Patent Application
20190365538
Not Applicable
The invention relates to devices, systems and features for mitigating paravalvular leak and optimizing functional efficiency of the prosthetic heart valve, including prosthetic mitral valve implant and prosthetic tricuspid valve implant. More specifically, mitigation of paravalvular leakage for a prosthetic mitral valve implant is provided.
The human heart comprises four chambers and four heart valves that assist in the forward (antegrade) flow of blood through the heart. The chambers include the left atrium, left ventricle, right atrium and right ventricle. The four heart valves include the mitral valve, the tricuspid valve, the aortic valve and the pulmonary valve. See generally
The mitral valve is located between the left atrium and left ventricle and helps control the flow of blood from the left atrium to the left ventricle by acting as a one-way valve to prevent backflow into the left atrium. Similarly, the tricuspid valve is located between the right atrium and the right ventricle, while the aortic valve and the pulmonary valve are semilunar valves located in arteries flowing blood away from the heart. The valves are all one-way valves, with leaflets that open to allow forward (antegrade) blood flow. The normally functioning valve leaflets close under the pressure exerted by reverse blood to prevent backflow (retrograde) of the blood into the chamber it just flowed out of. For example, the mitral valve when working properly provides a one-way valving between the left atrium and the left ventricle, opening to allow antegrade flow from the left atrium to the left ventricle and closing to prevent retrograde flow from the left ventricle into the left atrium. This retrograde flow, when present, is known as mitral regurgitation or mitral valve regurgitation.
Native heart valves may be, or become, dysfunctional for a variety of reasons and/or conditions including but not limited to disease, trauma, congenital malformations, and aging. These types of conditions may cause the valve structure to fail to close properly resulting in regurgitant retrograde flow of blood from the left ventricle to the left atrium in the case of a mitral valve failure.
Mitral valve regurgitation is a specific problem resulting from a dysfunctional mitral valve that allows at least some retrograde blood flow back into the left atrium from the right atrium. In some cases, the dysfunction results from mitral valve leaflet(s) that prolapse up into the left atrial chamber, i.e., above the upper surface of the annulus instead of connecting or coapting to block retrograde flow. This backflow of blood places a burden on the left ventricle with a volume load that may lead to a series of left ventricular compensatory adaptations and adjustments, including remodeling of the ventricular chamber size and shape, that vary considerably during the prolonged clinical course of mitral regurgitation.
Regurgitation can be a problem with native heart valves generally, including tricuspid, aortic and pulmonary valves as well as mitral valves.
Native heart valves generally, e.g., mitral valves, therefore, may require functional repair and/or assistance, including a partial or complete replacement. Such intervention may take several forms including open heart surgery and open heart implantation of a replacement heart valve. See e.g., U.S. Pat. No. 4,106,129 (Carpentier), for a procedure that is highly invasive, fraught with patient risks, and requiring not only an extended hospitalization but also a highly painful recovery period.
Less invasive methods and devices for replacing a dysfunctional heart valve are also known and involve percutaneous access and catheter-facilitated delivery of the replacement valve. Most of these solutions involve a replacement heart valve attached to a structural support such as a stent, commonly known in the art, or other form of wire network designed to expand upon release from a delivery catheter. See, e.g., U.S. Pat. No. 3,657,744 (Ersek); U.S. Pat. No. 5,411,552 (Andersen). The self-expansion variants of the supporting stent assist in positioning the valve, and holding the expanded device in position, within the subject heart chamber or vessel. This self-expanded form also presents problems when, as is often the case, the device is not properly positioned in the first positioning attempt and, therefore, must be recaptured and positionally adjusted. This recapturing process in the case of a fully, or even partially, expanded device requires re-collapsing the device to a point that allows the operator to retract the collapsed device back into a delivery sheath or catheter, adjust the inbound position for the device and then re-expand to the proper position by redeploying the positionally-adjusted device distally out of the delivery sheath or catheter. Collapsing the already expanded device is difficult because the expanded stent or wire network is generally designed to achieve the expanded state which also resists contractive or collapsing forces.
Besides the open heart surgical approach discussed above, gaining access to the valve of interest is achieved percutaneously via one of at least the following known access routes: transapical; transfemoral; transatrial; and transseptal delivery techniques.
Generally, the art is focused on systems and methods that, using one of the above-described known access routes, allow a partial delivery of the collapsed valve device, wherein one end of the device is released from a delivery sheath or catheter and expanded for an initial positioning followed by full release and expansion when proper positioning is achieved. See, e.g., U.S. Pat. No. 8,852,271 (Murray, III); U.S. Pat. No.8,747,459 (Nguyen); U.S. Pat. No.8,814,931 (Wang); U.S. Pat. No. 9,402,720 (Richter); U.S. Pat. No. 8,986,372 (Murray, III); and U.S. Pat. No. 9,277,991 (Salahieh); and U.S. Pat. Pub. Nos. 2015/0272731 (Racchini); and 2016/0235531 (Ciobanu).
In addition, all known prosthetic heart valves are intended for full replacement of the native heart valve. Therefore, these replacement heart valves, and/or anchoring or tethering structures, physically extend out of the left atrial chamber, in the case of mitral valves, and engage the inner annulus and/or valve leaflets, in many cases pinning the native leaflets against the walls of the inner annulus, thereby permanently eliminating all remaining functionality of the native valve and making the patient completely reliant on the replacement valve. In other cases, the anchoring structures extend into the left ventricle and may anchor into the left ventricle wall tissue and/or the sub-annular surface at the top of the left ventricle. Others may comprise a presence in, or engagement with, a pulmonary artery.
Obviously, there will be cases when native valve has lost virtually complete functionality before the interventional implantation procedure. In this case the preferred solution will comprise an implant that does not extent outside of, e.g., the left atrium, and that functions to completely replace the native valve function. However, in many other cases, the native valve remains functional to an extent and may, or may not, continue to lose functionality after the implantation procedure. A preferred solution in this case comprises delivery and implantation of a valve device that will function both as a supplemental or augmentation valve without damaging the native leaflets in order to retain native valve leaflet functionality as long as present, while also being fully capable of replacing the native function of a valve that slowly loses most or all of its functionality post-implantation of the prosthetic valve.
Further, as seen in
Finally, known prosthetic cardiac valves consist of two or three leaflets that are arranged to act as a one-way valve, permitting fluid flow therethrough in the antegrade direction while preventing retrograde flow. The native mitral valve is located retrosternally at the fourth costal cartilage, consisting of an anterior and posterior leaflet, chordae tendinae, papillary muscles, ventricular wall and annulus connected to the atria. Each native leaflet is supported by chordae tendinae that are attached to papillary muscles which become taut with each ventricular contraction preserving valvular competence. Both the anterior and posterior leaflets of the native valve are attached via primary, secondary and tertiary chordae to both the antero-lateral and posterio-medial papillary muscles. A disruption in either papillary muscle in the setting of myocardial injury, can result in dysfunction of either the anterior or posterior leaflet of the mitral valve. Other mechanisms may result in failure of one, or both of the native mitral leaflets. In the case of a single mitral valve leaflet failure, the regurgitation may take the form of a non-central, eccentric jet of blood back into the left atrium. Other leaflet failures may comprise a more centralized regurgitation jet. Known prosthetic valve replacements generally comprise leaflets which are arranged to mimic the native valve structure, which may over time become susceptible to similar regurgitation outcomes.
Known implantable prosthetic valves may be improved upon by employing structures that may extend the functionality of native valve leaflets in a supplement first, replace when required structure as described herein. It would be highly advantageous in this regard to provide a structure that only engages prolapsing native leaflets at a point of coaptation, thus preventing prolapse.
Certain inventive embodiments described herein are readily applicable to single or two chamber solutions, unless otherwise indicated. Moreover, certain embodiments discussed herein may be applied to preservation and/or replacement of native valve functionality generally, with improved native leaflet coaptation and/or prolapsing, and are not, therefore, limited to the mitral valve and may be extended to include devices and methods for treating the tricuspid valve, the aortic valve and/or pulmonary valves.
Various embodiments of the several inventions disclosed herein address these, inter alia, issues.
Generally, various embodiments of the present invention are directed to devices and methods for creating optimal apposition of a support structure or stent of a prosthetic heart valve to treat cardiac mitral or tricuspid valve regurgitation, mitigating paravalvular leak and optimizing functional efficiency of the prosthetic heart valve.
The support structure (i.e. stent) has multiple features that function to aid with the treatment of cardiac valve regurgitation (mitral or tricuspid). These functions include its function as a scaffold for the functioning prosthetic valve leaflets of the current invention, apposition to the atrial anatomy, optimized radial force for compliance with atrial distension, ability to load and deploy from a minimally invasive delivery system, and geometry to support with mitigating against paravalvular leak (PVL). The design features of the stent are adapted to meet one or more of the functions identified above. Specific design features and attributes for the stents are discussed in detail below.
The stent design concepts are intended to support minimally invasive procedures for the treatment of valvular regurgitation—mitral, tricuspid and/or otherwise. The stents may be self-expandable (e.g. nitinol or similar materials) or balloon expandable (e.g. cobalt chromium or similar materials). The stents are made of cells that may be open celled diamond like structures or continuous structures that have a working cell element. The stents may also be constructed using tubing, wires, braids or similar structures. Specific design features that aid with the functioning of the stent are described in detail below.
Referring to
A preferred construction comprises the prosthetic leaflets 106 disposed or spaced above the native leaflets when the prosthetic valve stent device 100 is implanted, wherein the prosthetic leaflets 106 are attached and spaced sufficiently away from (above) the native leaflets so as to not physically interfere or interact with the native leaflets. However, certain embodiments contemplate some interaction with the native leaflets.
The layer of stent cells that transition from the outer section to the inner section of the stent are termed as transition cells forming a transition section 108 generally as illustrated in
The outer and inner sections of the stent may be constructed from one continuous structure or may combine two or more structures to achieve intended design goals. As known in the art, stent structures may be formed using complementary shaped mandrels, including the outer section 102 of the stent, the transition section 108, and the inner valve support 104—including lobes L discussed above in certain embodiments—as a single unitary structure.
Referring now to
In certain embodiments the prolapse prevention structure 200 may comprise a coating comprising anti-thrombus formation compound(s) and/or anti-endothelization compound(s).
The exemplary prolapse prevention structure of
In certain embodiments, the outer support structure may be positioned generally so that it engages with tissue and works to prevent paravalvular leakage (PVL). For example, the outer support structure of the prolapse prevention structure may engage, or be integrated with, the transition section described above to provide a barrier against PVL.
Further in this regard, a preferred embodiment of the device shown in the Figures comprises a skirt S, comprising fabric or tissue, disposed along a portion of the outer surface of the outer frame element 102 and that extends along the outer surface of the transition section 108 and along the inner surface, or inwardly facing surface, of the inner valve support 102 so that the skirt S is facing the flow channel defined therein from the inflow end I to the outflow end O. In certain embodiments, the outer support structure of the prolapse prevention structure may also be covered with a fabric or tissue that, in combination with the tissue engagement of the outer frame and transition elements, may assist in preventing PVL.
Alternatively, the spanning elements or sections E may be connected to, or integrated with, the implanted prosthetic valve structure 200 as described above without aid or requirement of an outer support structure.
Generally the spanning elements or sections E may be disposed transverse to the blood flow through the inner valve support 104. In the case of an outer support structure, the spanning elements or sections E may be substantially coplanar with the outer support structure or, alternatively may extend either upwardly or downwardly from the outer support structure. All such exemplary structures are acceptable so long as the native leaflets are engaged by at least one spanning element or section E at a point of normal healthy functional coaptation. Thus, the outer support structure may be located at a point above the normal coaption point, wherein at least one spanning element or section extends therebelow to the normal coaptation point.
Turning now to
Alternatively, the leaf guards 200′ may effectively pin the native leaflets, so that the implanted prosthetic valve device 100 immediately becomes a full replacement device.
As shown in
An alternative embodiment to individual leaf guard elements 200′ may comprise one or more semi-circular leaf guard extensions, of a number and at a position that comports with the number of native leaflets and their general position. These semi-circular leaf guard elements 200′ may be positioned to (1) only engage native leaflets at the normal healthy coaptation point; or (2) effectively pin the native leaflets. In either case, the semi-circular leaf guard elements 200′ may be configured to, as described above, assist with positioning, locating and aligning the prosthetic valve device relative to the annulus. Further, as discussed above, the semi-circular leaf guard elements 200′ may be at least partially covered with a tissue or fabric that may be coextensive or connected with the skirt material of the outer frame, transition section and/or inner valve to assist in preventing PVL.
A still more alternative embodiment may comprise the leaf guard extension comprising an unbroken structure extending from the inner valve support and/or transition section, the unbroken structure taking an expanded shape that may be substantially circular and/or may substantially match the shape of the annulus. Again, the unbroken prolapse prevention structure may be configured to, as described above, assist with positioning, locating and aligning the prosthetic valve device relative to the annulus and may either engage the native leaflets at a normal healthy coaptation point or may work to pin the native leaflets. Further, as discussed above, the unbroken prolapse prevention element or structure may be at least partially covered with a tissue or fabric that may be coextensive or connected with the skirt material of the outer frame, transition section and/or inner valve to assist in preventing PVL.
In certain embodiments, at least a lower portion of the prolapse preventing elements 200′ may be relatively flexible and responsive to the pressure and fluid flow changes, while prevented from flexing upwardly past a coaptation point. Thus, during systole, the lower portion of the prolapse preventing elements 200′ may be urged to extend radially inwardly to engage the rising native leaflets at a normal healthy coaptation point. During diastole, the lower portion of the prolapse prevention elements 200′ may be urged to substantially straighten or be otherwise positioned to allow blood flow therealong such as may be seen with reference to
In some cases, the prolapse prevention elements 200, 200′ may be constructed to provide a second prosthetic valve, wherein they may, in response to the pressure and fluid flow changes discussed above, effectively open and close at least partially to further assist in preventing regurgitation. In this way, the prolapse prevention elements 200, 200′ may be viewed as the initial regurgitation barrier, in combination with the native leaflets, with the prosthetic leaflets functioning to stop any additional regurgitant. If, or when, the native leaflet function deteriorates nearly completely, the combination of the prolapse preventing elements 200, 200′ and the prosthetic leaflets 106 may work together to form a two-stage prosthetic staged set. This staging of regurgitant flow stoppage may work to extend the life of the native leaflets.
It is noteworthy that the various embodiments of the presently described prosthetic valve stent device 100 may be delivered percutaneously via one of at least the following known access and delivery routes: femoral access, venous access, trans-apical, trans-aortic, trans-septal, and trans-atrial, retrograde from the aorta delivery techniques. Alternatively, the prosthetic valve stent device 100 may be delivered and implanted using surgical and/or open heart techniques.
The description of the invention and its applications as set forth herein is illustrative and is not intended to limit the scope of the invention. Features of various embodiments may be combined with other embodiments within the contemplation of this invention. Variations and modifications of the embodiments disclosed herein are possible, and practical alternatives to and equivalents of the various elements of the embodiments would be understood to those of ordinary skill in the art upon study of this patent document. These and other variations and modifications of the embodiments disclosed herein may be made without departing from the scope and spirit of the invention.
This application claims the benefit of U.S. Provisional Application Ser. No. 62/680,073, filed Jun. 4, 2018 and entitled DEVICES, SYSTEMS AND METHODS FOR PREVENTING PROLAPSE OF NATIVE CARDIAC VALVE LEAFLETS, the contents of which are hereby incorporated by reference in its entirety.
| Number | Date | Country | |
|---|---|---|---|
| 62680073 | Jun 2018 | US |
