US20200146854A1 - Methods and devices for heart valve repair - Google Patents

Abstract

A system for reshaping a valve annulus includes an elongate template having a length along a longitudinal axis and at least one concavity in a generally lateral direction along said length. The pre-shaped template is positioned against at least a region of an inner peripheral wall of the valve annulus, and at least one anchor on the template is advanced into a lateral wall of the valve annulus to reposition at least one segment of the region of the inner peripheral wall of the valve annulus into said concavity. In this way, a peripheral length of the valve annulus can be foreshortened and/or reshaped to improve coaption of the valve leaflets and/or to eliminate or decrease regurgitation of a valve.

Description

CROSS-REFERENCE TO RELATED APPLICATIONS
• This application is a continuation-in-part of U.S. patent application Ser. No. 16/518,657 (Attorney Docket No. 32016-714.305), filed Jul. 22, 2019, which is a continuation U.S. patent application Ser. No. 16/356,933 (Attorney Docket No. 32016-714.304), filed Mar. 18, 2019, now U.S. Pat. No. 10,383,750, which is a continuation of U.S. patent application Ser. No. 16/039,194 (Attorney Docket No. 32016-714.303), filed Jul. 18, 2018, now U.S. Pat. No. 10,271,976, which is a continuation of U.S. patent application Ser. No. 15/921,508 (Attorney Docket No. 32016-714.302), filed Mar. 14, 2018, now U.S. Pat. No. 10,076,431, which is a continuation of U.S. patent application Ser. No. 15/605,601 (Attorney Docket No. 32016-714.301), filed May 25, 2017, now U.S. Pat. No. 9,943,426, which is a continuation of PCT Application No. PCT/US2017/032748 (Attorney Docket No. 32016-714.601), filed May 15, 2017, which claims the benefit of provisional patent application nos. 62/480,121 (Attorney Docket No. 32016-714.106), filed Mar. 31, 2017; 62/430,843 (Attorney Docket No. 32016-714.105), filed Dec. 6, 2016; 62/424,994 (Attorney Docket No. 32016-714.104), filed Nov. 21, 2016; 62/414,593 (Attorney Docket No. 32016-714.103), filed on Oct. 28, 2016; 62/374,689 (Attorney Docket No. 32016-714.102), filed on Aug. 12, 2016; and 62/337,255 (Attorney Docket No. 32016-714.101), filed on May 16, 2016, the full disclosures of which are incorporated herein by reference.
• This application is also a continuation in part of PCT/US2019/032976 (Attorney Docket No. 32016-717.601), filed on May 17, 2019, claiming the benefit of U.S. Provisional Application No. 62/767,958 (Attorney Docket No. 32016-717.102), filed Nov. 15, 2018, and of U.S. Provisional Application No. 62/673,680 (Attorney Docket No. 32016-717.101), filed May 18, 2018, the full disclosures of which applications are incorporated herein by reference.
• This application also claims the benefit of U.S. Provisional Application No. 62/937,417 (Attorney Docket No. 32016-717.103), filed Nov. 19, 2019, the full disclosure of which application is incorporated herein by reference.
BACKGROUND OF THEINVENTION1. Field of the Invention
• The invention generally pertains to mammalian body, specifically pertains to body lumens, vessels, openings, annuli, cavities, or organs. In particular this invention relates to the field of cardiology. More particularly, the invention pertains to heart valves treatment, repair, or replacement. More particularly, the invention pertains to devices and methods for repair of heart valves.
2. Description of the Background Art
• Heart valves have important biological function, with a wide range of anatomical configuration including shapes, designs, and dimensions, and are subject to an array of different conditions such as disease conditions that can cause impairment or malfunction. The mitral valve, for example, consists of an annulus containing anterior and posterior leaflets located at the junction between the left atrium and the left ventricle. The valve leaflets are attached to the left ventricle heart papillary muscles via chordae tendineae. Valvular impairment or dysfunction can be caused or exacerbated by changes to the valve configuration including shape, size, and dimension of the valve (or annulus), the length or functionality of the chordae, the leaflets function, causing impairment or dysfunction of the valve.
• An array of open heart surgical procedures have been utilized, including for example, surgical annuloplasty, implantation of artificial chordae or repair of chordae, and resection leaflet surgical valve repair. These procedures are performed typically via open heart typically using bypass surgery, including opening the patient's chest and heart, a risky and invasive procedure with long recovery times and associated complications.
• Current less invasive surgical devices and less invasive percutaneous devices are undergoing to replace or repair the mitral valve. Less invasive surgical and percutaneous options for valve repair typically attempt to replicate more invasive surgical techniques. These devices have the disadvantage of one or more of being large in size, complex to use, and have limited efficacy or applicability to the various anatomical configurations of valves. Results have been typically inferior to open surgical valve repair procedures. What is needed is a device that can be incorporated into less invasive surgical and percutaneous techniques, address valve regurgitation, minimize or eliminate device migration, device that is applicable to broader patient population having various valve configurations. The invention meets at least some of these needs.
SUMMARY OF THE INVENTION
• The present invention comprises devices and methods for less invasive surgical and/or percutaneous treatment or repair of a body organ, lumen, cavity, or annulus. In a preferred example, the present invention comprises devices and methods for open surgical, less invasive surgical, and percutaneous treatment or repair of heart valves comprising valve annulus and valve leaflets. An example of heart valves comprises aortic, mitral, pulmonary, and tricuspid valves. Although certain examples show a specific valve, the inventions described and claimed herein are applicable to all valves in the body and additionally other body annulus, lumen, cavity, and organs.
• In one example, the devices comprise a template having a first end, a second end, and a body extending between said first and second ends, wherein the device is configured to reshape a section of annulus from a substantially smooth shape to a convoluted shape which can foreshorten or otherwise tighten the valve or other annulus. Typically, the template is coupled to the annulus in one or more locations between said first and second ends. For example, the first and second ends of said template may be coupled to the annulus at two or more annulus points or regions, and/or said body may include one or more coupled locations which pull said annulus radially inwardly while said first and second ends exert a radially outward force on the annulus, substantially opposing the inward pull of said one or more coupled locations.
• In a preferred example, the template is coupled to the annulus at two or more location, and such locations are separated by a segment of the template body that exerts a radially outward force on the annulus substantially opposing the inward pull of said two or more coupled regions. In a preferred example, the body is coupled in one or more location to the annulus between the proximal and distal ends by means comprising one or more of: screws, clips, sutures, barbs, or other means. In another preferred example, the body is coupled to the annulus while the device is in a deflected configuration. In yet another preferred example, the body is coupled to the annulus at or near a mid-point between first and second ends. In yet another example, the body is coupled to the annulus at two locations, said locations lie between first and second ends. In yet another example, the body is coupled to the annulus in three locations wherein the locations lie between first and second ends of the template. In a preferred example, the device is formed from a material wherein the material comprises one or more of: rigid, self-expanding, elastic, super-elastic, plastically deformable, and has a form comprising one or more of: coil, screw, spiral, spring, barb, suture, hook staple, etc. In a preferred example, the means coupling one or more locations means on the body to the annulus comprises one or more of the following actions: penetrating the annulus, and holding together said annulus and body at the coupling location; penetrating the annulus, holding together said annulus and body at the coupling location, and pulling in said annulus to desired shape (configuration) upon deployment of the device; penetrating the annulus, holding together said annulus and body at the coupling location, and pulling in said annulus to desired shape (configuration) upon deployment of the device and coupling said proximal and distal ends to one or more annulus points or regions conforming to said body coupled region to said annulus, reshaping coupled annulus, reshaping coupled annulus to shape of body in the coupled region.
• In a preferred example, the template has an undulating shape.
• In another example, the template has an undulating shape with an even number of undulations pressing into the annulus, and an odd number of undulations which are coupled to the annulus by coupling mechanism(s) in tension.
• In another example, the template has an undulating shape with an odd number of undulations pressing into the annulus, and an even number of undulations which are coupled to the annulus by coupling mechanism(s) in tension.
• In another example, the template has an undulating shape with an even number of undulations pressing into the annulus, and an even number of undulations which are coupled to the annulus by coupling mechanism(s) in tension.
• In a preferred example, the template surface is compatible with tissue in contact with the template. This compatibility can be achieved through a number of methods known to the arts including template material choice, template surface finish, coatings, flocking. The compatibility can also be achieved through a variety of covering materials including ePTFE, Dacron knits, other knit fabrics, and the like.
• In a preferred example, the valve annulus comprises annulus and tissue adjacent to annulus.
• In another example, the device is an implant or a temporary implant.
• In one example, the device is formed from one or more of the following material: strong, stiff, resilient, shape memory, elastic, plastically deformable, capable of withstanding cyclic load of at least 10 million cycles.
• In another example, multiple devices are implanted along the annulus.
• In another example, multiple devices are implanted along the annulus and connected with rigid or semi-rigid connectors.
• In one example, the device is formed from a degradable or non-degradable material.
• Device comprises a template wherein the device comprises an expandable body, a ring, a body with one end, a body with two ends, a body with three ends or more.
• In certain further examples, the implant of the present invention may comprise a tissue coupling mechanism configured to anchor, secure, or stabilize the template and position the undulating body of the template adjacent to the inner surface of the heart valve annulus. The tissue coupling mechanism may comprise a tissue penetrating element. The tissue coupling mechanism may have a first tissue penetrating element at a first connected end of the inner and outer arcuate members and a second tissue penetrating element at second connected end of the inner and outer arcuate members, and the tissue penetrating element(s) may comprise of projection(s) such as barb(s).
• In one example, the device comprising a body wherein the body comprises a proximal end, a distal end, and a shaft extending between said proximal and distal ends, wherein the device is configured to being expandable from crimped configuration to an expanded configuration, and wherein the shaft is coupled to the annulus in one or more locations between said proximal and distal ends, and wherein the proximal and distal ends of said body are coupled to two or more annulus points or regions, and wherein said shaft one or more coupled locations pull said inward while proximal and distal ends stretch annulus coupled to said proximal and distal ends. In a preferred example, the shaft is coupled in one or more location to the annulus between the proximal and distal ends by means comprising one or more of: screws, clips, sutures, barbs, or other means. In another preferred example, the shaft is couple to the annulus while the device is in a crimped configuration. In yet another preferred example, the shaft is coupled to the annulus at a mid-point between proximal and distal ends. In yet another example the shaft is coupled to the annulus at two locations, said locations lie between proximal and distal ends. In yet another example, the shaft is coupled to the annulus in three locations wherein the locations lie between proximal and distal ends of the body. In a preferred example, the device is formed from a material wherein the material comprises one or more of: self-expanding, elastic, plastically deformable, coil, spring, etc. In a preferred example, the means coupling one or more locations means on the shaft to the annulus comprises one or more of the following actions: penetrating the annulus, penetrating the annuls and holding together said annulus and shaft at the coupling location, penetrating the annulus, holding together said annulus and shaft at the coupling location, and pulling in said annulus to desired shape (configuration) upon deployment of the device, penetrating the annulus, holding together said annulus and shaft at the coupling location, and pulling in said annulus to desired shape (configuration) upon deployment of the device and coupling said proximal and distal ends each to one or more annulus points or regions, conforming to said shaft coupled region to said annulus, reshaping coupled annulus, reshaping coupled annulus to shape of shaft in the coupled region.
• In a preferred example, the valve annulus comprises annulus and tissue adjacent to annulus.
• In another example, the device is an implant or a temporary implant.
• In another example the device comprises a body and two ends. In another example, the device comprising a body and two ends, wherein each end comprising at least one prong, wherein the two ends push two or more tissue points or regions outwardly. In one example, the two ends bifurcate into two or trifurcate into three prongs. In a preferred example, the two ends are connected by a shaft. In another example, the two ends are connected by one or more shafts. In yet another example the two ends are connected by two or more shafts. In yet another example, the two ends are connected by a shaft wherein the shaft branches into multiple shafts along the path of said shaft. In a preferred example the shaft comprises a solid body, yet it may also in other examples comprise hollow (tubular) body, or other. In a preferred example the shaft has a round shape. In other examples, the shaft shape comprises oblong, rectangle, semi-circle, triangle, elliptical, dog bone, square, or other shapes. The two ends may have the same shape and geometry or may have different shapes and geometries. In yet another example, the two ends have the same shape and geometry as the shaft. In yet another example, the device ends comprise one or more prongs wherein the prongs have a shape or geometry comprising one or more of spear, barb, pad, flat, disc, rough surface, round, square, rectangle, bulbous, arc, or other. In yet another example, the one or more prongs may be coupled to adjacent tissue wherein the prong coupling to the tissue comprises one or more of suturing, screw, geometry of the prong such as a barb configuration penetrating the tissue, coupling, placating, pressing, surface adhesion, surface friction, or other. In yet another example, each of the two ends comprises one or more prongs, wherein each end prongs have the same or different shape or geometry. In yet another example, each of the two ends comprises two or more prongs, wherein each of the prongs have the same or different shape or geometry. In yet another example, the device comprises at least one end wherein said end comprises at least two or more prongs bifurcate about the same location on the shaft. In yet another example, the two or more prongs bifurcate at different locations along the shaft length. In yet another example, the device comprises at least one end and wherein said at least one end has two or more prongs wherein the function of the two or more prongs may be the same or different. In yet another example, the device comprises at least one end and wherein said at least one end has two or more prongs and wherein at least one prong pushes adjacent tissue outwardly. In yet another example, the device comprises at least one end and wherein said at least one end has two or more prongs and wherein at least one prong pushes adjacent tissue outwardly and at least one prong pulls in adjacent tissue inwardly. In yet another example, the device comprises at least one end and wherein said at least one end has two or more prongs and wherein at least one prong pushes adjacent tissue outwardly and at least one prong holds adjacent tissue in place. In yet another example, the device comprises at least one end and wherein said at least one end comprises at least one prong and wherein the function of said prong comprises one or more of securing an end of the device to adjacent tissue, pushing adjacent tissue outwardly, holding in place adjacent tissue, pulling inward adjacent tissue, aligning tissue regions, configuring tissue regions to be out of plane (misaligned), controlling or limiting penetration depth of the device into the tissue, or other. In yet another example, the device comprising a body and two ends wherein each end comprising at least one prong, wherein the two ends push two or more tissue points or regions outwardly, and wherein other two or more tissue points or regions are pulled inwardly (or pulled in together). In yet another example, the device comprising a body and two ends wherein at least one end comprises at least two prongs, wherein at least one prong pushes adjacent tissue outwardly, and wherein at least one prong is pulling adjacent tissue inwardly, and wherein two or more tissue points or regions between the two ends are pulled inwardly. In a preferred example, the two or more tissue points or regions are adjacent to said body ends. In one example, the device is coupled to one or more tissue points or regions to push said tissue points or regions outwardly, and wherein the device is configured to exert outward force to said one or more tissue points or regions, and wherein the location of device coupling comprises one or more locations comprises the body of the device, device one or more ends, device one or more prongs, to affect an annulus shape wherein two or more points regions on the annulus are pushed outwardly while two or more points or regions on the annulus are pulled inwardly.
• In one example, the device comprising a body, wherein said body is connected to at least two ends wherein each end comprising at least one prong, wherein the at least two ends push two or more tissue points or regions outwardly. In yet another example, the device comprising a body and at least two ends, each end comprising at least one prong, wherein the at least two ends push two or more tissue points or regions outwardly, and wherein two or more other tissue points or regions are pulled inwardly. In a preferred example, the two or more tissue points or regions pushed outwardly are adjacent to said body ends and the other two or more tissue points or regions pulled inwardly are located between said body ends. In a preferred example, the device is positions in a valve annulus wherein two or more tissue points or regions pushed outwardly are adjacent to said body ends at the annulus and the other two or more tissue points or regions pulled inwardly are located between said body ends at said the annulus. In one example, the device is attached or affixed to adjacent tissue in one or more locations to affect outward and/or inward movement of tissue and/or annulus shape.
• In another example, the device comprises a body having at least two ends, wherein each end comprises at least one prong and wherein at least one end or at least one prong is pushing an adjacent tissue outwardly. In another example, the device comprising a body, wherein said body has at least two ends wherein each end comprising at least one prong, and wherein the device is coupled, in one or more locations, to one or more tissue points or regions and configured to pushing said tissue points or regions outwardly and wherein other tissue points or regions between said coupled locations are pull inwardly and wherein the device ends affect the tissue (including annulus) wherein an effect may comprise one or more of two ends pushing two or more tissue (including annulus) points or regions comprising one or more of apart, outwardly, in opposite direction, in plane, out of plane. In another example, the device comprising a body, wherein said body is connected to three ends wherein each end comprising at least one prong.
• The device may be a rod with two ends, a device having body like a disc or a stent, or other comparable structures.
• In one example, the device is formed from a resilient material shaped into a rod having two ends and a shaft connecting said two ends.
• In one example, the device is formed from one or more of the following material: strong, stiff, resilient, shape memory, elastic, plastically deformable, capable of withstanding cyclic load of at least 10 million cycles.
• In one example, the device is formed from a degradable or non-degradable material.
• Device comprises a body wherein the device comprises an expandable body, a ring, a shaft with one end, a shaft with two ends, a shaft with three ends or more.
• In a further aspect of the present invention, an implant is configured to reshape a heart valve having a valve annulus and valve leaflets. The implant comprises an inner arcuate member configured to conform to an inner surface of a heart valve annulus and an outer arcuate member configured to conform to an inner surface of a heart wall adjacent to the heart valve annulus. The inner and outer arcuate members are coupled together and are further configured to be attached to tissue in, on, or near the heart valve so that the inner arcuate member applies an inwardly acting radial force on at least a portion of the inner surface of the valve annulus and the outer arcuate member applies an outwardly acting radial force on the inner surface on the heart wall. Such forces will stabilize the annulus to promote enhanced leaflet coaptation with minimum stretching of the valve leaflets.
• In certain examples of the implant, the inner and outer arcuate members are connected at their ends and have an annular space between an outer edge of the inner arcuate member and an inner edge of the outer arcuate member. A mechanism may be disposed in the annular space and be configured to adjust the relative positions of the inner and outer arcuate members in order to, for example, allow adjustment of the reshaping and stabilization of the annulus. The mechanism may comprise a threaded member or other suitable linear translation element. Alternatively, the mechanism may comprise a spring or other self-adjusting coupling structure. In still further examples, the implant may comprise a plurality of mechanisms disposed in the annular space and configured to adjust the relative positions of the inner and outer arcuate members.
• In certain further examples, the implant of the present invention may comprise a tissue coupling mechanism configured to anchor the implant and position the inner arcuate member adjacent to the inner surface of the heart valve annulus and position the outer arcuate members adjacent to the inner surface of the heart valve wall. The tissue coupling mechanism may comprise a tissue penetrating element. The tissue coupling mechanism may have a first tissue penetrating element at a first connected end of the inner and outer arcuate members and a second tissue penetrating element at second connected end of the inner and outer arcuate members, and in all cases, the tissue penetrating element(s) comprise barb(s).
• In yet another aspect of the present invention, a method for treating a heart valve having a heart valve annulus, valve leaflets and a heart valve wall surface adjacent to the annulus comprises providing an implant comprising an inner arcuate member configured to conform to an inner surface of the heart valve annulus and an outer arcuate member configured to conform to an inner surface of the heart wall adjacent to the heart valve annulus. The implant is implanted above the heart valve so that the inner arcuate member applies an inwardly acting radial force on at least a portion of the inner surface of the valve annulus and the outer arcuate member applies an outwardly acting radial force on the inner surface on the heart wall.
• These methods may further comprise adjusting a width or other dimension, angle, or shape of an annular space between an outer edge of the inner arcuate member and an inner edge of the outer arcuate member to vary at least one of the inwardly acting radial force on at least a portion of the inner surface of the valve annulus and the outwardly acting radial force on the inner surface on the heart wall. Implanting may comprise anchoring the implant into tissue around the heart valve, for example by anchoring at least a first end on the implant and a second end of the implant wherein the inner and outer arcuate members are connected. Anchoring the implant into tissue around the heart valve may comprise penetrating elements into tissue in or adjacent to the annulus. For example, anchoring the implant into tissue around the heart valve may comprise inserting fasteners, such as barbs, helical anchors, screws, and the like which are attached or otherwise coupled to the implant, into tissue where the fasteners may be located at a first end on the implant and a second end of the implant wherein the inner and outer arcuate members are connected. In a further example, anchoring the implant into tissue in or adjacent to the annulus may comprise one or more tissue penetrating anchors intermediate to the first and second ends of the implant. In a further example, the tissue being pulled inward by the template may comprise valve leaflet tissue, which is stretched toward the opposing valve leaflet.
• Various control and delivery mechanisms are illustrated herein, including torsion tubes and delivery devices that interact with the body of the template. These control mechanisms may be actuated manually by the operator, or by a remotely powered actuator system.
• In various of the above examples, the surface of the template may be partially or fully covered with ePTFE, velour, knitting, weaving, spray coating, electrospun coatings, combinations thereof, or the like.
• In various of the above examples, the surface may be partially or fully coated with anticoagulants, anti-thrombotic agents, thrombolytic agents, anti-thrombin agents, anti-fibrin agents, anti-platelet agents, combination thereof, or the like.
• In various of the above examples, the surface or a surface covering may have pores at least partially filled with anticoagulants, anti-thrombotic agents, thrombolytic agents, anti-thrombin agents, anti-fibrin agents, anti-platelet agents, combination thereof, or the like.
• In various of the above examples, an anchor surface may be partially or fully coated with anticoagulants, anti-thrombotic agents, thrombolytic agents, anti-thrombin agents, anti-fibrin agents, anti-platelet agents, combination thereof, or the like.
• In various of the above examples, a proximal end of one or more anchors may collapse into a minimal structure upon removal of the torque tubing.
• In various of the above examples, the annulus may also include tissue adjacent to the annulus.
• In one exemplary embodiment, an implant constructed in accordance with the principles of the present invention for reshaping a valve annulus comprises a pre-shaped template and at least one anchor. The pre-shaped template has a length in an axial direction and at least one concavity extending in a lateral direction along the length. The concavity defines a concave surface on one side of the template, which concave surface is typically configured to be positioned against and/or adjacent to a peripheral wall of valve annulus. The at least one anchor on the template is configured to draw at least one segment (region) of the peripheral wall of the valve annulus into the concavity so that the segment (region) is brought up against the concave surface to at least partially conform to the shape and contour of the concave surface.
• The pre-shaped template may have a variety of geometries. It will typically be a non-linear elongated member having a surface with a shape or contour which will be imparted to the segment of peripheral wall of valve annulus after the template has been anchored to the annulus tissue. In many examples, the pre-shaped template will be curved along its length, typically having a serpentine, undulating, angulated (having one or more abrupt bends or angles along its length), or have another wave-like or zig-zag profile which will cause the periphery of the annulus to fold or plicate, thereby shortening and/or repositioning a peripheral length of the annulus, in a manner mimicking annuloplasty when the template is attached to the annulus.
• Although in many examples, the pre-formed template will be free from angled bends along its length, in other examples the concavity may be formed with angled bends (angulated) along the length of the template, for example the concavity may have a rectilinear periphery (four sequential bends of approximately 90° each defining the concavity). In other examples, angulated bends may be combined with curved or arcuate segments to shape the template.
• In many examples, the concavities of the pre-shaped template will be symmetric about a lateral axis, usually having opposed legs joined by a curved junction region forming the bottom of the concavity. In some examples, either or both opposed legs may have a convex surface (convexity) formed at an outer termination or transition region thereof. Usually, such convex surfaces will be axially and laterally spaced-apart from the curved junction region of the concavity, and the at least one anchor of the implant will be further configured to draw adjacent segments of the peripheral wall of the valve annulus against the convex surfaces as well as into the concavity.
• In still other specific examples, the pre-shaped template may have at least two concavities separated by a convexity therebetween. In such examples, the concavities may be disposed symmetrically about a lateral axis passing through a mid-point or apex of the convexity therebetween. The convexity will typically comprise a curved junction region which joins a pair of oppose legs, with each leg joined its lower end to one of the concavities, with each concavity being laterally spaced-apart from the mid-point of the convexity. In such examples, the at least one anchor on the template is further configured to draw adjacent segments of the peripheral wall of the valve annulus against the concave surfaces as well as against the convex surfaces therebetween.
• In all such examples, the implants of the present invention may be used individually or in groups of two, three, four, or more. When used in groups, the implants may be left unattached after they have been implanted, or alternatively may be further joined together in tandem, for example by bonding or attaching terminal regions of one implant to terminal regions of an adjacent implant.
• Implants of the present invention may be implanted in any cardiac valve, venous valve, or other vascular valve of a human or other patient. For example, the implants may be implanted into all or a portion of a patient's posterior mitral valve annulus, posterior tricuspid annulus, anterior-posterior tricuspid annulus, aortic annulus, pulmonary valve annulus, or the like.
• The templates of the present invention will generally comprise an elongate structure having at least two of terminal ends, a pair of side edges, a tissue-engaging surface, and an inwardly facing surface, but can have other structures with various number of edges, surfaces, and terminal ends. The length of template, when in its non-linear form, will typically be from 10 mm to 185 mm, often being in arange 10 mm to 75 mm, and sometimes being in therange 20 mm to 60 mm. The width of the template will typically be in a range from 1 mm to 15 mm, usually from 2 mm to 8 mm, and often from 2 mm to 6 mm. The thickness of the template will typically be from 0.1 mm to 2 mm, more usually from 0.2 mm to 1.5 mm. In specific examples, the elongate structures of the templates may comprise of a plate, a ribbon, a mesh, a lattice, a beam, a tube, a rod, a cylinder, a coil, a spiral, a spring, or a combination thereof. Exemplary templates will be elongated, shape-memory metal ribbons which have been heat-set or otherwise shape-set to a desired non-linear geometry with one or more concavities.
• The elongate structures of the templates may be formed from any material having sufficient strength, resiliency, and biocompatibility to be implanted in a patient's heart and to conform to a region of the patient's peripheral annulus to effect shortening thereof, typically being a metal, such as a nickel-titanium alloy, a stainless steel, or the like.
• Individual implants according to the present invention may have a single concavity, at least two concavities, at least three concavities, at least four concavities, typically having from one to twelve concavities.
• While the pre-shaped of the present invention templates will usually be a curved, elongated structure having and having first and second discrete ends, in other examples, they may comprise or be joined together as a continuous ring intended to be implanted about a full periphery of the patient's valve annulus. In some examples, a plurality implants (typically from two to six) having discrete ends may be configured to be joined end-to-end either before implantation or after implantation (in situ). In both examples, the templates will form a continuous structure about the entire periphery of the valve annulus.
• In many examples, the implant templates of the present invention will be pre-shaped, i.e. will have an undulating, serpentine, and/or angulated shape imparted during manufacturing. In other examples, it may be possible to provide templates which are configured to be shaped in situ.
• In some examples, the templates of the implants of the present invention may be covered in a biocompatible material, such as ePTFE, polyethylene terephthalate (Dacron®), or other materials intended to encourage tissue in-growth. Such biocompatible materials may be formed into suitable structures including open-cell foam structures, closed-cell foam structures, woven fabrics, non-woven fabrics, texture or surface finishes, and the like.
• The anchors of the implants of the present invention will typically be tension anchors configured to draw at least a portion of a segment of an inner surface of annulus into the concavity. For example, the anchors may comprise a helix, a ratcheting tether, a screw, a coil, a spiral, a hook, a barb, a clip, a lock, a staple, or any other type of fastener which can both engage the target tissue and draw the target tissue into the concavity. Suitable tissue anchors may have one or more ribs, wings, barbs, expansion elements, wedges, extensions, protrusions, and combinations thereof.
• In a specific instance, at least one anchor may comprise a helical anchor having a distal end and proximal end. The distal end may have a sharpened tip, and the proximal end may be rotatably secured in the concavity of the template, typically at a mid-point of a curved junction region. Usually, the helical anchor will be configured to be engaged by a detachable driver to rotate the helical anchor to drive the sharpened tip into the annulus and draw at least a segment of an inner surface of the annulus into the concavity. Such anchors may comprise a helical coil, a screw, a spiral, or the like, typically being a helical coil.
• In further specific examples, the concavity in the template will have a depth in the lateral direction. The helical anchor may have a length which is greater than depth of the concavity. In this way, the sharpened tip will be positioned beyond an outer tissue-engaging surface of the template so that the tip can engage tissue without the need to deform the pre-shaped template. In other examples, however, the helical anchor may have a length which is less than a depth of the concavity. In such examples, the sharpened tip can engage tissue by pressing the template against the target tissue and deforming the template to allow the sharpened tip of the helical anchor to engage the target tissue.
• In other exemplary examples of the present invention, the anchor may comprise any one or more of a ratcheting tether, hook, a barb, a fastener, a clip, a loop, or a staple. Such anchors have a distal end and a proximal end, where the distal may comprise a sharpened tip and the proximal end may be secured in concavity of the template and be configured to push and pull with a detachable driver. In this way, the anchor can push and pierce into the annulus to draw at least a segment of the inner surface of the annulus into the concavity and to lock that segment into place.
• In still further specific examples, the implants of the present invention may comprise elements or components for stabilizing tissue. For example, a tissue-coupling mechanism may be attached at either or both of the ends of a pre-shaped template to stabilize the template and hold it in place after implantation. Such tissue coupling mechanisms may comprise, for example, helical anchors or other fasteners configured to be rotatably advanced into tissue, where such anchors are similar to the primary anchor intended to draw tissue into the concavity. Other stabilizing tissue coupling mechanisms may include self-penetrating barbs, staples, clips, or the like that can be used to secure the free ends of the template against the valve annulus tissue.
• In still further specific examples of the present invention, the stabilizing mechanism for the template may comprise a stabilizing arm which extends laterally from the pre-shaped template, where the stabilizing arm may engage tissue above the annulus after the template has been implanted. The stabilizing arm may have a pad at its distal end, or may alternatively comprise a stabilizing anchor or other fastener similar to those described above for the ends of the template.
• In still further aspects, the present invention comprises systems for reshaping a valve annulus. Such systems may include any of the implants described above in combination with a delivery catheter. The delivery catheter typically has proximal end and a distal end, where the implant is removably carried on the distal end. In exemplary examples, the delivery catheters may comprise at least one flexible tension member secured to the at least one anchor on the template, typically comprising a plurality of flexible tension members when the template includes a plurality of anchors. The flexible tension members are removably secured to the anchors so that the catheter may be detached from the implant after implantation has been completed. The flexible tension members are typically further configured to rotate the at least one anchor to advance said anchor into tissue. For example, the flexible tension members may comprise a flexible coil or other rotatable drive shaft having a distal coupling member configured to removably engage a drive element on the proximal end of the at least one anchor.
• For example, the coupling member may comprise a sleeve or bushing with a hole or passage or other aperture formed in a wall thereof, and the flexible tension member may comprise a separate wire or elongate element for passing through the aperture in the coupling member so that rotation and attachment of the flexible tension member to the coupling member can controlled by advancing and retracting the elongate element into and out of the aperture.
• The systems of the present invention may further comprise elongated control elements detachably secured to the ends of the pre-shaped template. For example, the elongated control elements may be configured to collapse the pre-shaped template about the anchor, typically so that the implant may be collapsed during delivery and opened after advancement from the delivery catheter. Alternatively, the elongated control elements may be configured to pull back the pre-shaped template away from the anchor, again to reduce its profile for delivery while allowing release to its original configuration after advancement toward the valve annulus.
• In still further examples, the systems of the present invention may comprise a pre-anchor guide slidably coupled to delivery catheter. The pre-anchor guide may comprise a guide wire-like shaft having a coil or other tissue anchor at its distal tip. In this way, the pre-anchor guide may be advanced into the valve annulus at particular target location prior to advancement of the implant. The delivery catheter can then be advanced over the pre-anchor guide to properly position the implant prior to implantation.
• In still further exemplary examples, the present invention provides methods for reshaping a valve annulus. Typically the methods comprise engaging a template against a peripheral surface of the valve annulus, where the template has both a tissue-engaging surface and at least one concavity formed in the surface in a radially inward direction relative to the valve annulus. At least one segment of peripheral surface of the annulus is drawn into the concavity, resulting in a shortening and/or repositioning of a peripheral length of the valve annulus, which can mimic annuloplasty and reduce valve regurgitation, particularly mitral valve regurgitation in at least most patients.
• In specific examples of the methods herein, the template may be configured to be engaged against a peripheral surface of at least a length a posterior segment of a tricuspid valve annulus, an aortic valve annulus or a pulmonary valve annulus. The lengths of engagement will range from 10 mm to 185 mm, with other specific ranges as set forth above with regard to the implant design of the present invention.
• The implanted templates will typically comprise an undulating, serpentine or angulated structure having the at least one concavity. Such undulating, serpentine or angulated structures may have two concavities, three concavities, four concavities, five concavities or more as described previously. The templates will typically be pre-shaped but in other examples could be formed in situ. In still other examples, multiple templates may be implanted and joined together prior to implantation or in situ to provide for a longer engagement against the valve annulus, and in some examples engaging an entire periphery of a valve annulus.
• In many examples, applying tension to a peripheral wall segment to draw the segment in the concavity typically comprises advancing the anchor into a target region on the peripheral annulus in a manner that draws that tissue into the concavity on the template. Usually, the anchor comprises a helical coil, screw, or spiral having a proximal portion which is rotatably attached to the template, typically at a bottom of the concavity, so that the anchor will remain laterally fixed relative to the template while the anchor acts as “cork screw” in drawing tissue into the concavity.
• In other examples, drawing a segment of the annulus into the concavity may comprise applying compression to the segment to compress the segment into the concavity. For example, compression may be applied by looping, tying, suturing, clipping or the like. In other examples, compression may be effected by a compression anchor configured to secure and stabilize the template to the tissue. Such compression anchors include a helix, a ratcheting tether, a screw, a coil, a spiral, a hook, a barb, a fastener, a clip, a hook, a staple or the like.
• The methods of the present invention may comprise advancing the template intravascularly, percutaneously (such as via a transapical approach), or via a minimally invasive approach, such as a thoracoscopic approach.
• In specific examples, the templates may be attached to the target tissue of the annulus by rotating a helical end anchor on the template, where the anchor has a proximal end and sharpened distal end. Typically, rotating such anchors comprises rotating a flexible tension member in the delivery catheter to drive the sharpened distal tip into tissue and draw the tissue segment of the annulus into the concavity.
• In still further exemplary examples, the methods for reshaping a valve annulus may comprise placing a semi-rigid template adjacent to a portion of the peripheral wall of the heart valve annulus. The semi-rigid template is fastened to the portion of the peripheral wall in a manner such that the annulus is caused to approximate the shape of the template. For example, the template may exert opposing radial forces on the inner wall of annulus to cause the annulus to partially plicate and foreshorten. Usually, the semi-rigid template will not substantially increase a diametric dimension of the annulus. The template as with previous examples may comprise multiple segments having substantially the same shape. Alternatively, the template may comprise multiple segments having distinct shapes.
• In one example, the invention is a system to reshape a valve annulus comprises a template having a preformed shape with at least one concavity and at least one anchor on the at least one concavity, wherein the template is delivered to appose an annulus region, wherein said anchor is configured to reposition said annulus region into said concavity. In a further example, said template has two additional anchors to hold said template in place and prevent flipping or twisting of the template about its axis. In a further example, the template is releasably coupled to a delivery device, and wherein the delivery device is removed after anchoring said template to said annulus region. In yet another example, the said template having a length along a longitudinal axis and at least one concavity in a lateral direction along said length, and said template has two apex segments each segment connected by a leg to one side of said concavity, wherein each of said apex segment has an anchor configured to affix at least one region of said apex segment to adjacent annulus. In another example, the apex segment comprises one or more of convex region, flat region, and concave region(s). In yet another example, the template comprises a plurality of concavities and a plurality of apex segments, wherein some or all of the concavities has an anchor configured to reposition at least one region of an annulus into said concavities, and some, all, or none of the apex segments may have anchors to attach the apex segments to adjacent annulus regions. In yet another example, the template comprises a plurality of concavities and a plurality of apex segments, wherein each concavity has an anchor configured to reposition at least one region of an annulus into said concavities, and wherein said template further comprises at least two apex segments wherein at least one of said apex segments has an anchor configured to attach at least one region of the apex segment to the adjacent annulus. In another example, the said template has the advantage of repositioning selective regions of valve annulus. In another example, the template is configured to reposition one region of a valve annulus, wherein the region comprises a posterior annulus region, an anterior annulus region, a septal annulus region, or an anterior posterior region. In one example, annulus regions outside said template remain substantially unchanged. In another example, said template is configured to perform one or more of the following: reposition at least one region of an annulus into said concavity of the template, reduction of the valve annulus circumference, reducing an annulus configuration, reducing the annular area, reducing one or more dimensions of the annulus, reduction of a said annulus region circumference, configuration, or one or more dimension's. In another example, the template comprises at least one concavity joined by legs, wherein the legs comprise an apex segment and wherein each apex segment contains an anchor configured to attach at least one region of said segment to the adjacent annulus region, and wherein said concavity containing at least one anchor configured to pull in at least one region of an annulus into said concavity. In a preferred example, the apex segments have a substantially equal but opposite force to said anchor pulling in said annulus into said concavity. In another or same example, the apex segments are configured to prevent flipping or rotation of said template about its axis. In one example, the template is pre-formed before delivery into a patient body, in another example, the template is formed in situ. In a preferred example, the template comprising at least one concavity containing at least one anchor configured to pull in said adjacent and apposing annulus region into said concavity, wherein said annulus region conforms and/or contours substantially to the shape of said concavity. In another example, the template comprising at least one concavity may have various shapes of concavity, partial concavity, or a lateral space for an anchor to pull into said lateral space adjacent annulus region.
• In another example, a system to reshape a valve annulus comprises a template having a preformed shape, comprising at least one concavity and at least two apex segments wherein each apex segment has a leg connected to said concavity, and at least one anchor disposed in the at least one concavity, the template being constrained in a first crimped, smaller configuration for delivery to the annulus region, and being configured to appose an annulus region and pull in said annulus region into said concavity. In a variation of this example, the template is released from the first crimped configuration prior to apposing the said annulus, and constrained to a second crimped configuration wherein said second crimped configuration is larger or different than said first crimped configuration to reduce the force required to pull in said annulus region into said concavity. In this example, the second crimped configuration constraint means is different than the first crimped configuration constraint. In another example, the template is released from a first and/or second constraint after anchor pulls in annulus region into said concavity. In yet another example, the template is released from a first and/or second constraint prior to anchor pulling in said annulus region into said concavity. In a further example, the template comprises at least one opening in at least one apex segment connected to said concavity via a leg, wherein an anchor affixes at least one portion of said apex segment to an annulus region adjacent to the apex segment. In a preferred example, the template is held in the first crimped configuration inside a tubular body or at least partially inside a tubular body. In another example, the template is constrained in the second crimped configuration by at least one control wire configured to control at least one said apex segment rotation and/or affixing of said segment to adjacent annulus region, the template being releasably attached to said control wire, and said wire extending through a or the tubular body proximally outside the patient body to allow control of the template configurations at a distance from the template. In a further example, the template is releasably coupled to a delivery catheter and the delivery catheter is removed after anchoring the template to the annulus region. In a further example, the delivery catheter is inserted into the body or vasculature percutaneously, or surgically, or a hybrid procedure. In one example, the template is pre-formed prior to delivery into the annulus region. In another example, the template is formed in situ. In yet another example, the said template having a length along a longitudinal axis and at least one concavity in a lateral direction along said length, and said template has two apex segments each segment connected by a leg to one side of said concavity, wherein each of said apex segment has an anchor configured to affix at least one region of said apex segment to adjacent annulus. In another example, the apex segment comprises one or more of convex region, flat region, and concave region(s). In yet another example, the template comprises a plurality of concavities and a plurality of apex segments, wherein each concavity has an anchor configured to reposition at least one region of an annulus into said concavities, and wherein said template further comprises at least two apex segments wherein at least one of said apex segments has an anchor configured to attach at least one region of the apex segment to the adjacent annulus. In another example, the said template has the advantage of repositioning selective regions of valve annulus. In one example, the template is configured to reposition one region of a valve annulus, wherein the region comprises a posterior annulus region, an anterior annulus region, a septal annulus region, or an anterior posterior region. In one example, annulus regions outside said template remain substantially unchanged. In another example, said template is configured to perform one or more of the following: reposition at least one region of an annulus into said concavity of the template, reduction of the valve annulus circumference, reducing annulus configuration, reducing one or more dimensions of the annulus, reduction of a said annulus region circumference, configuration, area, or one or more dimensions. In another example, the template comprises at least one concavity joined by legs, wherein the legs comprise an apex segment and wherein each apex segment contains an anchor configured to attach at least one region of said segment to the adjacent annulus region, and wherein said concavity containing at least one anchor configured to pull in at least one region of an annulus into said concavity. In a preferred example, the apex segments have a substantially equal but opposite force to said anchor pulling in said annulus into said concavity. In another example, the apex segments are configured to prevent flipping or rotation of said template about its axis. In one example, the template is pre-formed before delivery into a patient body, in another example, the template is formed in situ. In a preferred example, the template comprising at least one concavity containing at least one anchor configured to pull in said adjacent and apposing annulus region into said concavity, wherein said annulus region conforms and/or contours substantially to the shape of said concavity. In another example, the template comprising at least one concavity may have various shapes of concavity, partial concavity, or a lateral space for an anchor to pull into said lateral space adjacent annulus region. In one example, the template is pre-formed into a substantially Omega shape comprising a concavity connected to two apex segments via legs connected to said concavity, and wherein said concavity having at least one anchor configured to pull in an annulus region into said concavity, and wherein the two apex segments each has an anchor configured to connect to adjacent annulus region to the said apex segment, and wherein the template is crimped into first crimped configuration having substantially U shape, wherein said U shaped template is constraint inside a first constraint comprising a tubular catheter and delivered in proximity to a valve annulus, and wherein the U shaped template is at least partially released from the tubular catheter, and wherein the concavity anchor apposes the desired annulus region and engages said annulus region pulling in said region into said concavity, and wherein the apex segments are positioned apposing to annulus regions and affixed to said annulus regions. The concavity anchor and apex segments anchors are controlled and/or constrained by (second constraint or second crimped configuration constraint) one or more wires, tubes, or the like that extend to outside the patient body and are configured to control anchoring of the template to the annulus, adjust the position of the template or template component, and/or to release the template. In one example, the template is pre-formed into a substantially Omega shape comprising a concavity connected to two apex segments via legs connected to said concavity, and wherein said concavity having at least one anchor configured to pull in an annulus region into said concavity, and wherein the two apex segments each has an anchor configured to connect to adjacent annulus region to the said apex segment, and wherein the template is crimped into first crimped configuration, wherein said template is constrained inside a first constraint comprising a tubular catheter and delivered in proximity to a valve annulus, and wherein the template is at least partially released from the tubular catheter, and wherein the concavity anchor apposes the desired annulus region and engages said annulus region pulling in said region into said concavity, and wherein the apex segments are positioned apposing to annulus regions and affixed to said annulus regions. The concavity anchor and apex segments anchors are controlled and/or constrained by (second constraint or second crimped configuration constraint) one or more wires, tubes, or the like that extend to outside the patient body and are configured to control anchoring of the template to the annulus, adjust the position of the template or template component, and/or to release the template. The template may be crimped into various shapes inside a constraint comprising U shape, helical shape, pre-formed shape, or other shapes configured to be deliverable into a patient body to an annulus region. In a preferred example, the apex segments are pulled or held in a proximal direction relative to the anchor to facilitate an easier anchoring of the concave anchor to the annulus and then the apex segments are positioned, anchored and released. In this example, the apex anchors enhance or augment the amount (or mass or volume or area) annulus region pulled into said concavity. In another example, the template concavity anchor engages the annulus pulling said annulus region into said concavity, while the apex segments are apposing an annulus regions, and then said apex segments apposing said annulus regions are affixed to said annulus region.
• In one example, a system to reshape a valve annulus comprising advancing an anchor which is releasably attached to an elongate control wire through a tubular body and attaching that anchor to an annulus region, placing a template having a preformed shape having a concavity (such as a template comprising a concavity and two apex segments connected to said concavity via legs forming a substantially Omega shape template) in a crimped (smaller) configuration into a constraint catheter, sliding the template concavity over the control wire and coupling the template concavity to the anchor. In a further example, said template further has at least one apex segment and has at least one additional anchor coupling the at least one apex segment to an adjacent annulus region. In a further example, the template is releasably coupled to a delivery catheter and the delivery catheter is removed after anchoring the template to the annulus. In another example, the delivery catheter is inserted into the body or vasculature percutaneously.
• In another example, a one or more segments of the template is coupled to an anchor to prevent translation along the axis of the anchor. In a further example, the one or more segments of the template is coupled to an anchor allowing the anchor to rotate about its axis relative to the template. In a further example, the anchor is coupled to the template in the region of a concavity.
• In one example, an implant having a preformed template wherein the template comprises at least one concavity and at least one connected apex segment wherein the at least one apex segment has at least one tissue anchor to affix the template to adjacent annulus, and at least one anchor is releasably attached to at least one elongate anchor control device extending from the implant to outside the delivery catheter of the implant. In a further example, the anchor control device is a tube with cut features to control flexibility. In a further example, the anchor control device is a tube with a key wire in the lumen configured to releasably engage the anchor. In a further example pulling the key wire releases the anchor from the anchor control device.
• In a preferred example, the template has at least one concave base and at least two apexes. In a further example, the width of the concave base is equal to the depth of the concavity. In a further example, the width of the concave base is greater than the depth of the concavity. In a further example, the width of the concavity is at least 1.5 times the depth of the concavity. In a further example, the width of the concavity is at least 2.5 times the depth of the concavity. In a further example, the width of the concavity ranges from 1× to 5× the depth of the concavity. In another example, the apex of the template has a flat or convex portion to it. In a preferred example, the template has a concave segment and two apexes, where the apexes have flat and/or convex segments. In a further example, the flat and/or convex segments of the apexes range from 2-40 mm long. In a further example, the flat and/or convex segments remain apposed to and/or affixed to the tissue. In another example, the implant has an apex segment comprising a length sufficient to inhibit tilting of the implant relative to the target tissue.
• In a preferred example, the template flexes in at least one direction during contraction of target tissue. In a further example, the template flexes to allow a change in distance between ends of the template as tissue flexes under one or more of the following physiologic conditions: heartbeat, annulus contraction, blood pressure changes, atrial expansion, ventricular expansion, blood flow, etc. In another example, the maximum dimension of the template in situ changes in response to tissue motion and physiologic forces.
• In one example, the implant template has at least one concave base and at least one apex connected to the concave base, wherein the apex and concave base are configured to be deformable and formed from one or more of the following materials: elastic, superelastic, shape memory, hard tempered, heat treated. Examples of said materials include one or more of the following: Nitinol, stainless steel, maraging steel, cobalt chromium, or the like.
• In another example, the implant template has at least one concave segment and at least one apex segment wherein the at least one apex segment is apposed and/or affixed to the annulus. In a further example, the implant has two or more concave segments separated by one or more apex segments, the concave segments being apposed and affixed to the annulus while one or more apex segments are apposed and/or affixed to the annulus. In another example, said implant has at least one apex on each end of the implant, wherein said apexes are apposed and/or affixed to the annulus. In a further example, the implant has at least one concave segment and at least one apex segment wherein the at least one apex segment is apposed and affixed to the tissue to inhibit tilting and/or rotation of the implant relative to the annulus or tissue.
• In a preferred example, the implant template is deployable from a crimped smaller configuration, to a larger or deployed configuration. In a further example, the crimped smaller configuration is smaller in at least one dimension than the deployed configuration. In a preferred example, the crimped smaller configuration passes through a smaller diameter tube than the larger or deployed configuration. In one example, in the crimped configuration, the ends of the implant are folded distally from the middle of the implant. In another example, in the crimped configuration, the ends of the implant are folded proximally from the middle of the implant. In a further example, in the crimped configuration, the ends of the implant are compressed toward the middle of the implant. In a further example, in the crimped configuration, the ends of the implant are compressed toward the middle of the implant and folded out of plane to form a substantially tubular shape.
• In a preferred example, the implant template having a preformed shape is deployable from a crimped smaller configuration, to a larger or deployed configuration. In another example, the deployed configuration is the unconstrained shape of the implant. In a further example, the crimped configuration is elastically deformed from the preformed shape. In another example, the implant is held in the crimped configuration until delivered adjacent to the annulus and/or tissue. In another configuration the implant is held in the crimped configuration by being at least partially inserted into a tubular body. In another example, the implant is deployed from the crimped shape to the deployed configuration by disengaging it from the tubular body, allowing it to return substantially to its preformed shape.
• In one example, the implant template comprises a preformed template configuration wherein the template comprises at least one concavity and at least one apex connected to said concavity, and a tissue anchor from the concavity and extending beyond the apex of the template in the preformed template configuration. In another example, the length of the anchor extends at least half way from the base of the concavity to the apex. In a further embodiment, the length of the anchor is greater than the depth from the base of the concavity to the apex such that as implant is in proximity to the tissue the anchor contacts tissue in advance of the apex of the template.
• In another example, an implant template has a crimped configuration and a deployed configuration, where the implant is delivered in the crimped configuration adjacent to the annulus and/or tissue, and then deployed by forming it in situ to the desired template shape. In another example, an implant having a delivery configuration and a deployed configuration, where the implant is in the delivery configuration is delivered adjacent to the annulus and/or tissue, and then deployed by forming it in situ to the desired template shape.
• In one example, an implant having a preformed template wherein the template comprises at least one concavity and at least one apex segment, wherein the apex and concavity are connected, defining the implant depth, and wherein the at least one apex segment has tissue engaging element to affix the template to adjacent annulus, and wherein the concavity comprises an opening to slidably engage a tissue engaging anchor element and lock to the tissue engaging anchor element. In another example, the implant system comprises a template having at least one concavity and at least one apex, and having a passage through which a tissue engaging anchor is slidably coupled.
• In one example, an implant having a preformed template wherein the template comprises at least one concavity and at least one apex segment, wherein the apex and concavity are connected, and the radius of curvature of the apex segment is greater than the radius of curvature of the concavity, wherein the apex segment in one example comprises a radius of curvature of at least 1.5 times the radius of curvature of the convex segment, wherein the apex segment in one example comprises a radius of curvature of at least 2.5 times the radius of curvature of the convex segment, wherein the apex segment in one example comprises a radius of curvature ranging from 1× to 5× the radius of curvature of the convex segment.
• In one example, an implant having a preformed template wherein the template comprises at least one concavity and at least one apex segment, wherein the apex and concavity are connected by legs, and the shape of the concavity and apex segments are configured to contact the tissue along substantially the entire inner surface of the implant when said tissue is pulled into said template.
• In one example, an implant having a preformed template wherein the template comprises at least one concavity and at least one apex segment, wherein the apex and concavity are connected, the concavity having a substantially rounded shape to receive and be coupled substantially along the length of the implant to the tissue and/or annulus when the implant is deployed in the tissue and/or annulus.
• In another example, an implant having a preformed template wherein the template comprises at least one concavity and at least one apex segment, wherein the apex and concavity are connected, and wherein the apex and concavity having substantially rounded shapes to receive and be coupled substantially along the length of the implant to the tissue and/or annulus when the implant is deployed in the tissue and/or annulus.
• In a preferred example, an implant having a template with one or more concavities connected to one or more apex regions by one or more legs, wherein the one or more concavities have annulus pulling anchors configured to pull inward said annulus region into said concavities, and wherein said one or more apex regions have one or more regions positioned against the annulus region to exert a radially outward force on the annulus, substantially opposing the inward pull force of the one or more concavities annulus pulling anchors. In a preferred example, the outward forces exerted by the apex segments do not reposition the annulus, or do not substantially reposition the annulus, outwardly. In another example, the template concavity repositions an annulus region into said concavity, wherein the circumference of the annulus remains substantially the same.
• In another example, an implant having a preformed template wherein the template comprises at least one concavity and at least one apex segment, wherein the apex and concavity are connected, and a tissue engaging anchor configured to draw at least a portion of a peripheral wall of a valve annulus at least partially into the concavity so that a peripheral length of the valve annulus can be foreshortened and/or reshaped to improve coapting of the valve leaflets and/or to eliminate or decrease regurgitation of a valve.
• In still another aspect of the present invention, a stent prosthesis for valve repair or replacement comprises a scaffold having patterned structural elements, said stent being expandable from a crimped configuration to an expanded configuration and having sufficient strength to support a body annulus in the expanded configurations, wherein the scaffold comprises at least one circumferential ring comprising struts and crowns, wherein at least one strut in said at least one ring comprises at least one separation region and wherein said at least one separation region comprises a male-female junction and a biodegradable polymer and/or adhesive, said separation region being held together in the crimped configuration and is configured to separate after expansion of the stent under physiologic environment, and at least one valve configured to be coupled to said at least one ring, said valve allowing blood to flow in one direction during the cardiac cycle.
INCORPORATION BY REFERENCE
• All publications, patents, and patent applications mentioned in this specification are herein incorporated by reference to the same extent as if each individual publication, patent, or patent application was specifically and individually indicated to be incorporated by reference.
BRIEF DESCRIPTION OF THE DRAWINGS
• The novel features of the invention are set forth with particularity in the appended claims. A better understanding of the features and advantages of the present invention will be obtained by reference to the following detailed description that sets forth illustrative examples, in which the principles of the invention are utilized, and the accompanying drawings of which:
• FIG. 1 shows a top down sectional view of the heart, illustrating the relative positions of the major valves of the heart.
• FIG. 2 shows a top view of the mitral valve in a closed configuration as visible from the left atrium.
• FIG. 3 shows a top view of the mitral valve having a gap between mitral valve leaflets preventing it from attaining a closed configuration thus causing Mitral Regurgitation (MR) or Functional Mitral Regurgitation (FMR). The valve typically has an enlarged annulus configuration.
• FIG. 4 shows the valve ofFIG. 3 stretched (extended) in accordance with the present invention (device not shown), in this example stretched in the Commissure to Commissure (C-C) dimension as shown, causing the gap between the leaflets to close as shown, thus reducing or eliminating MR or FMR. In this example, the annulus configuration changes wherein the annulus dimension becomes larger across the stretched dimension and becomes smaller across a perpendicular or offset dimension to the stretched dimension.
• FIG. 5A shows an example of a device in accordance of the present invention, having an arch shaped device which interacts (engages) with the valve commissures to affect the stretching illustrated inFIG. 4.
• FIG. 5B shows an example of a device in accordance of the present invention, having a partial ring shaped device which interacts (engages) with the valve annulus at multiple points to affect the stretching illustrated inFIG. 4.
• FIG. 6 shows an example of the arch shaped device ofFIG. 5 in place in the mitral valve. In this example, the arch of the device contacts the valve posterior annulus and substantially contours to the posterior shape of the valve annulus.
• FIG. 7 shows an example of an arch shaped stretching device secured by barbed penetrating ends.
• FIG. 8 shows and example of an arch shaped stretching device secured by helical fasteners at the ends.
• FIG. 9 shows an example of an arch shaped stretching device that stretches the annulus with shaped pads on each end.
• FIG. 10 shows a linear (straight) stretching device in a turnbuckle configuration.
• FIG. 11 shows a stretching device with a ratchet and pawl configuration.
• FIG. 12 shows a stretching device based on a compression spring.
• FIG. 13 shows a stretching device with an enclosed compression spring and a pin to hold it in a partially compressed state for delivery.
• FIG. 14 shows a close-up of the stretching device fromFIG. 13.
• FIG. 15 shows an alternative example of a stretching device based on a linkage configuration.
• FIG. 16 shows an alternative example of a stretching device based on a torsion spring, which is held in position by a helical fastener during delivery and placement.
• FIG. 17 shows an end view of one or more rings (or a stent-like structure) for stretching the mitral valve annulus across one or more dimensions.
• FIG. 18A andFIG. 18B show examples of placement of the stent-like structure.
• FIG. 18C shows an example of a structure with a single end.
• FIG. 19 shows an example of an elongated ring shape, applied to the annulus to stretch it in the C-C direction.
• FIG. 20 shows an example of an elongated partial ring shape with a gap, applied to the annulus to stretch it in the C-C direction.
• FIG. 21 shows an example of tightening pledgets applied to stretch the commissures of the valve.
• FIG. 22 shows an example of torsion springs attached at the commissures of the valve, configured to draw the leaflets together especially when the valve leaflets are out of plane while pushing the commissures apart.
• FIG. 23 shows an example of a semi-rigid, shape memory, or a spring like stent applied to the coronary sinus to straighten the sinus, creating a septal-lateral compression effect thus minimizing or eliminating MR or FMR.
• FIG. 24 shows an example of clips which attach to valve commissures or annulus in order to hold them in place, after using a stretching device to stretch the commissures or annulus thus allowing for removal of the stretching device while maintaining a smaller configuration (dimension) in the arterial-posterior direction of the valve or annulus.
• FIG. 25 shows a stretching device anchored at 3 points around the valve.
• FIG. 26 shows a range of angles at which application of the stretching device may be advantageous to treat or repair a valve impairment.
• FIG. 27 shows a stretching device with a Force Changing Element that changes the stretching force over time, preferably to decrease the stretching force once healing and/or tissue remodeling have taken place.
• FIG. 28 shows two examples of the Force Changing Element, one of which is separable into multiple components, the second of which remains a continuous component.
• FIG. 29A shows an illustration of the application of stretching devices to re-shape a round annulus to more approximate a triangle. As shown, the circle and triangle have substantially the same perimeter but can also be configured to be different.
• FIG. 29B shows an illustration of a stretching device configured to sit within a lumen and engage with three points around the circumference of the lumen, for example at a valve annulus, to re-shape it to more approximate a triangle.
• FIG. 30 shows the mitral valve of a pig in the at rest position.
• FIG. 31 shows the mitral valve of a pig with a stretching device in place. This stretching device arches above the plane of the mitral valve annulus. The stretching device increases the dimension of the annulus across the device path while decreasing the dimension of the annulus at an angle offset to the device path.
• FIG. 32 shows a helical member with a T-handle for applying torque, along with a snare and torque tube.
• FIG. 33 shows a pair of adjustable arms that are connected to two adjacent cells of the stretchable member and can draw them farther apart after initial deployment with a spring.
• FIG. 34 shows a conical spring that fixes one or more cells of the stretchable member and can draw the stretching member closer together and or farther apart after initial deployment by rotating the spring.
• FIG. 35A shows an element consisting of two arms that pivots to open or close depending on where the force is applied or released at their point of intersection.
• FIG. 35B illustrates the use of an expandable balloon to open or close the element inFIG. 35A.
• FIG. 36A shows a ring that fixed to the struts of one or more cells of the stretchable member.
• FIG. 36B illustrates the effect of the location of the ring with respect to the struts of a cell of stretchable member in causing the cell to open or close.
• FIG. 37 shows different spring or screw with a ball nut fixed to one or more cells of the stretchable member and rotated to draw the stretching member closer together and or farther apart after initial deployment.
• FIG. 38 shows a spring that fixes one or more cells of the stretchable member before and after the deployment of the stretchable member. Upon it removal, it allows the stretching member to go farther apart after initial deployment.
• FIG. 39 illustrates the use of shape memory elements embedded between adjacent cells of the stretchable member. The element remains the same distance before and after deployment of the stretchable member. After heating to a temperature above the transition temperature, it widens and allows the stretching member to become father apart.
• FIG. 40 illustrates the use of shape memory elements embedded between adjacent cells of the stretchable member. The element remains the same distance before and after deployment of the stretchable member. After heating to a temperature above the transition temperature, it narrows and draws the stretching member to closer together.
• FIG. 41 illustrates the use of shape memory elements connecting to a cell of the stretchable member. The element remains the same distance before and after deployment of the stretchable member. After heating to a temperature above the transition temperature, it narrows or widens and draws the stretching member closer together or farther apart to optimally adjust the valve dimensions.
• FIG. 42 shows an element consisting of two arms that pivots to open or close similar toFIG. 35A. It is fixed with a wire that can pivot the arms when it is twisted, causing the stretchable member to draw closer together or farther apart to optimally adjust the valve dimension.
• FIG. 43A shows an element consisting of two arms that pivots to open or close similar toFIG. 35A. It has a wire attached to two grippers that is secured to the arms at the point of their intersection. The wire is pulled by the use of an expandable balloon, causing the stretchable member to draw farther apart.
• FIG. 43B shows an element consisting of two arms that pivots to open or close similar toFIG. 35A. It has a wire attached to two grippers that is secured to the arms at the point of their intersection. The wire is pulled by the use of an expandable balloon, causing the stretchable member to draw closer together.
• FIG. 44 shows an element consisting of two arms that pivots to open or close similar toFIG. 35A. A double lead screw or spring mechanism with ball nuts apply or release forces on the point of intersection of the arms, causing the stretchable member to draw closer together or farther apart.
• FIG. 45A shows a section view of one of the implants showing coating on the surface of the implant.
• FIG. 45B shows a variety of cross sections that may be applicable to valve reshaping implants.
• FIG. 46 shows a cam element attached to adjacent cells of the stretchable element. When the cam is rotated, it narrows or widens the distance between the cells, causing the stretchable member to draw closer together or farther apart.
• FIG. 47 shows an element consisting of two arms that pivots to open or close similar toFIG. 35A. A conical spring is wound over the arms. When rotated, it pivots the arms to open or close, causing the stretchable member to draw closer together or farther apart.
• FIG. 48 shows an implant with a recurved spine which provides outward force to the anchor points.
• FIG. 49 shows a hook for capturing annular tissue with a barb to prevent inadvertent release of the device from the tissue.
• FIG. 50A shows a three-pronged end of an implant (device) arranged so that the two outer prongs are coplanar, and the middle prong is not coplanar.
• FIG. 50B shows the implant ofFIG. 50A with an elastic tissue member in place in the distal portion of the prongs.
• FIG. 50C shows the device (implant) ofFIG. 50A with the elastic tissue member ofFIG. 50B moved proximally in the prongs, resulting in a plication in the elastic tissue member.
• FIG. 51A shows a two-pronged implant with penetrating tips arranged at an angle to each other in proximity to an elastic tissue member.
• FIG. 51B shows the implant ofFIG. 51A having penetrated the elastic tissue member, resulting in bunching the elastic tissue between the two angled prongs.
• FIG. 52 shows a stretching device with a removable wire attached between the anchor points.
• FIG. 53 shows a stretching device with a retrieval device interface feature between the anchor points that can be grasped and released.
• FIG. 54 shows a stretching device with a third anchor point between the primary anchor points near the ends of the stretching member.
• FIG. 55 shows a partial ring-shaped stretching device with an anchor point near mid-span.
• FIG. 56 shows a stretching device with a third anchor point branching from one of the primary anchor points near the ends of the stretching device.
• FIG. 57 shows a stretching device with third and fourth anchor points branching from each of the primary anchor points near the ends of the stretching member.
• FIG. 58A shows a stretching device with four anchor points arranged to apply torsion between the pairs of anchors at each end point.
• FIG. 58B shows an additional example of a valve shaping device with four anchor points arranged to apply torsion between the pairs of anchors at each end point.
• FIG. 59A shows a saddle shaped mitral annulus with a shaping device having ends that mate with the curvature of the saddle shape to substantially maintain the saddle shape after a stretching device is deployed to minimize or prevent MR or FMR.
• FIG. 59B shows a flattened mitral annulus with a shaping device having ends that mate with the annulus, and a third attachment point that is disposed at a distance from the annulus.
• FIG. 59C shows the device of59B with the third anchor point brought into opposition with the annulus, restoring a saddle shape.
• FIGS. 60A-60I show a variety of stretching device configurations illustrated in position on the mitral valve.
• FIG. 61A shows a stretching device that starts in an arcuate configuration and moves to a substantially straight configuration.
• FIG. 61B shows a stretching device that starts in an initial arcuate configuration and moves to a configuration with an arcuate shape having a larger radius than the initial arcuate configuration, causing the angle of the ends to change as the distance between the ends increases.
• FIG. 61C shows a stretchable device that starts in an initial arcuate configuration and flattens in one portion while bending further in another, causing the angle of the ends to remain substantially constant as the distance between the ends increases.
• FIG. 62 shows a stretching device with a variable stiffness along the span between the ends, resulting in a stiffer end and a more flexible end.
• FIGS. 63A and 63B show a stretching device with two arches which move relative to each other as the length between the ends changes.
• FIGS. 64A to 64C show various configurations of stretching devices.
• FIG. 65A shows a docking anchor with removable wire.
• FIG. 65B shows a docking anchor with removable wire having been anchored to tissue.
• FIG. 65C shows a docking anchor with removable wire having been anchored to tissue, with a valve shaping device docked to the anchor.
• FIG. 65D shows the system ofFIG. 65C, the removable wire having been removed.
• FIG. 66A shows one end of a tissue shaping device engaged with a removable control wire based on a helical coil.
• FIG. 66B shows the device ofFIG. 66A with the control wire removed.
• FIG. 67A shows one end of a tissue shaping device engaged with a removable control wire based on screw threads.
• FIG. 67B shows the device ofFIG. 67A with the removable control wire removed.
• FIGS. 68A-68D show devices having multiple attachment points for flattening a segment of an annulus.
• FIGS. 69A and 69B show a device with two partial rings configured to apply an inward force on an area of the valve annulus and an outward force on the adjacent muscular wall of the heart.
• FIGS. 70A and 70B show adjacent partial rings configured to pull an annulus inwardly while pushing an adjacent muscular wall outwardly.
• FIGS. 71A and 71B show adjustable device with two partial rings having a single adjustment point to pull in an annulus point or region while stretching out an adjacent partial ring at the adjustment point.
• FIGS. 72A and 72B show an adjustable device with two partial rings having multiple adjustment points to pull in an annulus point or region and stretch out connected partial ring about the adjustment points.
• FIG. 73A shows a segment of a tube with controlled cuts, spaced relatively far apart to create a large bend radius.
• FIG. 73B shows a segment of a tube with widely spaced cuts and narrowly spaced cuts, to create bends with large and small radii, respectively.
• FIG. 74 shows a segment of a tube having cuts with different orientations, to create out of plane bends, or three-dimensional bend shapes.
• FIG. 75 shows a device with different bend radii and orientations which forms a “D” shape with an upright handle when subject to bending force, longitudinal compressive or tensile force, or a combination thereof.
• FIG. 76 shows the device ofFIG. 4 with the addition of control arms that can help to adjust the planar orientation of a substantially hoop shaped portion of the device.
• FIG. 77 shows alternative controlled cuts which include an interlocking feature of various designs.
• FIG. 78 shows an implant applied to a segment of the valve annulus having a curved shape
• FIG. 79 shows an implant applied to a segment of the valve annulus having a shape with multiple curves
• FIG. 80 shows an implant applied to an enlarged valve annulus consisting of multiple elastic segments, shown in the extended position.
• FIG. 81 shows an implant applied to an enlarged valve annulus consisting of multiple elastic segments, shown in the contracted position.
• FIG. 82 shows an implant with a combination of substantially rigid segment and elastic segments, shown in the contracted position.
• FIG. 83 shows an anchor for fastening implants to tissue which includes a helical coil, a torque member, and a key wire locking the two together against translational and rotational motion.
• FIG. 84 shows an implant which includes a helical coil in position in tissue prior to activation of the helical coil
• FIG. 85 shows an implant which includes a helical coil in position in tissue after activation of the helical coil
• FIG. 86 shows an implant with helical coils in place against a substantially straight section of tissue which is significantly longer than the implant itself.
• FIG. 87 shows the implant ofFIG. 86 with the same tissue ofFIG. 86 having been drawn into the concavities of the implant, bringing the ends of the tissue into approximation with the ends of the implant.
• FIG. 88 shows projected shapes of a model mitral annulus, that annulus treated with a flattening implant, and that annulus treated with an undulating implant.
• FIG. 89 illustrates an undulating implant that is assembled in place from sub-sections of the implant.
• FIG. 90 shows a subsection of an undulating implant folded to a reduced diameter for ease of delivery through a tube or tubular structure
• FIG. 91 shows a subsection of an undulating implant expanded to allow ease of anchor placement
• FIG. 92 shows a pair of subsections of an undulating implant arranged one in front of the other for simultaneous delivery through a tube or tubular structure.
• FIG. 93 shows an implant template that is placed in a substantially straight configuration, with deforming members in apposition to the implant template.
• FIG. 94 shows the implant template ofFIG. 93 having been deformed by the deforming members as they are moved distal relative to the anchor.
• FIG. 95 shows an array of subsections of an undulating implant pinned together via a pin extending through the two subsections with a locking cap to hold the two subsections together.
• FIG. 96 shows an array of subsections of an undulating implant having extensions that are substantially parallel to the anchor member which are held together with locking devices.
• FIG. 97 shows an array of subsections of an undulating with ends that are held together with locking devices.
• FIG. 98 shows a partial ring template with multiple anchors, the partial ring template being smaller than the mitral annulus, and the multiple anchors being used to draw the annulus towards the template.
• FIG. 99 shows a two-anchor segment with a convex profile for shaping the valve annulus
• FIG. 100 shows a template constructed from two two-anchor segments with convex profiles
• FIG. 101 shows an undulating template with a single undulation composed of straight segments aligned horizontally and vertically.
• FIG. 102 shows an undulating template with a single undulation composed of a combination of straight and curved segments aligned perpendicularly to each other.
• FIG. 103 shows an undulating template with a single undulation composed of a combination of straight and curved segments aligned at non-perpendicular angles to each other.
• FIG. 104 shows an undulating template with a single undulation composed of curved segments with the ends configured so that the tangent to the curved segment at the end is parallel to the tangent at the location where the tissue coupling mechanism is attached.
• FIG. 105 shows an undulating template with a single undulation composed of curved segments with the ends extending past the point at which the tangent to the curved segment is parallel to the tangent at the location where the tissue coupling mechanism is attached
• FIG. 106 shows an undulating template with a single undulation with a continuous non-circular shape.
• FIG. 107 shows an undulating template where the distance from the point where the tissue coupling mechanism is attached to the highest peaks of the body of the template is greater than the length of the tissue coupling mechanism
• FIG. 108 shows an undulating template where the distance from the point where the tissue coupling mechanism is attached to the highest peaks of the body of the template is less than the length of the tissue coupling mechanism
• FIG. 109 shows an undulating template with tissue held in place by a tissue coupling mechanism, causing the template to exert forces in a tensile manner normal to the original position of the tissue (via the tissue coupling mechanism) and in an inward manner, tangential to the original position of the tissue.
• FIG. 110 shows an undulating template with tissue held in place by a tissue coupling mechanism, causing the template to exert forces in a tensile manner normal to the original position of the tissue (via the tissue coupling mechanism) and in a compressive manner normal to the original position of the tissue at the peaks of the undulations.
• FIG. 111 shows an undulating template with tissue held in place by a tissue coupling mechanism, causing the template to exert forces in a tensile manner normal to the original position of the tissue (via the tissue coupling mechanism) and in a combined inward compressive manner, directed between normal and tangential directions to the original position of the tissue.
• FIG. 112 shows an undulating template with tissue held in place by a tissue coupling mechanism, causing the template to exert forces in a tensile manner normal to the original position of the tissue (via the tissue coupling mechanism) and in a combined inward compressive manner, directed between normal and tangential directions to the original position of the tissue.
• FIG. 113 shows an undulating template with stabilizing tissue coupling mechanisms at each end, in addition to the primary tissue coupling mechanism in the middle. Also shown are removable devices for placing and manipulating the tissue coupling mechanisms.
• FIG. 114 shows and undulating template with an additional stabilizing arm extending from the body, as well as stabilizing penetrating points.
• FIG. 115 shows an undulating template with the ends folded away from the attachment point of the tissue coupling mechanism to a delivery position, where the tissue coupling mechanism attachment allows the template to fold alongside the tissue coupling mechanism.
• FIG. 116 shows an undulating template in position adjacent to a mitral annulus in the untreated state.
• FIG. 117 shows an undulating template with a mitral annulus, where the tissue coupling mechanism has drawn the annulus tightly against the template. The original position of the annulus fromFIG. 116 is also shown.
• FIG. 118 illustrates a delivery device for placing an undulating template over a pre-anchor guide. The pre-anchor guide runs through a receiving slot in the delivery device.
• FIG. 119 shows percent area change for various templates implanted in-vivo.
• FIG. 120 shows percent circumference change for various templates implanted in-vivo.
• FIG. 121 shows percent minor axis change for various templates implanted in-vivo.
• FIG. 122 shows percent A-P (minor axis) reduction for various multi-wave templates implanted in excised porcine mitral annuli.
• FIG. 123 shows percent A-P (minor axis) reduction for various single-wave templates implanted in excised porcine mitral annuli.
• FIG. 124 shows a continuous template with one area of undulations.
• FIG. 125 shows a continuous template with two areas of undulations.
• FIG. 126 shows a continuous template with undulations on the entire circumference.
• FIG. 127 shows a template where the compression points form an angle with an anchor point.
• FIG. 128 shows a side view of a template where the compression points are offset to a different plane than the anchor point
• FIG. 129 shows a top view of a template where the compression points are offset to a different plane than the anchor point
• FIG. 130A shows a template in the preformed shape.
• FIG. 130B shows a template in a crimped or partially crimped configuration with both ends pressed toward the center.
• FIG. 130C shows a template in a crimped or partially crimped configuration with both ends rotated towards each other to a substantially circular shape.
• FIG. 131A shows a template with anchor, the template being in the preformed shape
• FIG. 131B shows a template with anchor, the template being constrained in a crimped state with the ends or wings of the template pulled proximally relative to the anchor.
• FIG. 132 shows a template, illustrating distance between ends, distance between apexes, width of concavity, and depth of concavity.
• FIG. 133A shows a template slidably coupled to an anchor control device, in position to move toward the anchor
• FIG. 133B shows the template, anchor, and anchor control device ofFIG. 133A, with the template coupled to the anchor by a template coupling mechanism.
DETAILED DESCRIPTION OF THE INVENTION
• The phrase “valve annulus” as used herein and in the claims means a ring-like tissue structure surrounding the opening at base of a heart valve that supports the valve's leaflets. For example, the annulus of the mitral valve, the tricuspid valve, the aortic valve, the pulmonary valve, venous valves and other annuluses of valves in the body. In the mitral valve, the annulus typically is a saddle-shaped structure that supports the leaflets of the mitral valve.
• The phrase “peripheral wall” as used herein and in the claims as applied to a valve annulus means a surface or portion of the tissue of the valve annulus, and/or a portion of the tissue adjacent to the valve annulus.
• “Concavity” as used herein and in the claims means a depression or well formed in a surface of the template. The concavity may comprise flat regions joined at angles, e.g. being rectilinear, but will more typically have a curved bottom portion joining a pair of generally straight and/or curved walls or legs. The curved bottom portion will typically span an arc of at least 45°, often at least 60°, usually at least 90°, typically at least 135°, and sometimes spanning a full 180°, with exemplary ranges from 45° to 180°, from 60° to 180°, from 60° to 135°, and from 90° to 135°. The concavities of the present invention will typically be symmetric having opposed walls or legs on each side of a central axis. In other cases, however, a concavity may be asymmetric with walls or legs on each side having unequal lengths and, in some cases, having only a single wall. Examples of concavities include the inner surface of a circle or sphere or other.
• “Convexity” as used herein and in the claims means a curved surface on the template like an exterior of a circle, parabola, ellipse, or the like. A convexity will typically be formed on a surface of the template on the side opposite to that of a concavity, and vice versa. Examples of convexities include the outer surface of a circle or sphere or other.
• As used herein and in the claims, an “implant” means an article or device that is introduced into and left in place in a patient's body by surgical methods, including open surgery, intravascular surgical methods, percutaneous surgical methods, and least invasive or other methods. For example, aortic valve replacement implant, coronary stent implant, or other types of implants.
• As shown inFIG. 1, theheart105, contains four major valves: the mitral orbicuspid valve101, thepulmonary valve102 with theRight Cusp102a,Left Cusp102b, andAnterior Cusp102c, theaortic valve103 with theNon-Coronary Cusp103a, theRight Coronary Cusp103b, and the Left Coronary Cusp130c, and thetricuspid valve104 with thePosterior leaflet104a, theAnterior Leaflet104b, and theSeptal Leaflet104c. Each valve has three leaflets, except for the mitral valve which has two.
• As shown inFIG. 2, themitral valve101 comprises amitral valve annulus201, and has ananterior leaflet203 with a first scallop (A1)203a, a second scallop (A2)203b, and a third scallop (A3)203c, and aposterior leaflet204 with a first scallop (P1)204a, a second scallop (P2)204b, and a third scallop (P3)204c, which join atcommissures202aand202b. Referring toFIG. 2, the septal aspect of thevalve206 is at the bottom of the figure, and the lateral aspect of thevalve205 is at the top.
• As shown inFIG. 3, themitral valve101 can enlarge, leaving a gap between the anterior203 and posterior204 leaflets. This gap prevents the valve from closing, allowing blood to return from the left ventricle to the left atrium, a condition referred to as MR or Functional Mitral Regurgitation, or FMR.
• As shown inFIG. 4, one object of this invention is to change the configuration of the valve to minimize or reduce MR. In this example, decreasing one dimension of a heart valve by increasing another using a stretching device (or implant). Referring toFIG. 4, the septal-lateral dimension of the mitral valve402a-bis decreased reducing the gap between the anterior and posterior valve leaflets by increasing the distance between the commissures, moving them in the approximate directions ofarrows401aand401b. A decrease in the gap between the anterior and posterior leaflets may also be achieved by stretching locations adjacent to the annulus but not necessarily adjacent to the commissures, at an offset angle to the septal-lateral direction of the valve and stretching sufficiently to achieve the desired valve configuration and/or gap dimensions in the lateral septal-lateral direction.
• As shown inFIG. 5A, one example of a device to accomplish the valve stretching (or reshaping) in accordance with this invention is an arch501 of resilient material such as stainless steel, shape memory alloys such as nitinol, or spring material, with anchoringelements502aand502bto interact with or engage the commissures of the valve and stretch them. The material of the arch501 may be super-elastic or shape memory material, in one example nitinol, hardened metal material, in one example hardened stainless steel, or a deformable metal which can be shaped and adjusted during deployment, in one example annealed cobalt chromium, or a composite material designed to achieve the required structural properties.
• As shown inFIG. 5B, a further example of a device to accomplish the valve stretching (or reshaping) in accordance with this invention is apartial ring503 of resilient material such as stainless steel, shape memory alloys such as nitinol, or spring material, with ananchoring feature504 and ends withbarbs505aand505bto interact with or engage the valve annulus. The material of thepartial ring503 may be super-elastic or shape memory material, in one example nitinol, hardened metal material, in one example hardened stainless steel, or a deformable metal which can be shaped and adjusted during deployment, in one example annealed cobalt chromium, or a composite material designed to achieve the required structural properties. Theanchoring feature504 and ends withbarbs505aand505bmay apply opposing loads to the annulus, in one example pushing the ends withbarbs505aand505boutward while pulling theanchoring feature504 inward.
• FIG. 6 shows thepartial ring503 in place in themitral valve101. During delivery, a flexible tension member (not shown) may be employed to hold the anchor points at a separation distance that will allow easy placement relative to the valve annulus in its native state. Releasing the flexible tension member will allow the stretching member to move the anchor points farther apart, affecting the desired change in the valve annulus such as reducing a gap between the anterior and posterior leaflets of the valve. The device may be configured to have apartial ring503 substantially contouring to annulus of the valve or have a different shape configuration (not shown). The devicepartial ring503 may be in contact with annulus of the valve or other valve components, or may be coupled to the annulus or other valve components through one or more fixing elements (not shown) along the length of the device in one or more locations. In one example, the fixing element (not shown) would couple to thepartial ring503 through theanchoring feature504. Alternatively, the devicepartial ring503 may be coupled to one or more locations in the atrium, above the valve, or coupled to locations in the ventricle, below the valve, along the length of the devicepartial ring503 in one or more locations. The device may be a permanent implant, wherein the device is left in the body. The device may be a removable device after stretching the valve in one or more dimensions and reduce the valve in other one or more dimensions, coupling (holding together) the stretched portion of the valve using clips, sutures or the like, and removing the stretching device after achieving minimal to no gap between the anterior and posterior leaflets. The implant may also be configured to stretch the valve in one or more directions for a period of time ranging from 1 month to 1 year, preferably ranging from 3 months to 6 months, and then is configured to have diminished or reduced stretching force. Typically, such implant is utilized when the annulus or heart remodels to the new valve configuration and continued stretching may not be needed. The material may be configured to fatigue over time, configured to have one or more separation regions forming one or more discontinuities in the implant along503,505a, or505bpath of the implant, or other means. The device may have a variety of shapes such as round, half circle, square, rectangle, elliptical, or other shapes. The cross-sectional area of the device ranges from 0.003 inches to 0.07 inches. The device may have constant or variable thickness, width, or dimensions along its length or at the anchoringelements505aand505b. The device may have a variety of shapes or geometries to stretch the valve (annulus) across a direction while reducing the valve (annulus) dimensions across a different direction, typically across a perpendicular direction to the stretching direction, but can also be at other offset angles to the stretching direction. The device may be a single element having a straight, arched, zig-zag, serpentine, or other structure.
• FIG. 7 shows an alternative example of the present invention, where the arch701 is attached to themitral annulus201 by penetratingbarbed points702aand702b.
• FIG. 8 shows another alternative example of the present invention, where the arch801 is attached to themitral annulus201 byspiral anchors802aand802b. The spiral anchors802aand802bmay be constructed of the same material asarch801, or a different material. In one example, it may be advantageous for the spiral anchors802aand802bto be constructed of hardened stainless steel, while the arch801 is constructed of super-elastic nitinol.
• FIG. 9 shows another alternative example of the present invention, where the arch901 presses outward on themitral annulus201 acting throughpads902aand902b. Thepads902aand902bdistribute the force thearc901 exerts on themitral valve annulus201. Thepads902aand902bmay be anchored to the annulus using any of a number of anchoring techniques, or they may simply rest against the junction between themitral valve annulus201 and the wall of the left atrium (not shown). Thepads902aand902bmay be covered in a material that encourages tissue ingrowth. Thepads902aand902bmay be constructed of the same material as the arch, or of a different material to achieve the structural properties required. Thepads902aand902bmay be symmetric to each other to allow the device to be placed in two different orientations without loss of function, or they may be asymmetric to re-shape the valve annulus to different radii in the area of each pad.
• An arch of resilient material is only one way to accomplish the valve re-shaping of the present invention.FIG. 10 shows an alternate, straight stretching member in a turnbuckle configuration which includes arotating sleeve1001 with two internal threads of opposite chirality (left and right handed), a first threadedrod1002 with andanchor1004aand with threads cut in a first chirality (in one example, right hand threads), and a second threadedrod1003 with ananchor1004band with threads cut in a second chirality (in one example, left handed threads). Rotating thesleeve1001 moves the threaded rods toward or away from each other, thus adjusting the length of the stretching member and effecting the desired change in valve shape.
• FIG. 11 illustrates another example of a stretching member, this one based on aratchet member1103 containing a ratchet and anchored1104bthe valve annulus andpawl member1102 containing apawl1101 and anchored to thevalve annulus1104ato hold the stretching member assembly in an extended length, affecting the desired change in valve shape.
• FIG. 12 illustrates another example of a stretching member, based on acompression spring1201 anchored at theends1202aand1202b. The compression spring is biased to a free length longer than the distance between valve commissures, stretching the valve in the direction of application and affecting the desired change in valve shape. The compression spring as shown is a helical coil, but other compressible structures may be utilized. Examples of suitable structures include an expanding lattice or net formed of closed cells, a series of sinusoidal curves, a braid of resilient material, a stack of Bellville washers, or other compressible structures know to the art.
• FIG. 13 illustrates another spring based stretching member, including aspring enclosure cylinder1301 withanchor1304a, apiston1302 withanchor1304b, and apin1305 that holds the assembly in a first length for placement. Removing the pin by pulling it out1303 allows the spring to extend, affecting the desired change in valve shape.
• As shown inFIG. 14, the spring based stretching member ofFIG. 13 contains acompression spring1401 that is at least partially enclosed incylinder1301.
• FIG. 15 illustrates a stretching member based on a crossedlinkage1501 withanchors1504aand1504b. Turning1502 theadjustment screw1503 actuates the linkage to move the anchor points closer together or farther apart as required to affect the desired change in valve shape. While shown as a crossed linkage, other structures may be used. In one example, a closed cell structure, in a second example a repeating sinusoidal pattern structure, in a third example a spiral structure, or braid structure or other structures known to the art may be employed.
• FIG. 16 illustrates atorsion spring1601 based stretching member. Thetorsion spring1601 is attached toanchors1604aand1604band is held in a first position by aretention spring1602. Theretention spring1602 can be removed by twisting1603, allowing thetorsion spring1601 to move to a second position, affecting the desired change in valve shape.
• As shown inFIG. 17, a valve shaping device1701 (dashed line) can be placed along the annulus, conforming approximately to the shape of the annulus and/or the left atrial wall.
• FIG. 18A shows examples ofvalve shaping device1701 which may be placed partially above and partially below the valve annulus (1801), or completely on one side of the annulus (1802). Such examples ofvalve shaping device1701 may include an adjusting mechanism1803, which employs any of a wide array of adjusting mechanisms including but not limited to linkages, screws, turnbuckles, or flexible tension members (sutures) with appropriate locking devices or knots. The adjustment device may be accessible from the inner aspect of thevalve shaping device1701 as shown in1803cand may be angled relative to the body of thevalve shaping device1701 as shown in1803dfor ease of access to the adjustment mechanism. While the stent structure is not shown, a variety of stent structures may be used. In one example, a closed cell structure, in a second example a repeating sinusoidal pattern structure, in a third example a spiral structure, or braid structure or other structures known to the art may be employed. A variety of stent materials may be employed, including stainless steel, cobalt chromium, platinum, or super elastic Nitinol.
• FIG. 18B shows an example of avalve shaping device1803ewith has two tissue engagement portions, and an elongated profile. This device configuration is a continuous loop without ends.
• FIG. 18C shows and example of avalve shaping device1806 which is constructed of an elongate member whose ends are joined into a single end.
• FIG. 19 shows avalve shaping ring1901 of resilient material which alters the shape of the atrium andvalve annulus201. Thevalve shaping ring1901 may include anchors in the area of the valve commissures or may act by pressing outward against the wall of the atrium in the area of the valve commissures. Thevalve shaping ring1901 preferentially includes a coating or outer sleeve to encourage tissue ingrowth and/or encapsulation.
• FIG. 20 shows a valve shaping c-ring2001 of resilient material which alters the shape of the atrium andvalve annulus201, which includes adiscontinuity2002. The discontinuity allows for re-shaping the ring for easier delivery to the valve site. The discontinuity may also include an adjustment mechanism. In one example, a flexible tension member may connect the two ends of the c-ring, limiting outward pressure. By adjusting the length of this flexible tension member, the level of re-shaping effect on the valve can be adjusted. The valve shaping c-ring2001 may include anchors in the area of the valve commissures or may act by pressing outward against the wall of the atrium in the area of the valve commissures. The valve shaping c-ring2001 preferentially includes a coating or outer sleeve to encourage tissue ingrowth and/or encapsulation.
• The valve reshaping of the present invention can be accomplished by acting independently on different areas of the valve. As shown inFIG. 21, tensioning members2501aand2501bat locations around the valve annulus can create similar reshaping. Referring toFIG. 21,tensioning member2105aincludes ananchoring pledget2101a, aflexible tension member2102a, a slidingpledget2103a, and anadjuster2104a. Theadjuster2104acan be used to adjust the position of the sliding pledget along theflexible tension member2102a, creating an area of compressed tissue between thepledget2101aand the slidingpledget2103a, and affecting the desired change to the valve shape. Examples of the mechanism used for theadjuster2104ainclude screw threads, suture locking devices, knots, glue, heat stakes and/or crimp tubes. Theadjuster2104amay be built in to the slidingpledget2103a, or a separate part. The adjuster may be partially or fully included in the removable deployment device. This example of the present invention may be advantageous in valves with three leaflets, such as theaortic valve103,tricuspid valve104, orpulmonary valve102.
• FIG. 22 showstorsion spring2201aand2201bbased reshaping devices which includeanchors2202a,2202b,2203a, and2203b. The torsion spring acts to bring the anchors closer together to affect the desired change in valve shape. These torsion springs2201aand2201bmay be held in a delivery position by a removable mechanism as shown inFIG. 16.
• The reshaping effect may also be achieved through application of devices external to the atrium. As shown inFIG. 23, a stent-like device2302 can be placed in thecoronary sinus2301 and anchored to the wall of the heart adjacent to the mitral annulus by twoanchors2303 and2304. The deployed shape of the stent is significantly straighter than the path of the coronary sinus, creating an inward pressure on thelateral aspect205 of the valve annulus.
• The reshaping members as part of this present invention may be temporary, removable devices to aid in placement of permanent clip or anchoring members. As shown inFIG. 24, the stretchingmember2401 represented by a dashed line, may be removed after placingpermanent clips2402aand2402b. Thepermanent clips2402aand2402bmaintain the desired change in valve shape after the stretchingmember2401 has been removed.
• While much of the present invention has described stretching members targeted at affecting the position of two points around a valve annulus, it may be advantageous to combine two or more such members to affect three or more points along the valve annulus. As shown inFIG. 25, the three-point shaping member2501 is anchored around the valve annulus with threeanchors2502a,2502b, and2502c. The combined directed motion can bring the anchor points2502a-ctowards a different triangular shape than their initial positions, or towards a straight line as required to affect the desired change in valve shape.
• While most figures in this disclosure indicate a stretching member situated approximately in line with the valve commissures, there are other stretching directions which may be advantageous in some situations.FIG. 26 shows thecommissural line position2601, asecond position2603 located at anangle2604 clockwise from the commissural line position and athird position2605 located at anangle2605 counterclockwise from the commissural line position. It may be advantageous for theangles2604 and2605 to be within 45 degrees of thecommissural line position2601. In a further example, it may also be advantageous for theangles2604 and2605 to be within 60 degrees of thecommissural line position2601.
• The effect of the stretching member on the valve will be acute, reshaping the valve and restoring function during the implantation procedure. Configurations of the stretching member which apply a force that changes over time may be advantageous. The force may decrease, to prevent long term valve remodeling or increase, to accommodate for further expansion of the heart affecting valve function.FIG. 27 shows a stretchingmember2702 with a time-alterable region2701 and anchors2703aand2703b. The time alterable region may function via bioresorbable components that alter applied force by degrading, by fatigue elements which disconnect after exposure to a period of cyclic loading, or by other mechanisms known to the art.
• As shown inFIG. 28, thediscontinuity region2701 may separate the stretchingmember2702 into two or more detached components (2801), or may leave the stretching member as one continuous component with a more flexible structural shape (2802).
• The present invention may also be applied advantageously to a substantially round valve with three leaflets, such as thepulmonary valve102, theaortic valve103, and/or thetricuspid valve104. As shown inFIG. 29A, around annulus2901 can be shaped to a triangular annulus2902 by moving three anchor points outward (2903). This results in substantialinward motion2904 in segments of the valve annulus. These segments of the valve annulus which move inward may correspond to leaflets in an enlarged valve, or to commissures of a valve with stenosis.
• FIG. 29B illustrates an example of avalve shaping device2905 with a substantially circular shape, and three tissue engagement points arranged to shape a round annulus towards a more triangular shape.
• FIG. 30 illustrates the mitral valve of a pig heart, with much of the left atrium removed for viewing.
• FIG. 31 illustrates the mitral valve of a pig heart with a stretchingmember3101 in place, creating an elongation in the commissural linear direction and a reduction in size in the septal-lateral direction. In this configuration, the stretchingmember3101 arches over the plane of the mitral valve, and may rest against the roof of the atrium, not shown.
• FIG. 32 shows ahelical member3205 incorporating a T-handle3203. The T-handle3203 can be used to twist or untwist thehelical member3205 when it is held in theengagement slot3202 oftorsion tube3201 through tension on thesnare3204. One example of the use of this device would be ahelical member3205 with a penetratingtip3206 used to anchor a device (not shown) to tissue. Thehelical member3205 may also take the form of a screw thread, and the torsion used to rotate it relative to an engaging thread (not shown), which could adjust the force or displacement provided by the stretching member. In addition, the T-handle3203 may remain in place in the implant, to be accessed via snare to adjust or remove the implant peri-procedurally, or at a subsequent operative procedure. Thetorsion tube3201 can interact remotely with a manual handle, or a powered remote actuator.
• Accordingly, it is to be understood that the examples of the invention herein described are merely illustrative of the application of the principles of the invention. Reference herein to details of the illustrated examples is not intended to limit the scope of the claims, which themselves recite those features regarded as essential to the invention.
• FIGS. 33 to 47 illustrate different adjustable elements, which may be used to adjust a stretching member such as that described in with a closed cell structure, repeating sinusoidal pattern structure, spiral structure, braid structure or other structures known to the art. Each adjustable element can draw the stretching member closer together and or farther apart as required to affect the desired change in valve shape.
• FIG. 33 shows twostraight arms3301aand3301bconnected toadjacent cells3302aand3302bof the stretchingmember3300. As shown, the ends of two arms3301enter holes3303 located at the end of these cells3302 such that it allows the arms to pivot at these points of connection. Onearm3301ais also inserted into ahole3304 located on theother arm3301band is free to pivot. Both arms haveadditional holes3305aand3305bthat allow a spring orspiral element3306 to core through. The spring orspiral element3306 prevents the arms from opening. After deployment of the stretchingmember3300, thespring3306 is turned such that it is released from theholes3305aand3305bof the twoarms3301aand3301b. This allows thearms3301aand3301bto pivot and draws thestretchable member3300 farther apart.
• FIG. 34 shows a conical or taperedspring3401 cores around the arms of anunexpanded cell3402 of thestretchable member3400. Thespring3401 has aloop3403 on top such that upon turning in clockwise or counterclockwise direction, it will narrow or widen theunexpanded cell3402, and draw the stretchingmember3400 closer together and or farther apart after initial deployment.
• FIG. 35A shows twostraight arms3501aand3501bconnected to adjacent cells (not shown) to the stretching member similar toFIG. 33 where the point of connections between thearms3501aand3501band the holes on the cells allow pivoting of thearms3501aand3501b. Thearms3501aand3501bcan pivot at the point of theirintersection3502. One or more torsion springs3503amade from ductile plastic, metal or alloy serve as a gripping mechanism to prevents thearms3501aand3501bfrom pivoting at the point ofintersection3502 by application ofcompressive forces3504aand3504b.FIG. 35B illustrates two extendingarms3504aand3504bofFIG. 35A from the end of thetorsion spring3503agripping thearms3501aand3501btogether. After accessing thehole3505 of thetorsion spring3503awith aguide wire3506, a deflatedballoon3507 is inserted over theguide wire3506 and into thehole3505. This balloon is inflated and opens the torsion spring, thereby opening thegrips3504aand3504band releasing thearms3501aand3501band allowing them to pivot at the point ofintersection3502. This allows the stretchable member3500 to draw closer if thegrips3504aand3504bapplied a force from3504a. It allows the stretchable member3500 to become farther apart when the force is applied from3504b.
• FIG. 36A shows two ‘FIG. 8’ring element3601aand3601baround thefixed crowns3602aand3602band afree crown3603 before deployment. After deployment of thestretchable member3600, the fixedcrown3602aand3602bremain the same while thefree crown3603 opens.FIG. 36B illustrates that theleft ring elements3601acan be moved such that it becomes closer to the valley of the fixedcrown3602aafter deployment, thereby, allowing thestretchable member3600 to become farther apart.
• FIG. 37 shows different screw or spring drivenadjustable elements3701,3702, and3703 that fix to one ormore cells3704 of thestretchable member3700. By rotating the screw or spring with alever handle3705,ring3706, or other means, thenut block3707,3708, and3709 withslots3710 orholes3711 and3712, which encircles the twoarms3713 of thecell3704 and matches the pitch of the screw orspring3701,3702, and3703, moves along the length of thestruts3713 of thecell3704. As thenut block3707,3708 and3709 moves toward the middle of thecell3704, it draws it together and spread the stretchingmember3700 closer. As it moves towards the crown by rotating the screw orspring3701,3702, and3703, it draws thecell3704 apart, drawing the stretchingmember3700 farther apart after initial deployment.
• FIG. 38 shows aspring3801 that surrounds acell3802 of the stretchingmember3800. It has alever handle3803 that can be used to turn thespring3801. Thestruts3804 of the cell havelinear teeth3805 that match the pitch of the spring. During deployment, it fixes thecell3802 while those adjacent freelyopenable cells3806 that are not fixed with this spring open to their maximum predetermined size. As thespring3801 is rotated with thelever handle3803, it moves toward the middle of thecell3802, it draws it together and spread the stretchingmember3800 closer. As it moves towards the crown by rotating thespring3801, it draws thecell3802 apart, drawing the stretchingmember3800 farther apart after initial deployment. When removed, it can let thecell3802 open freely to the opening of the maximum predetermined size.
• FIG. 39 illustrates the use ofshape memory cells3901 that are placed adjacent tosuperelastic cells3902 of thestretchable member3900. Theshape memory cell3901 remains closed before and after deployment of thestretchable member3900. When heated to a temperature above the transformation temperature of theshape memory material3903, theshape memory cell3901 widens to its trained size and allows the stretchingmember3900 to become father apart.
• FIG. 40 illustrates the use ofshape memory cells4001 that are placed adjacent tosuperelastic cells4002 of thestretchable member4000. Theshape memory cell4001 remains open before and after deployment of thestretchable member4000. When heated to a temperature above the transformation temperature of theshape memory material4003, theshape memory cell4001 narrows to its trained size and allows the stretchingmember4000 to become closer.
• FIG. 41 illustrates the use of shape memory wire orarm4101 that connects to thestruts4102 of acell4103 of thestretchable member4100. This wire orarm4101 remains the same distance before and after deployment of thestretchable member4100. After heating to a temperature above the transformation temperature of theshape memory material4104, it narrows or widens (not shown) and draws the stretchingmember4100 to closer or farther apart.
• FIG. 42 shows twoarm pivoting element4201 similar toFIG. 35A that are connected toadjacent cells4202 of thestretchable member4200. Awire4204 is attached to the point ofintersection4203 between thearms4201. After deployment of thestretchable member4200, thewire4204 can be latched with ahook4205 and twisted4206 to compress the point of intersection, which causes the arms to pivot and open. This results in drawing thestretchable member4200 to farther apart. The wire can also be arranged to close the arms, which results in drawing thestretchable member4200 closer.
• FIG. 43A shows twoarm pivoting element4301 similar toFIG. 35A that is connected toadjacent cells4302 of the stretchable member4300. After deployment of thestretchable member4200, awire4303 with twogrips4304 and4305 are secured to the arms at the point ofintersection4306. The wire also has aloop4306 at one end. Aguidewire4307 can be used to locate inside of theloop4306. Theballoon4308 of a catheter can then be guided to the inside of the loop with this guidewire. Upon balloon expansion, the loop enlarges, and the arm at the point of intersection is compressed or released, causing the arms to pivot and open or closed. This results in drawing the stretchable member4300 farther apart.FIG. 43B shows thewire4303 at an alternate fixation point to close thearms4301 when theballoon4308 is expanded, which results in drawing the stretchable member4300 closer.
• FIG. 44 illustrates twoarms4401 forming apivoting element4402 similar toFIG. 35A that is connected to adjacent cells (not shown) of the stretchable member4400. Two lead screws orsprings4403 and4404, each with two ball nuts,4405,4406,4407, and4408, compress thearms4401 together at the point ofintersection4409. Each lead screw or spring is attached to alever handle4410. When the lead screws orsprings4403 and4404 are rotated with one or bothhandles4410, thearms4401 pivot to open or close thepivoting element4402. This mechanism tightens or loosen theelement4402 such that it causes the stretchable member4400 to draw closer together or farther apart.
• FIG. 45A illustrates acoated implant4500 having acore4501 and a first coating layer4502 bonded to thecore4501. This coating can alter the surface properties of the implant, act as a drug delivery matrix, or provide a media for tissue ingrowth. It may also be advantageous to add asecond coating4503 on top of the first coating4502 if one coating alone cannot provide all of the desired properties. In one example, the first layer of coating4502 may bond well to thecore4501 and to thesecond coating layer4503, and thesecond coating layer4503 would alter the surface properties of the implant, act as a drug delivery matrix, or as a media for tissue ingrowth. Additional layers of coatings are conceivable. An example of a three-layer coating system would have a first layer (not shown) of corrosion protective material (metal plating, an oxide layer, etc.), and the twoadditional coating4502 and4503 as described above.
• FIG. 45B illustrates a variety of alternate cross-sectional shapes, including circular4504, semi-circular4505, oval or elliptical4506, pinched rounded4507, rectangular4508, square4509, crescent shaped4510, tubular4511,hourglass4512, or H-beam shaped4513. Other cross-sectional shapes are also known to the art. Cross sectional shapes may be applied to any portion or portions of the stretching member to achieve desired structural properties, tissue interaction properties, shapes in bending, interaction with delivery and/or removal devices, interaction with tissue engagement mechanisms, interaction with additional valve shaping devices, interaction with coatings, drug release dynamics, or other properties of the valve shaping device.
• FIG. 46 illustrates acam drive element4601 that is embedded between two overlappingadjacent cells4602 and4603 of the stretchable member4600. It has alever handle4604 that rotates it. When thecam4601 is rotated in clockwise or counter-clockwise direction, the distance between theadjacent cells4602 and4603 widens (not shown) or narrows (as shown) and results in drawing the stretchable member4600 farther apart or closer.
• FIG. 47 illustrates twoarms4701 forming apivoting element4702 similar toFIG. 35A that is connected to adjacent cells (not shown) of the stretchable member4700. Aconical spring4703 is wound over thearms4701 and has alever handle4704. When thespring4703 is rotated clockwise or counter-clockwise, the arms pivot to close or open, causing the stretchable member4700 to draw closer together or farther apart.
• FIG. 48 shows a stretching member with twoanchor points4801aand4801b,tissue support members4802aand4802b, a primarycurved section4804 generally following the curvature of the annulus, and tworeverse curve sections4803aand4803bcurved in a different direction than the primarycurved section4804. The angular deflection of the primarycurved section4804 and the two secondarycurved sections4803aand4803bpartially offset, maintaining a more constant angle under flexure between the twoanchor points4801aand4801bandtissue support members4802aand4802bthan with a single curved section.
• FIG. 49 shows oneend4901 of a stretching member configured to interact with tissue featuring abarb4902 to prevent inadvertent loss of tissue contact with theend4901 of the stretching member during device placement. Thebarb4902 may be present on one end only of the stretching member, or on two or more ends as needed.FIG. 49 additionally shows aplacement hook4903 which interacts with a placement device (not shown) by trapping a segment of the placement device between theplacement hook4903 and the main body of the stretching member to control position of the stretching member during placement.
• FIG. 50 shows a tissue placating end of a stretchingmember5001 consisting of threetines5002a,5002b, and5003. As shown inFIG. 50A,tines5002aand5002bare approximately coplanar, whiletine5003 has acoplanar section5003aand anon-coplanar section5003b.FIG. 50B shows atissue member5004 in position adjacent to thenon-coplanar section5003bso that it is approximately un-deflected by the threetines5002a,5002b, and5003. As the stretching member applies force to the surrounding tissue, thetissue member5004 may be moved proximally along the tines to aplicated configuration5005 as it approaches thecoplanar section5003 of the tines. This plication results in an overall shortening of thetissue member5004 in addition to the stretching effect of the stretchingmember5001. Thetines5002a,5002b, and5003 as shown have non-penetrating ends, but could be offered in an array of other ends common to the art, examples including sharp penetrating ends, barbed anchor ends, or helical anchor ends.
• FIG. 51 illustrates one end of a stretchingmember5101 with two divergingtines5102aand5102b.FIG. 51A shows the two divergingtines5102aand5102bwith tissue penetrating ends in proximity to thefree tissue member5103.FIG. 51B shows the two diverging tines having entered penetratedtissue member5104. As the penetrated tissue member moves proximally up the divergingtines5102aand5102b, the angle between the tines compresses the tissue member causing bunching5105, resulting in an overall shortening of the penetratedtissue member5104, in addition to the stretching effect of the stretchingmember5101. The divergingtines5102aand5102bare shown with tissue penetrating ends, but could be offered in an array of other ends known to the art, examples including rounded ends, barbed anchor ends, or helical anchor ends.
• FIG. 52 illustrates a stretchingmember5201 having awire attachment point5202 which releasably engages with awire end5203 which is attached towire5204. Thewire5204 would enhance control of the position of the stretchingmember5201 during delivery and verification of position and appropriate function of the stretchingmember5201. If the results of placement of the stretchingmember5201 are acceptable, thewire5204 andwire end5203 can be disengaged from thewire attachment point5202 and removed. If the results of placement are not acceptable, the wire can be used to retrieve the stretchingmember5201. A number of suitable releasable attachment mechanisms exist in the art which would be applicable to this device configuration. Examples of releasable attachment mechanisms include screws, snap fits, and interference fits. Thewire5204 may also be anchored to the valve annulus prior to introduction of the stretchingmember5201, and the stretchingmember5201 advanced over the wire into position, where it attaches to the anchor.
• FIG. 53 illustrates a stretchingmember5301 with aretrieval device interface5302 arranged between the ends of the stretchingmember5301. A retrieval device (not shown) could attach to thisretrieval device interface5302 in order to retrieve a stretchingmember5301. As shown, theretrieval device interface5302 is a simple T-handle that could be accessed with a snare, but numerous appropriate mechanisms are documented in the art. Examples of such mechanisms include magnetic interfaces, threaded fasteners, ball and socket joints, wire snares, latches, or hooks and eyes.
• FIG. 54 shows a stretchingmember5401 withends5402aand5402b, and anattachment point5403 arranged between the two ends5402aand5402b. Theattachment point5403 includes areleasable placement feature5404 which engages with an attachment device (not shown) to facilitate attachment of theattachment point5403 to the target tissue. As shown, theattachment point5403 consists of a helical anchor, and thereleasable placement feature5404 is a T-handle, but other configurations known to the art may be advantageous. Examples of alternate configurations for theattachment point5403 include tissue penetrating points with or without barbs, tissue penetrating hooks with or without barbs, staples, or clips. Examples of alternate configurations for the releasable placement feature include magnetic interfaces, threaded fasteners, ball and socket joints, wire snares, or hooks and eyes.
• FIG. 55 illustrates a valve shaping C-ring5501 with twoends5502 and ananchor point5503 arranged in the span between the two ends of the valve shaping C-ring5501. Theanchor point5503 has areleasable placement feature5504 which engages with an attachment device (not shown) to facilitate attachment of theanchor point5503 to the target tissue. As shown, theanchor point5503 consists of a helical anchor, and thereleasable placement feature5504 is a T-handle, but other configurations known to the art may be advantageous. Examples of alternate configurations for theanchor point5503 include tissue penetrating points with or without barbs, tissue penetrating hooks with or without barbs, staples, or clips. Examples of alternate configurations for the releasable placement feature include magnetic interfaces, threaded fasteners, ball and socket joints, wire snares, or hooks and eyes.
• FIG. 56 shows a stretchingmember5601 with three branchedattachment points5602a,5602b, and5602carranged to create a wider variety of forces among the attachment points than is possible with two attachment points. In principle, all forces created by two attachment points must be substantially along the line between those points and therefore aligned substantially with a diameter of the valve, while three attachment points allow applied forces to have a tangential component as well. In one example, the tangential component applied toattachment points5602aand5602cmay have substantial component in the direction of the aortic valve (down the page as shown inFIG. 56), which is balanced by an opposed force applied atanchor point5602b. Other combinations of force vectors may be advantageous. In one example, a substantial stretching force created between two attachment points and a tension at the third, the tension at the third point creating a local reduction of diameter in the valve annulus.
• FIG. 57 shows a stretchingmember5701 with fourbranched attachment points5702a,5702b,5702c, and5702darranged to create a wider variety of forces among the attachment points than is possible with two or three attachment points. In one example, the attachment points may create an in-plane force couple, pushingattachment point5702aaway from the center of the valve while pullingattachment point5702btoward the center of the valve, creating a twisting or torsional moment balanced by an opposed couple on the other end of the stretchingmember5701, in particular pushingattachment point5702caway from the center of the valve, while pullingattachment point5702dtoward the center of the valve. Other combinations of force vectors may be advantageous.
• FIG. 58A shows a stretchingmember5801 with fourbranched attachment points5802a,5802b,5803a, and5803barranged to apply a torque between two pairs of attachment points. In one example,attachment point5802aapply an upstream force on the valve annulus, whileattachment point5802bapplies a downstream force on the valve annulus, creating a torque at one of the stretchingmember5801 which is counterbalanced by a torque applied at the other end, withattachment point5803aapplying a downstream force on the valve annulus, and5803bapplying an upstream force on the valve annulus. In this example, upstream and downstream refer to the direction of flow through the valve. The net effect of these applied loads could deflect the valve annulus out of plane, in one example to restore or enhance a saddle shape present in healthy mitral valves.
• FIG. 58B shows a further example of the device inFIG. 58A, in perspective view. In this example, torsion between the two ends is applied by atwisted torsion bar5805, resulting in a counter-clockwise twist on theannulus5804 at afirst end5806, and a clockwise twist on theannulus5804 at asecond end5807. Each twist acts to shorten the annulus in the area of the applied twist. Further, each twist moves the annulus out of plane, potentially reducing flattening of the annulus and thereby improving valvular function.
• FIG. 59A illustrates amitral valve5902 with a saddle shape and a stretchingmember5901 applied at an out of plane bend in the valve annulus, theends5903aand5903bof the stretchingmember5901 having a corresponding out of plane curvature. In one example, the out of plane curvature of the ends of the stretching member enhances or maintains the saddle shape of themitral valve5902.
• FIG. 59B illustrates a flattened mitral valve with aposterior aspect5908 and a shapingmember5904 applied to one area of the annulus. The shapingmember5904 has four attachment points,5905a,5905b.5906a, and5906b, and anattachment feature5907 arranged to rest at a distance from theposterior aspect5908 of the mitral valve annulus. The shaping member may additionally present an inward or outward force between the two ends, or match the native dimensions of the annulus and apply little or no inward or outward forces. Drawing theattachment feature5907 toward theposterior aspect5908 of the mitral annulus, as shown inFIG. 59C, causes upward force on the attachment points5905aand5905b, and downward force on the attachment points5906aand5906b, restoring, partially restoring, or enhancing a saddle shaped geometry to the mitral annulus. Drawing theattachment feature5907 is only one example of the present invention. Attaching theattachment feature5907 to other points within the atrium and ventricle may have advantageous effects. Examples of other attachment points include the atrial septum and the wall of the atrium adjacent to the coronary sinus.
• FIGS. 60A-I illustrate a variety of valve shaping devices shown in place above the mitral valve.
• FIG. 60A shows avalve shaping device6001 with a single stretching member in a substantially straight position.
• FIG. 60B shows avalve shaping device6002 with a single stretching member in a curved position.
• FIG. 60C shows a valve shaping device withdual stretching members6003 and6005, separated by adistance6004, curved in substantially the same direction.
• FIG. 60D shows a valve shaping device withdual stretching members6006 and6007, curved in substantially opposite directions.
• FIG. 60E shows avalve shaping device6008 with a single stretching member in a substantially straight position, having at least onesplit end feature6009, the split end feature having two distinct tissue engagement points. These distinct tissue engagement points can apply loads in different directions to the tissue, resulting in an applied moment, and/or an applied force with components that act out of the plane of the mitral valve.
• FIG. 60F shows avalve shaping device6010 with a single stretching member in a substantially straight position, arranged at an angle to the valve commissures, the angle being counterclockwise as viewed from the atrium.
• FIG. 60G shows avalve shaping device6011 with a single stretching member in a substantially straight position, arranged at an angle to the valve commissures, the angle being clockwise as viewed from the atrium.
• FIG. 60H shows avalve shaping device6012 with a single stretching member in a substantially straight position, having three tissue engagement features6012a,6012b, and6012carranged on the same side of the body of the valve shaping device.
• FIG. 60I shows avalve shaping device6013 with a single stretching member in a substantially straight position, having three tissue engagement features6013a,6013b, and6013carranged on different sides of the body of the valve shaping device.
• FIGS. 61A through 61C illustrate a variety of functional diagrams of valve shaping devices of the present invention.
• FIG. 61A shows a device placed in acurved configuration6101, which straightens6102 as it engages with tissue, stretching tissue further6103 until the shaping device is essentially straight6104. Throughout the motion, the ends of the shaping device move farther apart, and the crown of the bend moves closer to a line drawn between the two ends, until it substantially reaches that line. In one example, the ends of the tissue shaping device are engaged with the target tissue. In a further example, both the ends of the tissue shaping device, and one or more points along the span of the tissue shaping device engage with the target tissue.
• FIG. 61B shows a device placed in acurved configuration6105, which straightens6106 as it engages with tissue, stretching6107 until the tissue forces prevent further straightening, and the shaping device retains a substantially curved shape. Throughout the motion, the ends of the shaping device move farther apart, and the crown of the bend moves closer to a line drawn between the two ends, until it substantially reaches that line. In one example, the ends of the tissue shaping device are engaged with the target tissue. In a further example, both the ends of the tissue shaping device, and one or more points along the span of the tissue shaping device engage with the target tissue.
• FIG. 61C shows a device placed in acurved configuration6108, which flattens6109 on the top of the arch as it engages with tissue, providing outward force on the tissue while the ends of the tissue shaping device exhibit a reduced degree of rotation relative to their initial angles relative to the tissue. Throughout the motion, the ends of the shaping device move farther apart, and the crown of the bend flattens. In one example, the ends of the tissue shaping device are engaged with the target tissue. In a further example, both the ends of the tissue shaping device, and one or more points along the span of the tissue shaping device engage with the target tissue.
• FIG. 62 shows an asymmetrical tissue shaping device, with a moreflexible side6203 and astiffer side6202. The tissue shaping device expands in an asymmetrical manner from afirst position6201 to asecond position6204 where the ends have moved relative to one another. In one example, the ends of the tissue shaping device are engaged with the target tissue. In a further example, both the ends of the tissue shaping device, and one or more points along the span of the tissue shaping device engage with the target tissue, which results in a larger outward force at the end of the tissue shaping device on its stiffer side6206 when compared to the outward force applied at the end of the tissue shaping device on the moreflexible side6203.
• FIGS. 63A and 63B shows a tissue shaping device of thepresent invention6301, having afirst arch6302 and a second arch6303 separated by aninitial distance6304, where the position of and forces applied by the device ends vary in conjunction with the variation of the separation distance between thefirst arch6302 and asecond arch6303. In one example, the arches are configured to increase the force at the device ends as the separation distance between thefirst arch6302 and the second arch6303 increases. In a further example, the arches are configured to increase the force at the device ends as the separation distance between thefirst arch6302 and the second arch6303 decreases. In a further example, thefirst arch6302 and a second arch6303 include a contact point that limits decreases in separation distance so that the force at the device ends decreases once contact between thefirst arch6302 and thesecond arch6303 is established.
• FIG. 63B shows a tissue shaping device of thepresent invention6306, having afirst arch6307 and a second arch6308 separated by avariable distance6309, where the position of and forces applied by the device ends vary in conjunction with the variation of the separation distance between thefirst arch6307 and asecond arch6308. In one example, thevariable distance6309 can be adjusted by twisting a member with a helical adjustment feature, controlling the arch distance and thereby controlling the force at the ends of the tissue shaping device.
• FIGS. 64A through 64C show arrangements of tissue shaping devices within a target tissue.
• FIG. 64A shows a substantiallycircular target tissue6401 and a tissue shaping device that engages6402 with two points on the target tissue and moves it to anelongate configuration6403. In one example, the forces on ends of the tissue shaping device act substantially along a line drawn between the two ends.
• FIG. 64B shows a substantiallycircular target tissue6404 and a tissue shaping device that engages6405 with three points on the target tissue and moves it to anelongate configuration6406. In one example the forces on the ends of the tissue shaping device have a component that is perpendicular to a line drawn between the two ends.
• FIG. 64C shows a substantiallycircular target tissue6407, a firsttissue shaping device6408 and a secondtissue shaping device6409 that each engage with two or more points on the target tissue and moves it to anon-circular configuration6410.
• FIG. 65A shows adocking anchor6500 with aremovable wire6503. Thedocking anchor6500 has, in one example, ahelical coil anchor6501 that can engage with tissue by applying twist to thedocking anchor6500 via theremovable wire6503. Theremovable wire6503 may also be used to guide thedocking anchor6500 into position against the target tissue. Thedocking tab6502 of thedocking anchor6500 in this example is a tab that extends outside of the normal outer diameter of thedocking anchor6500.
• FIG. 65B shows thedocking anchor6500 fully engaged with thetissue6504. Theshaping device6505 is inserted over the proximal end of the removable wire6503 (not shown in this figure.)FIG. 65C shows theshaping device6505 in place and fully engaged with thedocking anchor6500. In this example, the docking feature in theshaping device6505 slides over the outer diameter of thedocking anchor6500, compressing thedocking tab6502 until it has been inserted past the end of thedocking tab6502, allowing thedocking tab6502 to return to a position extending outside the normal diameter of thedocking anchor6500, and preventing motion of theshaping device6505 in at least one direction relative to thedocking anchor6500. As shown inFIG. 65D, the removable wire is detached from thedocking anchor6500, leaving theshaping device6505 attached to thetarget tissue6504.
• FIG. 66A shows one end of ashaping device6601 withremovable control wire6603. In this example, theshaping device6601 has anend feature6602 having a diameter substantially larger than the inner diameter of a helical coil formed at or near the end of thecontrol wire6603. Twisting thecontrol wire6603 causes it to release from the end of theshaping device6601, as shown inFIG. 66B.
• FIG. 67A shows a further example of ashaping device6701 andremovable control wire6703. In this example, thecontrol wire6703 has a threadedsection6704 that mates with a threadedend feature6702 of theshaping device6701. Twisting thecontrol wire6704 causes it to unscrew from theend feature6702 of theshaping device6701, exposing theinternal threads6705 of theend feature6702 as shown inFIG. 67B.
• FIGS. 68A-68D illustrate the interaction of a flattening device with a segment of an annulus. InFIG. 68A, aflattening device6801 with three tissue coupling points shown asarrows6802a,6802b, and6803 is in a curved configuration as attached to an annulus. In this initial configuration, the lateral attachment points6802aand6802bdefine afirst line6804a, and themedial attachment point6803 resides at afirst distance6805afromline6804a. Theflattening device6801 acts to straighten the annulus to the configuration shown inFIG. 68B, where the lateral attachment points6802aand6802bdefine asecond line6804b, and themedial attachment point6803 resides at asecond distance6805bfromline6804b. In one example, thesecond distance6805bis shorter than thefirst distance6805a, while thesecond line6804bis longer than thefirst line6804a.
• FIG. 68C shows aflattening device6806 with four tissue coupling points6807a-d. The mostlateral coupling points6807aand6807ddefine a line6809, and theintermediate coupling points6807band6807creside atdistances6808aand6808brespectively from line6809. In one example, the effect of theflattening device6806 acts to reducedistances6808aand6808b, while increasing the length of line6809.FIG. 68D shows aflattening device6810 with five tissue coupling points6811a-e. The mostlateral coupling points6811aand6811edefine a line6813, and theintermediate coupling points6811b,6811c, and6811dreside atdistances6812a,6812b, and6812crespectively from line6813. In one example, the effect of theflattening device6810 acts to reduce distances6812a-c, while increasing the length of line6813.
• FIG. 69A shows anannuloplasty device6900 comprising or consisting of an innerpartial ring6901 and an outerpartial ring6902, connected atconnection points6906aand6906b. It includestissue coupling mechanisms6905aand6905b, such as tissue penetrating barbs, near the connection points6906aand6906brespectively. As illustrated inFIG. 69B, the innerpartial ring6901 lies adjacent to or otherwise follows the contour of the valve annulus, and the outerpartial ring6902 engages and presses outwardly on the an adjacent muscular wall region of the heart. The outerpartial ring6902 may be in the same plane as the innerpartial ring6901, or on a plane at an angle to and/or offset from the valve annulus as desired, for example to enhance the ability of the inner and outer partial rings to separately engage the annulus and heart valve wall. In one example, the innerpartial ring6901 creates aninner acting force6903 on the valve annulus, in response to anouter acting force6904 applied by the outerpartial ring6902 on the muscular wall of the heart. In a further example, the innerpartial ring6901 is attached to the annulus at one or more points intermediate to thetissue coupling mechanisms6905aand6905bshown, as may be advantageous to create the desired shape in the valve annulus.
• FIG. 70A shows an annuloplasty device comprising or consisting of an innerpartial ring7001 and an outer partial ring7002 connected atconnection points7003aand7003band having amechanism7004 to adjust a relative position of a crown of the innerpartial ring7001 and a crown of the outer partial ring7002. By adjusting the relative positions, the resulting force and/or displacement created on the valve annulus can be varied.
• FIG. 70B shows a close-up of anexemplary adjustment mechanism7004 having ahelical screw7006 having a distal tip that engages and presses against an inner surface of the outer partial ring7002 at acontact point7005. Thehelical screw7006 passes through a threadedcoupler7007 formed in or attached to the innerpartial ring7001. Atorque feature7008, such as a screw head, on thehelical screw7006 allows it to engage with an adjustment device (not shown) to adjust the relative positions of the innerpartial ring7001 and an outer partial ring7002 as needed to achieve the desired force and/or displacement in the valve annulus, typically by rotating the screw in the threadedcoupler7007. While this adjustment mechanism is illustrated as a helical screw, other adjustment devices are known to the art and would serve the appropriate function in this application.
• FIG. 71A shows an annuloplasty device consisting of an innerpartial ring7101 and an outerpartial ring7102 in place in a mitral heart valve. This example has asingle adjustment mechanism7105 disposed near the middle of the partial rings, in one example a spring adjusted by rotating relative to the rings.FIG. 71B shows a schematic representation of the device ofFIG. 71A, showing innerpartial ring7101 and an outerpartial ring7102 connected atconnection points7103aand7103b. It includestissue coupling mechanisms7104aand7104bnear the connection points7103aand7103brespectively. In one example, thesingle adjustment mechanism7105 is disposed near the middle of the partial rings. In a further example, thesingle adjustment mechanism7105 is disposed closer to one end than to the other end to bias the effect of the adjustment.
• FIG. 72A shows an annuloplasty device7200 comprising or consisting of an innerpartial ring7201 and an outerpartial ring7202 in place in a mitral heart valve. The annuloplasty device7200 has twoadjustment mechanisms7205aand7205bdisposed along the partial ring, for example being disposed between an outer surface or edge of the inner ring and an inner surface or edge of the outer ring.FIG. 72B shows a schematic representation of the device ofFIG. 72A, showing innerpartial ring7201 and an outerpartial ring7202 connected atconnection points7203aand7203b. The annuloplasty device7200 further includestissue coupling mechanisms7204aand7204b, such as barbs, located near the connection points7203aand7203brespectively. In one example, the twoadjustment mechanisms7205aand7205bare spaced symmetrically or near spaced from a midpoint of the span or “arc” of the partial rings. In a further example, the twoadjustment mechanisms7205aand7205bmay be spaced non-symmetrically relative to the midpoint of the span of the partial rings to bias the effect of the adjustment.
• Although certain embodiments or examples of the disclosure have been described in detail, variations and modifications will be apparent to those skilled in the art, including embodiments or examples that may not provide all the features and benefits described herein. It will be understood by those skilled in the art that the present disclosure extends beyond the specifically disclosed embodiments or examples to other alternative or additional examples or embodiments and/or uses and obvious modifications and equivalents thereof. In addition, while a number of variations have been shown and described in varying detail, other modifications, which are within the scope of the present disclosure, will be readily apparent to those of skill in the art based upon this disclosure. It is also contemplated that various combinations or sub-combinations of the specific features and aspects of the embodiments and examples may be made and still fall within the scope of the present disclosure. Accordingly, it should be understood that various features and aspects of the disclosed embodiments or examples can be combined with or substituted for one another in order to form varying modes or examples of the present disclosure. Thus, it is intended that the scope of the present disclosure herein disclosed should not be limited by the particular disclosed embodiments or examples described above. For all of the embodiments and examples described above, the steps of any methods for example need not be performed sequentially.
• FIG. 73A shows a tube withcuts1011 to allow controlled flexibility. Thecuts1011 leave an attachedspine1012 that flexes to achieve a controlled bend radius. The controlled bend radius is determined by afirst space1013 between thecuts1011. As shown inFIG. 73A, the cuts are at a spacing that creates a relatively large controlled bend radius.
• FIG. 73B shows a tube with two groups ofcuts1011 having different spacings. In the first group, thefirst space1013 between thecuts1011 results in a relatively large controlled bend radius, and thesecond spacing1014 results in a relatively smaller controlled bend radius.
• FIG. 74 shows two groups of cuts, afirst group1021 arranged so that the spine is up as shown, and asecond group1022 arranged so the spine is at a different angle. The different orientation of the second group ofcuts1022 will result in a flexed shape outside of the plane defined by the curve created by the first group ofcuts1021. More complex combinations of changes in spacing and orientation can combine to cause the tube to deform into complex three-dimensional shapes.
• FIG. 75 shows a tube of the present invention flexed into a controlled 3-dimensional shape, including a section of relativelylarge radius bend1031, relatively small radius bends inplane1032, astraight segment1033, and an out ofplane bend1034. As shown, the in-plane bent shape approximates the letter “D”, a shape relevant to target anatomies. Other combinations of bends of various radii allow other in-plane or out of plane shapes that may match, approximate, or re-shape anatomy in a desired manner. The out ofplane bend1034 allows the tube itself to act as a single locating handle, controlling both the rotation and axial position of the in-plane bent shape.
• FIG. 76 shows the tube ofFIG. 75 with the addition of twocontrol arms1041 and1042 to allow control of the angle of the plane of the planar segment of the bend tube. Specifically, the rigid or semi rigid tube itself can control the planar segment's position in four degrees of freedom, including translation up-down, side-to-side, and forwards-backwards, as well as rotation about the tube axis, while two additional control wires control rotation of the planar segment about the remaining axes orthogonal to the tube axis, allowing fine control of the position of the flexed section of tube in a total of 6 degrees of freedom. This control arm approach also applies to non-planar complex 3d flexed shapes of tubes.
• FIG. 77 shows the tube of the present invention with cuts that have alocking feature1051 to strengthen the tube against flexure in the opposite of the intended direction, as well as against torsion along the axis of the tube. To minimize distance between cuts, thereby minimizing the bend radius, cuts with thelocking feature1051 can be alternated with cuts having one or more offset lockingfeatures1052, allowing combination of small space between cuts (and therefore small bend radius) with cuts having an interlocking feature.
• FIG. 78 shows amain implant template1064 designed to create two areas of outward force1061A and1061B counterbalanced by aninward force1062. These forces are applied by ananchor1063, applying theinward force1062, and amain implant template1064, applying the outward forces1061A-B. The curvature shape of themain implant template1064 approximates a desired shape for the target segment of the annulus. An array of these implants could be applied to different annular segments to vary the total level of effect.
• FIG. 79 shows awavy implant1074 having a repeating pattern of areas creatingoutward forces1071A-D counterbalanced byinward forces1072A-C. Each area of inward force is attached to thewavy implant1074 byanchors1073A-C. As shown, three inward force areas and 4 outward force areas are shown, but these numbers can be varied as needed to offer differing levels of effect.
• FIG. 80 shows an implant consisting of an array of extensible members in theextended position1082A-D, anchored to an annulus by a corresponding array ofanchors1081A-E. As shown, the extensible members in theextended position1082A-D are attached to the enlarged annulus to be treated. Extensible members can be constructed of a resilient material or using a spring design known to the art to allow a sufficient range of elastic deformation. The materials of the extensible members can be superelastic nitinol, muscle fibers, flexinol), rubber, plastics, metals, or alloys with a high yield strength to provide appropriate elastic range for the desired function. Alternately, the extensible members may be constructed in a manner makes them transformable between an elongated configuration (as shown) and a shorter configuration (seeFIG. 81.) Various transformable structures that would fit this purpose (including stents, balloons, linkages, or closed cellular structures) are known to the art. The numbers of extensible segments and anchors may be altered as needed to provide varying degrees of effect.
• FIG. 81 shows an implant consisting of an array of extensible members in thecompressed position1092A-D, anchored to an annulus by a corresponding array ofanchors1091A-E. As shown, the extensible members in thecompressed position1092A-D have compressed the previously enlarged annulus to effect a reduction in the annular circumference, the annular area, the annular diameter, or some combination thereof.FIG. 82 shows a combination implant, including asemi-rigid shaping segment11003, which is attached to the annulus by an array ofanchors11001B-11001D. The motion of this semirigid shaping element11003 is augmented byextensible elements11002A and11002B having both an extended and a contracted configuration, which are attached to the semirigid shaping element11003 and/or theanchors11001B and11001C and are further anchored to the annulus in the extended configuration at a distance from the anchors. The materials of the extensible members can be superelastic nitinol, muscle fibers (flexinol), rubbers, plastics, metal, or alloys with a high yield strength to provide appropriate elastic range for the desired function. Alternately, the extensible members may be constructed in a manner makes them transformable between an extended configuration and a contracted configuration. Various transformable structures that would fit this purpose (including stents, balloons, linkages, or closed cellular structures) are known to the art. When theextensible elements11002A and11002B are released/transformed to their contracted configuration, they act to additionally reduce the annular circumference, the annular area, the annular diameter, or some combination thereof.
• FIG. 83 shows an anchor for fastening an implant to tissue, including ananchor member1110 having ahelical coil section1111, animplant stop feature1112, and alocking feature1115. The anchor system also includes atorque member1113 and alocking wire1114. Thehelical coil section1111 of theanchor member1110 can be fastened into the tissue by twisting thetorque member1114, which transfers the torque through thelocking wire1114 to theanchor member1110 via thelocking feature1115. The locking wire also holds theanchor member1110 to thetorque member1114 in the longitudinal Withdrawing thelocking wire1114 by pulling it proximally releases theanchor member1110 from thetorque member1113 allowing removal of thetorque member1113 andlocking wire1114.
• FIG. 84 shows animplant1121 which defines aconcave space1122. The concave space is also referred to herein as a “concavity,” as defined previously. Thetissue1123 is shown in place in contact with both theimplant1121 and ahelical coil1124 having a sharpened tip of the implant, but not entering theconcave space1122. Rotating thehelical coil1124 in the direction of thearrow1125 will cause thehelical coil1124 to draw thetissue1123 into theconcave space1122. A single implant could define multiple concave spaces, and include multiple helical coils, or multiple single-concave space implants could be used. Prior to rotating the helical coil, its sharpened tip extends beyond both sides of the implant to facilitate penetration of the tissue.
• FIG. 85 shows animplant1131 in place intissue1133. In this figure, thehelical coil1134 has been activated to draw the surroundingtissue1133 into theconcave space1132, substantially filling thespace1132.
• FIG. 86 shows an undulatingtemplate1141 in place against a substantially straight segment oftissue1142, with threehelical anchors1143A-1143C connecting the undulatingimplant1141 to thetissue segment1142 without substantially deforming thetissue segment1142. The ends of thetissue segment1142 are substantially farther apart than the ends of the undulatingtemplate1141, although their lengths are comparable.
• FIG. 87 shows the undulatingtemplate1141 ofFIG. 86 with the now undulatingtissue segment1152 having been pulled tightly against the undulatingtemplate1141 by thehelical anchors1143A-1143C. The ends of the now undulatingtissue segment1152 are proximate to the ends of the undulatingtemplate1141, although its length is comparable to the substantially straight segment oftissue1142 fromFIG. 86.
• FIG. 88 shows the deformations projected on an untreatedmitral valve annulus1161 by aflattening template1162 and an undulatingtemplate1163. The undulating template creates similar reduction in vertical dimension as shown, without substantially increasing horizontal dimension as shown.
• FIG. 89 shows asegmented undulating template1171, consisting ofsegments1172A-1172C. As shown,segments1172B and1172C have been delivered into the desired position, andsegment1172A is being delivered to the desired position by sliding it along anelongate locating member1173 which is attached to the already placedsegment1172B. An elongate locatingmember1174 is attached to thesegment1172A which is in the process of being placed, offering guidance for placement of an additional segment (not shown). In this way, it is possible to place an arbitrary number of segments by sliding the next segment up the outermost elongate locatingmember1174.
• FIG. 90 shows a segment of an undulatingtemplate1181 folded distally for delivery through a tube or tubular structure. The ends of the segment of the undulatingtemplate1181 are held together by aremovable shaper1182 which holds the undulatingtemplate1181 in its folded configuration during delivery. In addition, two elongated control elements such ascontrol wires1183A and1183B are shown attached near the ends of the segment of the undulatingtemplate1181.
• FIG. 91 shows a segment of an undulatingtemplate1191 which has been expanded by applying tension to thecontrol wires1193A and1193B. Theanchor1192 extends away from the segment of the undulatingtemplate1191 to allow easy anchoring in tissue (not shown)
• FIG. 92 shows two segments of undulatingtemplates12001A and12001B attached to controlwires12002A-R,12002A-L,12002B-R, and12002B-L andtorque members12003A and12003B, arranged one behind the other for delivery through a tubular structure (not shown). The alignment of thesegments12001A and12001B is shown slightly offset, but should be adjusted to allow for minimum tube diameter that allows passage of the segments of undulatingtemplates12001A and12001B,control wires12002A-R,12002A-L,12002B-R, and12002B-L andtorque members12003A and12003B through as small a diameter tubular structure as practical. Additional segments of undulating template (not shown) can be arranged in similar fashion for placement through a tubular structure as needed.
• FIG. 93 shows a substantially flat,shapeable template1211 with ananchor1212 withtorque member1214 and forming dies1213A and1213B. The orientation of the forming dies1213A and1213B relative to theanchor1212 andtorque member1214 is such that the forming dies1213A and1213B appose theshapeable template1211 in its substantially flat configuration. In this substantially flat configuration, theshapeable template1211 can be firmly attached to the target tissue (not shown) through activation of theanchor1212.
• FIG. 94 shows ashapeable template1221 in the shaped configuration, created by relative motion between theanchor1222 and forming dies1223A and1223B. When theshapeable template1221 is firmly attached to tissue via the anchor1223, the tissue will move along with the template as it is shaped, creating a desired shaping and/or shortening effect.
• FIG. 95 shows an assembled undulatingtemplate1231 made up of threeundulating template segments1232A-1232C. The segments are connected withpin connectors1233A and1233B, each of which is made up of apin element1234 attached to an undulating template segment through anattachment device1235. Typical attachment devices known to the art which may be applicable to this mechanism include threaded fasteners such as nuts, crimp connectors, and push-on retaining rings.
• FIG. 96 shows an assembled undulatingtemplate1241 made up of threeundulating template segments1242A-1242C. The segments are connected by anintegral post1243 joined by anattachment device1244. Typical attachment devices known to the art which may be applicable to this mechanism include threaded fasteners such as nuts, crimp connectors, and push-on retaining rings.
• FIG. 97 shows an assembled undulatingtemplate1251 made up of threeundulating template segments1252A-1252C. The segments are connected bymechanical connectors1254. Typical mechanical connectors applicable to this mechanism include crimp connectors and clips.
• FIG. 98 shows a partialannular ring1261 withmultiple anchors1262 disposed within avalve annulus1263. Theanchors1262 are of sufficient length to bridge the gap between the partial annular ring and thevalve annulus1263. Activating theanchors1262 draws theannulus1263 toward thepartial ring1261, reshaping theannulus1263 to the desired configuration. It is possible to apply this approach to a closed ring of the desired shape as well as the partialannular ring1261 as shown. Desired shapes for the partial or close ring may include circular, D-shaped, oval, elliptical, or with a concave section corresponding to one ormore anchor1262 positions.
• FIG. 99 shows an alternate segment of an undulatingtemplate1271 having twoanchors1272A and1272B separated by aconvex segment1273.
• FIG. 100 shows an undulatingtemplate1281 consisting of twoalternate segments1282A and1282B each having two anchors separated by a convex segment, joined by anattachment mechanism1283. Typical mechanical connectors applicable to this mechanism include crimp connectors, clips, sutures, or the like.
• FIG. 101 shows an undulatingtemplate2012 composed of approximately straight segments arranged in a rectilinear pattern with angled bends or corners, with atissue coupling mechanism2011 attached approximating the mid-point of the body of the template, twobody segments2013aand2013brising from the point of attachment of thetissue coupling mechanism2011, and twocompressive peaks2014aand2014b. The area of the undulatingtemplate2012 where the tissue coupling mechanism is attached as well as the area of thecompressive peaks2014aand2014bare substantially horizontal, while the risingbody segments2013aand2013bare substantially vertical.
• FIG. 102 shows an undulatingtemplate2021 composed of approximately straight segments connected by arcuate segments including the lower rightarcuate segment2022.
• FIG. 103 shows an undulating template where the risingbody segments2031aand2031bform a diverging angle relative to each other and the point of attachment of the tissue coupling mechanism. As tissue is drawn towards the base of the tissue coupling mechanism, the gap between the risingbody segments2031aand2031bnarrows, causing increasing compressive forces on the tissue.
• FIG. 104 shows an undulatingtemplate2041 composed of arcuate segments ending so that the segment ends near thecompressive peak2042.
• FIG. 105 shows an undulatingtemplate2051 composed of arcuate segments ending so that the segment end2052) extends past thecompressive peak2053.
• FIG. 106 shows an undulatingtemplate2061 composed of a continuous, non-circular shape. As shown, the shape is a sinusoidal curve.
• FIG. 107 shows an undulatingtemplate2071 where the distance from the point where the tissue coupling mechanism is attached to the compression peaks of the body of the template is greater than the length of the tissue coupling mechanism. Aline2072 tangent to the compression peaks is not crossed by the distal tip of the tissue coupling mechanism. Placement of such a template can be accomplished, for example, by deflecting the template proximally so that the tissue coupling mechanism can penetrate the target tissue.
• FIG. 108 shows an undulating template2081 where the distance from the point where the tissue coupling mechanism is attached to the compression peaks of the body of the template is less than the length of the tissue coupling mechanism. The distal tip of the coupling mechanism crosses a line2082 tangent to the compression peak. Placement of such a template can be accomplished, for example, with the ends of the template in the relaxed and non-deflected position.
• FIG. 109 shows an undulating template withtissue2093 held in place by a tissue coupling mechanism, causing the template to exerttensile force2091 normal to the original position of the tissue (via the tissue coupling mechanism) andinward forces2092aand2092b, tangential to the original position of the tissue.
• FIG. 110 shows an undulating template withtissue21003 held in place by a tissue coupling mechanism, causing the template to exerttensile force21001 normal to the original position of the tissue (via the tissue coupling mechanism) andcompressive forces21002aand21002b, normal to the original position of the tissue in substantially the opposite direction as thetensile force21001.
• FIG. 111 shows an undulating template withtissue2113 held in place by a tissue coupling mechanism, causing the template to exerttensile force2111 normal to the original position of the tissue (via the tissue coupling mechanism) and compressive-inward forces2112aand2112b, between normal and tangential to the original position of the tissue.
• FIG. 112 shows an undulating template withtissue2123 held in place by a tissue coupling mechanism, causing the template to exerttensile force2121 normal to the original position of the tissue (via the tissue coupling mechanism) and compressive-outward forces2122aand2122b, between normal and tangential to the original position of the tissue.
• FIG. 113 shows an undulating template with stabilizingtissue coupling mechanisms2131aand2131bat each end of the body, in addition to the primary tissue coupling mechanism in the middle. The stabilizingtissue coupling mechanisms2131aand2131beach have a penetrating coil at their distal ends, and acoupling coil2133 at the proximal end with the opposite handedness of the penetrating coil. The stabilizingtissue coupling mechanisms2131aand2131bare releasably coupled viacoupling bushings2134 attached tosmall torque members2136. Thecoupling bushings2134 guide and capture thecoupling coil2133 of the stabilizingtissue coupling mechanisms2131aand2131bagainst turning in one direction. They are prevented from turning relative to each other by akey wire2135aand2135b. Removing thekey wire2135aor2135ballows thesmall torque members2136 and attachedcoupling bushings2134 to turn relative to thecoupling coil2133, releasing the stabilizingtissue coupling mechanisms2131aand2131bfrom thecoupling bushing2134. A slot in the undulating template is arranged so that the stabilizingtissue coupling mechanisms2131aand2131bwill not slide freely through the undulating template when coupled to adjacent tissues by twisting.
• FIG. 114 shows and undulatingtemplate2141 with twoprincipal ends2142aand2142b, and an additional stabilizing arm2143 extending from the body, as well as stabilizing penetratingpoints2144aand2144b, in this example disposed near the principal ends2142aand2142b. The body of thetemplate2141 may include a single stabilizing penetrating point, two stabilizing penetratingpoints2144aand2144bas shown, or more as required. The stabilizingpenetrating points2144aand2144bmay include curves, barbs, bends, or other such features to allow them to passively penetrate the tissue adjacent to the undulatingtemplate2141, or may benefit from action on behalf of the user to actuate the stabilizingpenetrating point2144aand2144b.
• FIG. 115 shows an undulatingtemplate2151 with theends2152aand2152bfolded away from the tissuecoupling mechanism attachment2153 to a delivery position as shown, where the tissuecoupling mechanism attachment2153 and or flexibility in thetissue coupling mechanism2154 allow the template arms to fold together alongside thetissue coupling mechanism2154. This configuration may allow for more compact delivery size of the implant compared to configurations where the delivery position has thetissue coupling mechanism2154 disposed between thearms2152aand2152bof the undulatingtemplate2151
• FIG. 116 shows an undulatingtemplate2161 in position adjacent to amitral annulus2162 in the untreated state. As shown, the undulatingtemplate2161 is not interacting with the tissue but is positioned approximately as it would be prior to coupling it to the tissue via a tissue coupling mechanism (not shown).
• FIG. 117 shows an undulatingtemplate2171 with amitral annulus2172, where the tissue coupling mechanism has drawn the annulus tightly against the template. As shown, the circumference of the annulus following the template is essentially unchanged, but the effective circumference of the annulus (bypassing the segment captured by the template) has decreased. The effect of decreasing the effective circumference of the annulus, in combination with deforming the central portion of the annulus toward the middle of the valve, reduces both the minor axis diameter of the valve and the area of the valve. The original position of theannulus2162 fromFIG. 116 is also shown for reference.
• FIG. 118 illustrates adelivery device2184 for placing an undulatingtemplate2182 over apre-anchor guide2181. Thepre-anchor guide2181 runs through a receiving slot in thedelivery device2184. Thepre-anchor guide2181 consists of a tissue coupling feature (a penetrating coil as shown) and a long guide wire. It may be advantageous to place thepre-anchor guide2181 with a separate delivery device prior to introducing the undulatingtemplate2182. In that case, thedelivery device2184 for the undulatingtemplate2182 may have reduced flexibility, steer-ability, diameter, torquability, or other requirements since the target position has been pre-selected and verified duringpre-anchor guide2181 placement. The pre-anchor delivery device may include an outer steerable sheath, and an inner steerable sheath, the outer steerable sheath being steerable along a radius of from 1 cm to 3 cm, and capable of bending to and angle between 90 and 200 degrees. The inner steerable sheath is able to be rotated within the outer sheath, and extended or retracted relative to the outer sheath, allowing between 1 cm and 10 cm of the inner sheath to extend past the tip of the outer sheath. The inner steerable sheath may be steerable along a radius of from 0.5 cm to 3 cm, through an angle between 30 and 90 degrees. There may be features on thetemplate2182 that interact with thedelivery device2184 to stabilize thetemplate2182 for improved maneuverability during placement. Such features could also be used with a remotely actuated powered system for increased precision control.
• Thedelivery device2184 provides channels for the releasable torque member attached to the primary tissue coupling mechanism, for the small torque members attached to the stabilizing tissue coupling mechanisms (not shown), and for thepre-anchor guide2181. These channels may be formed as an extrusion with four distinct inner lumens. The channels for thepre-anchor guide2181 and the primary tissue coupling mechanism exit the distal end of thedelivery device2184, while the channels for the small torque members attached to the stabilizing tissue coupling mechanisms (not shown) have aside exit2185 that communicates with the distal end of thedelivery device2184, allowing the small torque members (not shown) to be delivered within the outer diameter of thedelivery device2184 when the undulatingtemplate2182 is folded forward in the delivery configuration (as shown inFIG. 115), and then to extend outside the diameter of thedelivery device2184 when the arms are in the placement position.
• Thedelivery device2184 also incorporates arotational guide member2183 which couples the undulatingtemplate2182 to thedelivery device2184. Depending on the exact use configuration of thedelivery device2184, the body of thedelivery device2184 may be long and flexible to function as a catheter, or short and rigid for open surgical procedures. Thedelivery device2184 may include an outer steerable sheath, and an inner steerable sheath, the outer steerable sheath being steerable along a radius of from 1 cm to 3 cm, and capable of bending to and angle between 90 and 200 degrees. The inner steerable sheath is able to be rotated within the outer sheath, and extended or retracted relative to the outer sheath, allowing between 1 cm and 10 cm of the inner sheath to extend past the tip of the outer sheath. The inner steerable sheath may be steerable along a radius of from 0.5 cm to 3 cm, through an angle between 30 and 90 degrees.
• FIGS. 119-121 show percent change for annular dimensions in various templates implanted in-vivo. These data were collected during open heart implantations in the porcine model; the chest was opened, bypass readied, and pre-op measurements made. The animal was then put on bypass, the device implanted, the heart closed and taken off bypass. When the heart was pumping successfully on its own, post-operative measurements were taken and compared to the pre-op measurements. All measurements were taken in systole.
• FIG. 119 shows percent area change for various templates implanted in-vivo.
• FIG. 120 shows percent circumference change for various templates implanted in-vivo.
• FIG. 121 shows percent minor axis change for various templates implanted in-vivo.
• FIGS. 122-123 show percent change in the minor axis diameter for various templates in excised porcine hearts. Hearts were obtained fresh, mounted in a stand so that the mitral annulus was approximately horizontal, and held so that the pre-procedure ratio of major to minor axis was between 1.2:1 and 1.3:1 as verified by D-shaped valve sizers. The implants were placed, and the altered dimension of the mitral valve again measured by D-shaped valve sizers.
• FIG. 122 shows percent A-P (minor axis) reduction for various multi-wave templates implanted in excised porcine mitral annuli.
• FIG. 123 shows percent A-P (minor axis) reduction for various single-wave templates implanted in excised porcine mitral annuli.
• FIG. 124 shows acontinuous ring template2241, having a single undulating region with one or more tissue anchors2242 separated by one or more wave peaks2243. Thisring template2241 may include alatching discontinuity2244, allowing it to be inserted and deployed in a substantially straight configuration, and connected to form a semi-rigid structure. Such a structure may be used as a stabilizer for placement of a replacement valve as required.
• FIG. 125 shows acontinuous ring template2251, having multiple undulating region with one or more tissue anchors2252 separated by one or more wave peaks2253. Thisring template2251 may include alatching discontinuity2254, allowing it to be inserted and deployed in a substantially straight configuration, and connected to form a semi-rigid structure. Such a structure may be used as a stabilizer for placement of a replacement valve as required.
• FIG. 126 shows acontinuous ring template2261, having one undulating region which covers essentially the entire circumference of thering template2261, with one or more tissue anchors2262 separated by one or more wave peaks2263. Thisring template2261 may include alatching discontinuity2264, allowing it to be inserted and deployed in a substantially straight configuration, and connected to form a semi-rigid structure. Such a structure may be used as a stabilizer for placement of a replacement valve as required.
• FIG. 127 shows an undulating template with anangle2271 between theanchor2274 and thecompression pad feature2273. Thisangle2271 causes the line oftensile force2272 and the line ofcompressive force2273 to intersect, encouraging theanchor2274 to form a desired angle with the target tissue. Thisangle2271 can be built into the template, formed after the template is in position, or can be one stable state of a bi-stable system, which goes in straight and snaps to the angled configuration.
• FIG. 128 shows an undulating template with a parallel offset between thetensile forces2281 on theanchor2283 and thecompressive force2282 on thecompression pads2284. The offset between these forces creates a moment that biases theanchor attachment point2285 to move in a desired angular direction relative to the target tissue.
• FIG. 129 shows an end-on view of the implant fromFIG. 128, illustrating the separation between the plane of thecenter anchor2291 and the plane of the side anchors2292.
• As shown inFIG. 130A, atissue shaping template13001 has a preformed shape it takes in the unconstrained configuration. The unconstrained configuration is optimized for tissue interaction, but not for delivery to the desired site on the tissue.FIG. 130B shows thetissue shaping template13001 in a first crimped position, having been constrained in a way that brings the two ends (13002 and13003) closer together by forcing them toward the middle of the implant. In certain implant configurations, it may be advantageous to push the ends very closely together, arriving at a crimped configuration that is small enough for insertion through a delivery catheter or other device to the desired location in the tissue.FIG. 130C shows thetissue shaping implant13001 having been curved, bending one end in aclockwise direction13004 and the opposite end in acounterclockwise direction13005 to form a substantially circular crimped configuration. This crimped configuration may be easier to deliver through a small diameter tube than the unconstrained configuration.
• FIG. 131A shows an unconstrained preformed orpre-shaped template13101. The unconstrained preformed orpre-shaped template13101 is coupled to controlwires13104A and13104B, as well as ananchor13102 which is in turn coupled to ananchor control device13103.FIG. 131B shows the template ofFIG. 131A in acrimped configuration13105, which is constrained with the ends or wings of the template retracted proximally relative to theanchor13102 bycontrol wires13104A and13104B which apply a proximal tension to deform the wings proximally away from the anchor. This crimped configuration allows the anchor to be coupled to the desired tissue by initially or fully penetrating theanchor13102 while the wings are in the constrainedconfiguration13105, which may simplify the placement of the template. After theanchor13102 has been fully or partially penetrated into the target site, the retracted ends or wings of the template may be released from the control wires to return to the configuration ofFIG. 131A. Depending upon how far theanchor13102 has been penetrated, the tissue of the annulus will be fully or partially drawn into the convexity between the wings. Theanchor13102 may be further rotated to fully draw in the tissue as needed.
• FIG. 132 shows various dimensions on a typical preformed orpre-shaped template13200 having aconcavity segment13205 and two apex orconvex segments13206A and13206B. The end-to-end length13201, the peak-to-peak length13202, theconcavity width13203 andconcavity depth13204 are illustrated on the diagram. The relationship between theconcavity width13203 andconcavity depth13204 may affect the magnitude of the tissue reshaping effect, as well as the suitability of the preformed orpre-shaped template13200 for reshaping various different target tissues. Similarly, the relationship between the end-to-end length13201 of thetemplate13200, and the overall length of the flattened template shape (not shown) may be indicative of the magnitude of the reshaping effect.
• FIG. 133A shows a pre-delivery position of a preformed orpre-shaped template13301 slidably engaged with a shaft of ananchor control device13303. As shown, thetemplate13301 is spaced proximally from theanchor13302, where theanchor13302 may be releasably coupled to the shaft of theanchor control device13303.FIG. 133B shows the preformed orpre-shaped template13301 in afinal delivery position13305, having slid distally to engage theanchor13302. Of particular significance, by allowing the preformed orpre-shaped template13301 to slide over the shaftanchor control device13303, theanchor control device13303 can act as a guide to properly position thetemplate13301 at a target tissue site in the annulus or other tissue.
• Thetemplate13301 infinal delivery position13305 may be coupled to theanchor control device13303 by ananchor coupling device13304. The anchor coupling device can take several forms, including elastic tabs (similar to those inFIG. 65) that capture the template infinal delivery position13305, a nut that is screwed on to theanchor13302, or other such mechanisms known to the art. When theanchor control device13303 is released from theanchor13302, for example by removing akey wire13306, theanchor control device13303 can be removed, while the template infinal delivery position13305 remains coupled to theanchor13302 in the tissue.
• While preferred examples of the present invention have been shown and described herein, it will be obvious to those skilled in the art that such examples are provided by way of example only. Numerous variations, changes, and substitutions will now occur to those skilled in the art without departing from the invention. It should be understood that various alternatives to the examples of the invention described herein may be employed in practicing the invention. It is intended that the following claims define the scope of the invention and that methods and structures within the scope of these claims and their equivalents be covered thereby.
Examples
• In a preferred example, the template outline was laser cut from a 0.020″ thick sheet of superelastic Nitinol® to the desired flat shape, which was cleaned and polished by ultrasonic cleaning and manual polishing, then the flat was clamped into a shaping fixture made of heat resistant aluminum that held the flat shape in a configuration with a single concavity and two convexity or apex or convex segment regions, and the heat set assembly was heated to 485° C. for 4 minutes by submerging in a fluidized bed of aluminum oxide, then was rapidly quenched in a room temperature water bath to set the shape. The now preformed shape was removed from the shaping fixture, inspected, cleaned, and finished (by rounding sharp edges with a hand tool), then covered with an ePTFE sleeve, and attached to an anchor in the concavity region.
• In this example, the initial implants were performed via open heart bypass procedure in the ovine model. Templates and anchors were attached to an open surgical delivery device in a substantially unconstrained state. The heart was accessed through a thoracotomy, the animal was put on bypass, the heart stopped, and the mitral valve was accessed through the left atrial wall. The template was maneuvered into position with the delivery device. The apex anchor control devices were retracted, the central anchor positioned on the annulus, and the central anchor control device was twisted to engage the central anchor with the annular tissue. The apex anchor control devices were advanced, and the apex anchors twisted to engage them with the tissue. All three key wires were removed, and the delivery device and anchor control devices were removed, leaving the template, center anchor, and apex anchors in place. The opening in the left atrial wall was closed, the heart was restarted, and measurements of the annulus were taken via ultrasound. In sterile procedures, the implant, anchors, and delivery device were attached to a protective card, sealed into a Tyvek pouch, and sterilized by exposure to EtO gas. At the conclusion of survival implant procedures, the thoracotomy was closed, and the animal moved to an intensive care suite to recover.
• In this example, the template was implanted through a trans-septal catheterization. First, the formed single concavity template with anchor was loaded into a delivery catheter by attaching the anchor to an anchor control device with a key wire and placing two convexity or apex or convex segment anchors (having been previously attached to the convexity or apex anchor control devices via key wires) to the convexity or apex regions of the formed template. Trans-septal access was gained through the femoral vein, and a needle and steerable outer catheter advanced across the septum. The apex regions of the template were forced distally (relative to the concavity anchor) to reduce the assembly diameter and inserted through the steerable delivery catheter for delivery to the target annulus. The formed template with anchors was pushed distally through the steerable outer catheter, where it substantially regained its formed shape, and the apexes or wings were retracted distally by pulling on the apex anchor control devices. Pulling the apex anchor control devices independently allowed an added means of control of the curvature and position of the distal end of the tubular catheter, anchors and template. The anchor control device was rotated to couple the convexity anchor to the annulus, the apex control devices were released to bring the apexes into apposition with the annulus tissue, the apex control devices were rotated to couple the apex anchors to the annular tissue. The 3 key wires were then removed, and the control devices and delivery catheter withdrawn, leaving the formed template with attached anchor, as well as the two apex anchors, in place on the annulus.
• In another preferred example, the template outline was laser cut from a 0.020″ thick sheet of superelastic Nitinol® to the desired flat shape, which was cleaned and polished by ultrasonic cleaning and manual polishing, then the flat was clamped into a shaping fixture made of heat resistant aluminum that held the flat template in a configuration with three concavities and four apex or convex regions, and the heat set assembly was heated to 485° C. for 4 minutes by submerging in a fluidized bed of aluminum oxide, then was rapidly quenched in a room temperature water bath to set the shape. The now preformed shape was removed from the shaping fixture, inspected, cleaned, and finished (by rounding sharp edges with a hand tool), then covered with an ePTFE sleeve, and one anchor was attached to each of the three concavity regions.
• In this example, the formed triple concavity template with anchors was then loaded into a delivery catheter by attaching the anchors to anchor control devices with key wires. The apex or convex regions were forced medially (toward the middle of the implant) and then wrapped into a substantially circular shape to reduce the assembly diameter and inserted through an elongated tubular catheter for delivery to the target annulus. The formed template with anchors was pushed distally out of the tubular catheter, where it substantially regained its formed shape, and the outer concavities were retracted distally by pulling on the outer anchor control devices. Pulling the outer anchor control devices independently allowed an added means of control of the curvature and position of the distal end of the tubular catheter, anchors and template. The central anchor control device was rotated to couple the central convexity anchor to the annulus, the outer control devices were released to bring the outer anchors into apposition with the annulus tissue, and the outer control devices were rotated to couple the outer concavity anchors to the annular tissue. The 3 key wires were then removed, and the control devices and delivery catheter withdrawn, leaving the formed template with attached anchors in place on the annulus.

Claims (30)

What is claimed is:

1. A stent prosthesis for valve repair or replacement comprising:

a scaffold comprising patterned structural elements, said stent being expandable from a crimped configuration to an expanded configuration and having sufficient strength to support a body annulus in the expanded configurations, wherein the scaffold comprises at least one circumferential ring comprising struts and crowns, wherein at least one strut in said at least one ring comprises at least one separation region and wherein said at least one separation region comprises a male-female junction and a biodegradable polymer and/or adhesive, said separation region being held together in the crimped configuration and is configured to separate after expansion of the stent under physiologic environment; and

at least one valve configured to be coupled to said at least one ring, said valve allowing blood to flow in one direction during the cardiac cycle.

2. An implant for reshaping a valve annulus, said implant comprising:

a pre-shaped metallic template having a length in an axial direction and at least one concavity in a lateral direction along said length, said concavity having a concave surface configured to be positioned adjacent to a peripheral wall of the valve annulus; and

at least one anchor configured to be coupled to the pre-shaped metallic template and to draw at least one segment of said peripheral wall of the valve annulus into said concavity to thereby reduce a diameter of said annulus in a radially inward direction, wherein said template is deployable to said pre-shaped configuration from a crimped configuration.

3. The implant ofclaim 2, wherein the pre-shaped metallic template has a single concavity with a pair of opposed legs disposed about a lateral axis and joined by a curved junction region.

4. The implant ofclaim 2, wherein each of the opposed legs each have a convex surface which is axially and laterally spaced-apart from the concavity and wherein the at least one anchor on the template is further configured to draw adjacent segments of said peripheral wall of the valve annulus against the convex surfaces.

5. The implant ofclaim 4, further comprising an anchor on each of the convex surfaces of the opposed legs.

6. The implant ofclaim 2, wherein the pre-shaped metallic template has at least two concavities separated by a convexity.

7. The implant ofclaim 6, wherein each concavity has at least one anchor configured to draw at least one segment of said peripheral wall of the valve annulus into said concavity.

8. The implant ofclaim 2, wherein the at least one region comprises all or a portion of a posterior mitral valve annulus.

9. The implant ofclaim 2, wherein the pre-shaped metallic template comprises an elongate structure having a length in a range from 10 mm to 30 mm.

10. The implant ofclaim 9, wherein the width of the concavity is in a range from 1 to 5 times the depth of the concavity.

11. The implant ofclaim 2, wherein the at least one anchor comprises a helical anchor having a distal end and a proximal end, said distal end having a sharpened tip, and said proximal end being rotatably secured in the concavity of the template.

12. The implant ofclaim 2, wherein the anchor is configured to be coupled to the tissue while the template is coupled to the anchor.

13. The implant ofclaim 2, wherein the anchor is configured to be coupled to the tissue before the anchor is coupled to the template.

14. A system comprising:

the implant ofclaim 11; and

a driver configured to detachably attach to and rotate the helical anchor to drive the distal tip of the helical anchor into the annulus and draw at least a segment of an inner surface of the annulus into the concavity.

15. The system ofclaim 14 wherein the template is slidably coupled to the detachable driver and can be moved distally relative to the detachable driver to couple with the anchor.

16. The system ofclaim 14 wherein the template is rotatably coupled to the anchor.

17. A method for reshaping a valve annulus, said method comprising:

delivering in a crimped configuration a metallic implantable template having a tissue-engaging surface pre-shaped with at least one concavity;

expanding said template with an open end of the at least one concavity oriented against a peripheral surface of the valve annulus, and

drawing at least one segment of the peripheral surface of the valve annulus into the concavity to reduce a diameter of said valve annulus.

18. The method ofclaim 17, wherein drawing at least one segment of the peripheral surface of the valve annulus into the concavity aligns the template with the valve annulus.

19. The method ofclaim 17, wherein drawing at least one segment of the peripheral surface of the valve annulus into the concavity comprises engaging an anchor against the annulus segment to apply tension or compression to draw said annulus segment into said concavity.

20. The method ofclaim 19, wherein the anchor comprises a helical coil and drawing comprises rotating the helical coil to penetrate the peripheral surface of the valve annulus.

21. The method ofclaim 20, wherein the helical coil is detachably attached to a driver and rotating the helical coil comprises rotating the driver.

22. The method ofclaim 21, wherein the metallic implantable template is slidably coupled to said driver and said method further comprises applying tension to said driver and said helical coil to draw said annulus segment into said concavity.

23. The method ofclaim 22, further comprising locking the template to the helical coil after the annulus segment has been drawn into said concavity.

24. The method ofclaim 21, wherein the driver is advanced and rotated to implant the helical coil in the valve annulus, the template is advanced over the driver and coupled to the helical coil after the coil has been implanted in the valve annulus, and the driver is detached from the coil after the template has been advanced over the shaft and coupled to the coil.

25. The method ofclaim 17, wherein the anchor comprises a helical coil rotatably attached to the template and drawing comprises rotating the helical coil so that the tissue is drawn into the concavity while the anchor remains attached to the template.

26. The method ofclaim 17, wherein template is constrained in the crimped configuration and expanding comprises releasing the template from constraint.

27. The method ofclaim 17, wherein the peripheral surface includes at least a portion of a mitral valve annulus, tricuspid valve annulus, an aortic valve annulus, or a pulmonary valve annulus.

28. The method ofclaim 17, wherein drawing consists of drawing a single segment of the peripheral surface of the annulus into a single concavity on a single template.

29. The method ofclaim 17, wherein drawing comprises drawing at least two segments of the peripheral surface of the annulus into at least two concavities on a single template.

30. The method ofclaim 17, wherein engaging the template against the peripheral surface of the valve annulus comprises intravascularly advancing the template.

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