral valve and engage cardiac tissue within the atrial space. In particular, at least the lower surface or apex 153 of the arcuate or S-shaped struts 152 may provide a tissue engagement region for contacting the upper ring tissue, e.g., to provide a seal against paravalvular leakage and inhibit downstream migration of the prosthesis 100 relative to the native annulus.

In some embodiments, the upwardly directed lip portions 158 of the struts 152 rising to form the crowns 156 can provide further tissue contact areas that can further inhibit downstream movement of the prosthesis 100 relative to the native valve annulus and inhibit wobble or side-to-side rotation of the prosthesis 100 within the native valve during the cardiac cycle, thereby inhibiting paravalvular leakage and ensuring alignment (alignment) of the prosthetic valve assembly 130 within the native valve annulus. In other embodiments, the radially extending segment 150 may be a flange, rim, ring, finger-like protrusion, or other tissue that protrudes into the atrial space to at least partially engage at or above its upper annulus region.

Referring to fig. 5A and 5B simultaneously, support arm 140 is shown having a curvilinear shape 141 and extending from downstream portion 126 of valve support structure 120. The support arms 140 are configured to engage a subannular region of the mitral valve MV within the native leaflets (if present) and/or ventricular space. In one embodiment, support arms 140 are configured to engage the outer surface of the leaflets (e.g., facing toward the ventricular side) such that the native leaflets are captured between support arms 140 and outer wall 123 of valve support structure 120. In one such embodiment, the preformed curvilinear shape 141 of the support arm 140 (e.g., at the transition tip 144a of the second arcuate region 144) may be biased toward the outer wall 123 of the valve support structure 120 such that the compressive force F is_C1The leaflets LF are pressed against the outer wall 123 of the valve support structure 120 in a manner that clamps, grasps, curls, or otherwise traps the leaflets within the space 105 between the support arms 140 and the outer wall 123 of the valve support structure 120.

To further inhibit upstream migration of the prosthesis 100 relative to the native valve annulus AN, the second arcuate region 144 is configured to engage a sub-annulus region (e.g., behind the leaflet LF) via a contact surface or landing zone 145. In further embodiments, the second curved region 144 may contact tissue underlying the annulus AN, such as a ventricular wall (as shown in fig. 5C). By passing through the tissue below the contact sub-ring region (fig. 5A and 5B) and/or annulus AN (fig. 5C) via, for example, the widened portion 446 (fig. 4A and 4C) extending to the arm tip 148, the landing zone 145 distributes surface contact over a larger area to inhibit tissue erosion and distribute load stresses on the support arm 140 in AN atraumatic manner.

In various arrangements, the curvilinear shape 141 of the support arm 140 may form a generally S-shaped profile. In some arrangements, the support arms 140 can be more flexible (e.g., than other portions of the frame 110) and/or made of a resilient material (e.g., a shape memory material, a superelastic material, etc.) that can absorb forces exerted on the support arms 140 when implanted in the heart 10 and during a cardiac cycle. For example, these forces may cause the substantially S-shaped profile to temporarily deform, deflect, or otherwise change shape. Similarly, the curvilinear shape 141 of the support arm may provide a compressive force F in an upstream direction (e.g., at contact region 145) and against the valve annulus tissue_C2. In one embodiment, the tip 153 (e.g., lower surface) of the radially extending segment 150 may be longitudinally separated from the landing zone 145 of the second arcuate region by a gap 106. When implanted, the gap 106 may be sized to receive annulus tissue therein. In one embodiment, the top end 153 of the arcuate strut 152 may be disposed across the gap 106 and the compressive force F_C2Providing a downward compressive force F on opposing contacting tissues_C3. Thus, a compressive force F_C2And F_C3May conform to each other (aligned) and/or oppose each other such that the annulus tissue is captured between the radially extending segment 150 and the support arm 140 having the pre-formed curvilinear shape 141. In some embodiments, the strut 152 may be circumferentially and radially aligned with the second arc region 144 of the support arm 140 such that the compressive force F_C1With a compressive force F_C3(as shown in fig. 5B) in direct opposition to effectively clamp the annulus AN therebetween.

In some embodiments, portions of the prosthesis 100, such as the radially extending section 150, the valve support structure 120, and/or the support arms 140, may be provided with a sealing material 160 (fig. 4B) to cover at least a portion of the prosthesis 100. The sealing material 160 may prevent paravalvular leakage and provide a medium for tissue ingrowth after implantation, which may further provide the desirability of the prosthesis 100 in the native heart valve areaBiomechanical retention (biomechanical retention) in the deployed position. In some embodiments, the sealing material 160 or portions thereof may be a low porosity woven fabric, such as polyester,Polyester, or Polytetrafluoroethylene (PTFE), that when attached to the frame 110 creates a one-way fluid channel. In one embodiment, the sealing material 160 or portions thereof may be a more loosely knit or woven fabric, such as a polyester or PTFE braid, which may be used when it is desired to provide a medium for tissue ingrowth, as well as the ability of the fabric to stretch to conform to a curved surface. In another embodiment, a polyester velour fabric may be substituted for at least part of the sealing material 160, for example when it is desired to provide a tissue ingrowth medium for one side and a smooth surface for the other. For example, these and other suitable cardiovascular fabrics are commercially available from Bard Peripheral Vascular, inc. In another embodiment, the sealing material 160 or portions thereof may be a natural graft material, such as pericardium or another membranous tissue.

Fig. 6A-6C are side views of various support arm configurations in accordance with additional embodiments of the present technology. Referring also to fig. 6A-6C, in one embodiment, the support arm 140 may generally have a curvilinear shape 141 with first and second curved regions 142, 144, the first and second curved regions 142, 144 separated by an elongated or substantially linear region 143 that together extend substantially parallel to the longitudinal axis 601 (e.g., substantially parallel to the longitudinal axis L of the valve support structure 120)_aAligning; fig. 5B). In some embodiments, the support arm 140 has an S-shaped profile. As shown in FIGS. 6A-6C, the first curved region 142 may have a first radius of curvature R₁The second arcuate region 144 may have a second radius of curvature R₂In some embodiments, the second radius of curvature R₂(a) Is substantially equal to the first radius of curvature R₁(FIG. 6A), (b) is much smaller than the first radius of curvature R₁(FIG. 6B), or (c) substantially larger than the first radius of curvature R₁(FIG. 6C).

Referring to fig. 5B and 6A-6C concurrently, the second arcuate region 144 may have a tissue engaging portion or contact region 145 for engaging a sub-ring or other cardiac tissue during and/or after deployment. In the embodiment shown in fig. 6A-6C, the support arm 140 includes an arm post 146 at the first end 140a, and the first arcuate region 142 is generally from the longitudinal axis L_A601 extend in an outward direction and are radially aligned with a downstream portion of the valve support structure 120 (fig. 5B). The first arc-shaped region 142 surrounds a first center of curvature C_C1And (4) bending. As shown in fig. 6A, a generally straight or elongated portion 143 extends between first arcuate region 142 and second arcuate region 144. The second arcuate region 144 is radially aligned with a middle or central portion 170 of the valve support structure 120 between the upstream and downstream portions 124, 126 (fig. 5B). In one embodiment, the second arcuate region 144 surrounds a second center of curvature C_C2And (4) bending. In the embodiment shown in fig. 5B and 6A-6C, the first center of curvature C is passed_C1The first axis (not shown) is drawn parallel to the second center of curvature C_C2A second axis is drawn (not shown). The first and second axes are substantially perpendicular to the longitudinal axis L_A601 (fig. 6A).

Referring to fig. 6A, in some embodiments, the arm post 146 may be substantially linear and have a suitable length L₁For extending the first curved region 142 downstream from the connector (not shown) to a desired distance of the valve support structure 120. In some embodiments, the arm posts 146 may be substantially parallel to the longitudinal axis L of the prosthesis 100 and/or the valve support structure 120 (as shown in fig. 5B)_A. Following the general curvature of the first arcuate region 142 shown in fig. 6A, the first curved segment 610 of the region 142 extends radially outward from the arm post 146. More specifically, the first curved segment 610 may be described as curved or generally curved in an outward and downstream direction until it reaches the transition tip 142a of the first curved region 142. Thereafter, the second curved segment 614 of the first arced region 142 continues the curved profile and extends in an outward and generally upstream direction from the transition tip 142 a.

As shown in FIG. 6A, the first transition point 616 begins at the support arm 140An elongated region 143, wherein the elongated region 143 is accompanied by a longitudinal axis L of the valve support structure 120_AIs inclined and extends in an upward and inward direction to end at a second transition point 618. In a similar manner, the general curvature of the second arcuate region 144 begins at a second transition point 618 such that, after the curvature of the second arcuate region 144, a third curved segment 620 is defined, the third curved segment 620 generally curving in an outward and upstream direction to reach the transition apex 144a of the second arcuate region 144. The fourth curved segment 622 of the second arcuate region 144 continues the curved profile and extends in an outward direction (e.g., relative to the longitudinal axis L) from the transition tip 144a_A) And may also curve slightly downstream toward the free end or arm tip 148. An opening 624 between the second arc-shaped region 144 and the first arc-shaped region 142 of the support arm 140 is generally formed in the space between the third transition 618 and the first end 140a of the support arm 140, and may be configured to receive the native leaflet LF and/or chordae tendineae therein. Other embodiments of the support arm 140 may have curved segments 610, 614, 620, and 622 of lesser or greater curvature. In addition, the support arms 140 of the embodiment shown in fig. 5B and 6A-6C can have a height H that is less than the valve support structure 120 (fig. 5B and 6A)₂Total height H of₁. Other arrangements and heights are also contemplated. Thus, except for the radius of curvature R of the first and second arcuate regions 142, 144₁、R₂And/or other geometric features/changes, the overall height H of the support arm 140₁May be selected to conform to the anatomy at the desired target location of the heart valve.

Referring to fig. 6A, the first and second arc regions 142, 144 of the support arm 140 may be configured to absorb, translate, and/or mitigate torsional forces present within the heart during, for example, systole and diastole. In certain arrangements, the support arm 140 has a spring-type response to a twisting force (e.g., a physical force that can be exerted on the support arm 140 and alter the profile of the support arm 140). As described in more detail herein, the support arm 140 may have multiple hinge points for bending or absorbing such twisting forces. For example, as a result of the spring-type response of the single support arm 140, the first torsional force may be absorbed in a manner that elastically or reversibly and temporarily distorts the unbiased configuration (unbiased configuration) of the support arm 140. As the first torsional force dissipates (e.g., during a cardiac cycle), the spring-like motion continues the transition of the support arm profile from the twisted position back to the unbiased configuration. Thus, the spring-like response of the support arm 140 occurs in a manner opposite the first torsion force. In these arrangements, the degree to which the support arm 140 is compressed and/or extended is proportional to the twisting force exerted on the support arm. The support arm 140 can have a selected stiffness that provides a constant for the distance or increment of twist (e.g., compression, expansion). In some arrangements, the support arm 140 may have a constant stiffness along the entire length of the support arm and covering all of the multiple hinge points. In other arrangements, the support arm 140 may have a variable stiffness along the length of the support arm and contain different hinge points. This stiffness selectivity of the individual support arms 140 can provide a prosthetic design to accommodate unique and variable natural structures, for example, for accommodating variable twisting forces exerted by the natural mitral valve region. Variable stiffness can be achieved in a number of ways: i) the difference in cross-sectional area of the support arms, ii) variable cold working of the selected support arms in the case of conventional elastoplastic metals (e.g., stainless steel, titanium alloys, cobalt-chromium alloys), and/or iii) selective heating or a provided heat treatment of one or more support arms but not others.

In particular embodiments, the shape and/or size of the first and second curved regions 142, 144 can be selected to accommodate forces, such as radial compressive forces Fa, longitudinal relaxation forces Fd and contraction forces Fs, hoop stresses, etc., exerted by the native annulus and/or leaflets. The absorption of the twisting forces may serve to prevent those forces from being translated to the valve support structure 120 and thereby maintain engagement of the prosthetic valve assembly 130. Additionally, as further shown in FIG. 7, absorption of twisting forces along the entire support arm 140 and/or at several hinge points or locations 701 (e.g., the transitions 140a, 142a, 616, 618, and 144a) distributes the force-induced stresses, thereby substantially preventing fatigue of the support arm 140 and/or minimizing tissue erosion at the contact portions of the natural anatomy. In accordance with the present techniques, the support arms 140 can flex, bend, rotate, or twist under a twisting force while the valve support structure 120 substantially retains its rigid and/or original shape (e.g., substantially circular).

Fig. 8A-8H are side views of various support arms 140 that bend in response to a twisting force in accordance with other embodiments of the present technology. The degree of flexibility of a single support arm 140 may be consistent between all support arms 140 of the prosthesis 100, or alternatively, some support arms 140 may be more flexible than other support arms 140 on the same prosthesis 100. Similarly, the degree of flexibility of a single support arm 140 is consistent throughout the entire length of the support arm 140 or is consistent over the curvature of the first and second arcuate regions 142, 144. However, in other embodiments, the degree of flexibility may vary along the length and/or shape of each support arm 140.

As shown in fig. 8A-8H, the first and second arcuate regions 142, 144 of the support arm 140 may be curved relative to the arm post 146, the valve support structure 120 (shown in phantom), and/or configured to change their arcuate shape in response to varying twisting forces F that may be applied by surrounding tissue during or after implantation of the prosthesis 100. From the resting position (fig. 8A), the first arcuate region 142 is responsive to a downward force F caused by, for example, a cord load (e.g., from a tendon engaging the first arcuate region 142)₁Can be bent down to shape/position 842B (fig. 8B). In another embodiment, the second arced region 144 may curve downward and the first arced region 142 may compress from the resting position (fig. 8A) to shapes/positions 844C and 842C (fig. 8C), respectively, in response to a downward force F caused by, for example, tip load (e.g., from left ventricular pressure)₂. Similarly, the first and second curved regions 142, 144 are responsive to laterally directed inward forces F caused by, for example, ventricular wall loading (e.g., left ventricular contraction)_3a、F_3bCan be bent or compressed inward to a shape/position 842D, 844D (fig. 8D). Generating a force F₄Can cause the second arcuate region 144 to flex inwardly and compress to the shape/position 844e, which can also facilitate the change of position in the first arcuate region to position 842E (fig. 8E). In some embodiments, the first and second arced regions 142 and 144 are responsive to a transverse direction force F_3a、F_3b、F₄Or in response to a force F in a substantially vertical direction₁、F₂And bends downward, rotates inward/outward, and/or deforms.

In other arrangements, as shown in fig. 8F-8H, the first and second arced regions 142, 144 shown in a static position in fig. 8F may also respond to the transversely-oriented force F by bending at one or more of the transitions 140a, 142a, 616, 618, and 144a (fig. 6A)₅Laterally bent and/or rotated, for example, to positions 842G/844G (FIG. 8G) or 842H/844H (FIG. 8H), for example, at independent and variable angles from midline 802 such that arm tips 148 may spread apart from one another.

Fig. 9 is an enlarged cross-sectional view of the heart valve prosthesis 100 of fig. 5A-5B shown in a compressed delivery configuration (e.g., a low-profile or radially compressed state) configured in accordance with embodiments of the present technique. The prosthesis 100 may be configured for delivery within a delivery catheter sheath (not shown) in a radially compressed configuration as shown in fig. 9. More specifically, in the radially compressed configuration, the radially extending section 150 may be elongated, folded, or otherwise arranged to extend longitudinally from the valve support structure 120 in a substantially straightened state. Additionally, the plurality of support arms 140 extend longitudinally and are arranged in a substantially straightened state for percutaneous delivery to the target native heart valve. As shown in fig. 9, the support arm 140 can extend beyond the second end 127 of the valve support structure 120 such that the first arcuate region 142 is substantially linear and aligned with the longitudinal axis L_ASubstantially parallel, while the second arcuate region 144 maintains a curved profile. Once the radial constraint is released, the support arms 140 can be moved to the outwardly biased position as the delivery catheter sheath (not shown) is withdrawn and the radially extending segments 150 can self-expand to the radially expanded configuration (fig. 5B). Further, in the event that the heart valve prosthesis 100 requires repositioning, removal, and/or replacement after implantation, the radially extending segment 150 and the valve support structure 120 can be transitioned from a radially expanded configuration (e.g., the deployed state) (fig. 5B) back to a radially collapsed configuration (fig. 5B) using a catheter device or other lateral retaining sheath9)。

Access to the mitral valve or other atrioventricular valve may be accomplished percutaneously through the patient's vasculature. Depending on the point of vascular access, the approach of the mitral valve may be antegrade and may rely on crossing the interatrial septum into the left atrium. Alternatively, the mitral valve approach into the left ventricle through the aortic valve or transapical puncture may be retrograde. Once percutaneous access is achieved, the interventional tool and support catheter may be advanced intravascularly to the heart and positioned in various ways near the targeted heart valve. For example, the heart valve prosthesis 100 may be delivered to the area of the native mitral valve to repair or replace the native valve by a transseptal approach (as shown in fig. 10), by an aortic valve, or a retrograde approach via transapical puncture. Suitable transapical and/or transarterial implantation procedures for heart valve prosthesis 100 described herein are disclosed in U.S. application No. 13/572,842 filed on 13/8/2012 of Igor Kovalsky, U.S. application publication No. 2011/0208297 to Tuval et al, and U.S. application publication No. 2012/0035722 to Tuval et al, which are hereby incorporated by reference in their entirety.

Fig. 10 is a cross-sectional view of a heart 10 illustrating steps in a method of implanting a heart valve prosthesis 100 using a transseptal approach in accordance with another embodiment of the present technique. Referring to fig. 5A, 9 and 10 concurrently, the prosthesis 100 may be advanced into the delivery catheter 20 adjacent the mitral valve MV. Alternatively, a guidewire (not shown) may be used over which the delivery catheter 20 may be slidably advanced. As shown in fig. 10, the sheath 22 of the delivery catheter 20, which contains the prosthesis 100 in a radially compressed configuration (shown in fig. 9), is advanced through the mitral annulus AN between the native leaflets LF. Referring to fig. 10, sheath 22 is then retracted proximally, allowing prosthesis 100 to expand such that support arms 140 are in an outward position and longitudinal axis L_ASpatially separate and while the valve support structure 120 remains radially contracted. During this deployment phase, the shape-memory bias (shape-memory bias) of the first curved region 142 can facilitate outward movement of the support arms 140. In this transition stage, the first arcuate region 142 may have a radius of curvature greater than the first radius of curvature R₁Third song of (2)Radius of curvature R₃While the second arcuate region 144 continues to retain the second radius of curvature R₂. The second arcuate region 144 provides atraumatic engagement of the heart tissue (as shown in fig. 10) during all stages of deployment within the mitral valve MV (as shown in fig. 10). For example, the second arcuate region 144 is configured to deflect in response to contact with the chordae tendineae CT when transitioning between the radially contracted configuration and the radially expanded configuration. The second curved region 144 may also atraumatically engage the wall of the left ventricle LV as the support arm 140 moves or swings behind the native leaflet LF during deployment. When the support arm 140 is fully deployed (e.g., fig. 5A), the support arm 140 is disposed relative to the longitudinal axis L_AFurther inwardly positioned and such that the leaflets LF engage between the support arms 140 and the valve support structure 120. The sheath 22 can be further retracted to release the valve support structure 120 and the radially extending segment 150 (e.g., within the space of the left atrium LA).

After the sheath 22 has been removed and the prosthesis 100 is allowed to return to its deployed state, the delivery catheter 20 may still be connected to the prosthesis 100 (e.g., a system eyelet, not shown, is connected to the prosthesis eyelet) so that the operator may further control the deployment of the prosthesis 100 as the prosthesis 100 expands toward the radially-expanded configuration. For example, the prosthesis 100 may be expanded upstream or downstream of the target site and then pushed downstream or upstream, respectively, to the desired target site prior to releasing the prosthesis 100 from the delivery catheter 20. Once the prosthesis 100 is positioned at the target site, the delivery catheter 20 may be retracted in a proximal direction and disengaged from the prosthesis 100 when the prosthesis 100 is in a radially expanded configuration at the target native valve (e.g., mitral valve MV).

While various embodiments have been described above, it should be understood that they have been presented by way of illustration and example only of the technology, and not limitation. It will be apparent to persons skilled in the relevant art that various changes in form and detail can be made therein without departing from the spirit and scope of the technology. Thus, the breadth and scope of the present technology should not be limited by any of the above-described embodiments, but should be defined only in accordance with the following claims appended hereto and their equivalents. It should also be understood that each feature of each embodiment discussed herein and of each reference cited herein may be used in combination with the features of any other embodiment. All patents and publications discussed herein are incorporated by reference in their entirety.