Patent Grant
11517429
Some applications of the present invention relate in general to valve replacement. More specifically, some applications of the present invention relate to prosthetic valves for replacement of a cardiac valve.
Ischemic heart disease causes regurgitation of a heart valve by the combination of ischemic dysfunction of the papillary muscles, and the dilatation of the ventricle that is present in ischemic heart disease, with the subsequent displacement of the papillary muscles and the dilatation of the valve annulus.
Dilation of the annulus of the valve prevents the valve leaflets from fully coapting when the valve is closed. Regurgitation of blood from the ventricle into the atrium results in increased total stroke volume and decreased cardiac output, and ultimate weakening of the ventricle secondary to a volume overload and a pressure overload of the atrium.
For some applications of the invention, a prosthetic valve support is provided for facilitating transluminal implantation of a prosthetic valve at a native valve (e.g., a native heart valve) of a subject. The prosthetic valve support is configured to be placed at the native valve, such as by placing an upstream support portion (e.g., an annular portion) of the prosthetic valve support against an upstream surface of the native valve (e.g., against a native valve annulus). The prosthetic valve is subsequently implanted at the native valve by coupling the prosthetic valve to the prosthetic valve support, such as by expanding the prosthetic valve in an opening defined by the prosthetic valve support. For some applications, the prosthetic valve support is couplable to the native valve, independently of the prosthetic valve. The implantation of the prosthetic valve at the native valve replaces native check valve functionality of the native valve with substitute check valve functionality of the prosthetic valve. For some applications, the prosthetic valve support and/or the prosthetic valve comprise tissue-engaging elements (e.g., support-anchoring elements, and valve-anchoring elements, respectively), such as anchors or clips.
Typically, the prosthetic valve is expanded within one or more openings defined by the prosthetic valve support, and coupling of the prosthetic valve to the prosthetic valve support is facilitated by radially-expansive force applied by the prosthetic valve against the prosthetic valve support. For some applications, additional coupling techniques, such as support-engaging elements, coupling leads, ratchet mechanisms, protrusions, and/or pockets are used.
For some applications, the prosthetic valve support is configured to receive, at different periods, more than one prosthetic valve. For example, a first prosthetic valve may be removed from the prosthetic valve support, and replaced with a second prosthetic valve. Alternatively, the first prosthetic valve may be left in place when the second prosthetic valve is implanted. For example, the prosthetic valve support may define more than one lumen, each lumen configured to receive a respective prosthetic valve. Alternatively, the prosthetic valve support may define a lumen that is configured (e.g., shaped) to receive a first valve at a first period, and a second valve at a second period.
For some applications, the prosthetic valve support comprises support-anchoring elements that are flexibly-coupled to the upstream support portion. For some such applications, the support-anchoring elements are configured to anchor the prosthetic valve support to the native valve, while allowing the leaflets of the native valve to continue to function, at least in part. For some applications, the prosthetic valve support comprises support-anchoring elements whose length is variable (e.g., adjustable).
For some applications of the invention, a cross-sectional area of the opening defined by the prosthetic valve support is adjustable.
For some applications of the invention, delivery apparatus for implantation of a medical device (e.g., a prosthetic valve and/or a prosthetic valve support) is provided, the delivery apparatus and/or the medical device being configured to allow retrievability of the medical device during one or more stages of delivery and/or deployment of the medical device.
There is therefore provided, in accordance with an application of the present invention, apparatus for use with a first prosthetic valve and a second prosthetic valve at a native heart valve of a subject, the apparatus including:
a prosthetic valve support, shaped to define at least one lumen, and configured:
In an application, the prosthetic valve support is configured to facilitate the implantation of the first prosthetic valve by being configured to receive the first prosthetic valve in the at least one lumen.
In an application, the prosthetic valve support includes a seal, which:
does not cover at least a first region of the at least one lumen,
covers at least a second region of the at least one lumen, and
is configured to be openable at least the second region, and the prosthetic valve support is configured:
to facilitate the implantation of the first prosthetic valve by being configured to receive the first prosthetic valve in the first region, and
to facilitate the implantation of the second prosthetic valve by being configurable, by opening of the seal, to receive the second prosthetic valve in the second region.
In an application, the at least one lumen is shaped to define at least a first lumen and a second lumen, and the seal covers the second lumen.
In an application, the first region and the second region are defined by the same lumen.
In an application, the apparatus includes a covering that covers the prosthetic valve support, and the seal is defined by a portion of the covering.
In an application, the prosthetic valve support is configured to receive the first prosthetic valve in the lumen, and is configured to facilitate the implantation of the second prosthetic valve by being configured to receive the second prosthetic valve in the same lumen.
In an application, the apparatus further includes the first and second prosthetic valves, the first prosthetic valve defines a lumen therethrough, and the second prosthetic valve is configured to be implanted in the lumen of the first prosthetic valve.
In an application:
the second prosthetic valve defines a lumen therethrough,
after the first period, and before the second period, the lumen of the first prosthetic valve has a first diameter, and
the prosthetic valve support is configured such that, after the second period, the lumen of the second prosthetic valve has a diameter that is at least as great as the first diameter.
In an application, the prosthetic valve support is configured such that, after the second period, the lumen of the second prosthetic valve has a diameter that is greater than the first diameter.
In an application, the prosthetic valve support includes a weak zone that circumscribes and defines the lumen, and is configured to facilitate enlarging of the lumen.
In an application, the prosthetic valve support is configured to facilitate enlarging of the lumen by being configured to be deformed by a radially-expansive force applied from within the lumen.
In an application, the prosthetic valve support includes a cylindrical element:
shaped to define the lumen,
configured to receive the first prosthetic valve at a first portion of the lumen, and
configured to receive the second prosthetic valve support at a second portion of the lumen.
In an application, the cylindrical element is configured to receive the first prosthetic valve at a first longitudinal portion of the lumen, and to receive the second prosthetic valve at a second longitudinal portion of the lumen.
There is further provided, in accordance with an application of the present invention, apparatus for use with a prosthetic heart valve for implantation at a native heart valve of a subject, the apparatus including:
a core, shaped to define at least one conduit therethrough; and
one or more control filaments, slidable through the conduit, and reversibly couplable to the prosthetic valve,
the apparatus being configured such that sliding the control filaments in a first direction through the conduit facilitates expansion of the prosthetic valve, and sliding the control filaments in a second direction through the conduit facilitates compression of the prosthetic valve.
In an application, the apparatus is configured such that sliding the control filaments in the first direction through the conduit facilitates radial expansion of the prosthetic valve away from the core.
In an application, the apparatus further includes the prosthetic valve, a delivery tube and a pushing member, and:
the prosthetic valve has an expanded configuration and a compressed configuration,
the delivery tube is configured to be transluminally delivered to the native valve,
the pushing member includes the core,
the pushing member is configured:
In an application, the apparatus further includes one or more release wires, configured to facilitate decoupling of the control filaments from the prosthetic valve.
In an application, the apparatus further includes one or more guide elements, radially extendable from the core, and configured to guide expansion of the prosthetic valve away from the core.
In an application, the guide elements are configured to automatically radially retract when the control filaments are decoupled from the prosthetic valve.
There is further provided, in accordance with an application of the present invention, apparatus for use at a native heart valve of a subject, the apparatus including:
a prosthetic valve, configured to be transluminally delivered to, and implantable at, the native valve of the subject;
a prosthetic valve support, configured to be transluminally delivered to the native valve of the subject, and to facilitate implantation of the prosthetic valve;
at least one coupling lead, extending between the prosthetic valve and the prosthetic valve support; and
a ratchet housing, slidably coupled to the coupling lead, and configured to be slidable over the coupling lead in a first direction, and inhibited from sliding over the coupling lead in an opposite direction,
the apparatus being configured such that sliding of the ratchet housing over the coupling lead in the first direction facilitates coupling of the prosthetic valve to the prosthetic valve support.
In an application, the coupling lead extends between a proximal portion of the prosthetic valve, and the prosthetic valve support.
In an application, the prosthetic valve support includes one or more support-anchoring elements, configured to couple the prosthetic valve support to the native valve, and the coupling lead extends between the prosthetic valve and the support-anchoring elements.
There is further provided, in accordance with an application of the present invention, apparatus for use with a native heart valve of a subject, the apparatus including:
a first expandable prosthetic valve component, including a crimpable frame, and configured to be transcatheterally advanceable toward the native valve while the first prosthetic valve component is in a crimped state thereof;
a second expandable prosthetic valve component, including a crimpable frame, and configured to be transcatheterally advanceable toward the native valve, placeable in the native valve while the second prosthetic valve component is in a crimped state thereof, and couplable to the first prosthetic valve component, expansion of the second prosthetic valve component facilitating coupling of the second prosthetic valve component to the first prosthetic valve component; and
one or more tissue-engagement elements, coupled to at least one of the prosthetic valve components, the tissue-engagement elements configured, when the prosthetic valve component is in an expanded state thereof, to extend from the prosthetic valve component, and to inhibit a proximal movement of the prosthetic valve component.
There is further provided, in accordance with an application of the present invention, apparatus for use with a prosthetic valve for implantation at a native valve of a subject, the native valve (1) defining an orifice, (2) including at least one native leaflet, having a native beating, and (3) having a native blood flow regulation functionality, the apparatus including:
For some applications, techniques described herein are practiced in combination with techniques described in one or more of the references cited in the Background section and Cross-references section of the present patent application.
Reference is made to
Support 40 is held against the annulus of native valve 23 (e.g., by holding members 46) such that the lumen of support 40 aligns with the lumen of the native valve, and such that atrium 26 and ventricle 28 remain in fluid communication.
Following the positioning of support 40 against the annulus of the native valve, prosthetic valve 42 is percutaneously (e.g., transcatheterally) advanced and delivered toward the native valve, typically along guidewire 45, as shown in
Prosthetic valve 42 is typically expandable, and typically comprises a wire frame which comprises a shape-memory material such as, but not limited to, nickel titanium (nitinol). For some applications of the invention, prosthetic valve 42 comprises nickel cobalt, stainless steel and/or titanium. During the advancing, prosthetic valve 42 is disposed in a distal portion of a delivery tube 60, which holds the prosthetic valve in a compressed (e.g., crimped) configuration. Delivery tube 60 is slidably advanceable within overtube 44. Prosthetic valve 42 is typically delivered through the native valve and into ventricle 28, as shown in
Typically, a plurality of tissue-engaging elements 62 are disposed at a distal portion of the primary structural element 130 of prosthetic valve 42. For applications in which prosthetic valve 42 comprises tissue-engaging elements 62, tissue-engaging elements 62 comprise valve-anchoring elements 64. For such applications of the present invention, primary structural element 130 of prosthetic valve 42 is generally cylindrical (e.g., shaped so as to define a right circular cylinder), and anchoring elements 64 protrude radially from a surface of the cylinder. It is to be noted that although prosthetic valve 42 is shown comprising tissue-engaging elements 62, the scope of the present application includes prosthetic valves with no tissue-engaging elements 62.
Following the capturing of native leaflets 82, prosthetic valve 42 is then fully exposed from within delivery tube 60 (by pushing valve 42 relative to delivery tube 60 or by retracting delivery tube 60 with respect to valve 42) and is allowed to expand further.
For some applications of the present invention, support 40 prevents valve 42 from expanding to assume a fully-expanded configuration (i.e., a configuration to which valve 42 would otherwise expand without being impeded by support 40 or tissue). In such applications, the radial force exerted by support 40 on valve 42 facilitates coupling and sealing between support 40 and valve 42 (for example, by increasing friction between support 40 and valve 42), and facilitates implantation of implant 30 at native valve 23.
Typically, when deployed as shown, prosthetic valve 42 is configured to be aligned with the native valve such that valve-anchoring elements 64 protrude toward, and engage leaflets 82 of the native valve. In some applications of the present invention, valve-anchoring elements 64 protrude toward, and engage, commissures 84 of the native valve. In some applications of the invention, a single valve-anchoring element 64 is disposed on each side of the prosthetic valve. It is to be noted that the scope of the present application includes any other suitable arrangement of valve-anchoring elements 64 with respect to valve 42. Typically, valve-anchoring elements 64 capture leaflets 82 of the native valve, holding them clear of the flow of blood through the prosthetic valve and the left ventricular outflow tract (LVOT).
For clarity of illustration, the lumen defined by prosthetic valve 42 is shown as being empty, such that ventricle 28 is visible. However, as described hereinabove, prosthetic valve 42 typically comprises valve components (e.g., prosthetic valve leaflets, not shown in
Reference is again made to
For other applications, prevention of proximal migration of valve 42 is maintained, while movement of native leaflets 82 with respect to prosthetic valve 42 is allowed. For example, valve-anchoring elements 64 may have the aforementioned functionalities by having lengths of less than 5 mm, and/or by having a total width of each cluster of valve-anchoring elements (corresponding to respective leaflets of the native valve) being less than 5 mm. For example, the valve may include a single valve-anchoring element 64 corresponding to each leaflet of the native valve, the width of each of the single valve-anchoring elements being less than 1 mm. Thus, the valve may be stopped from proximally migrating into the atrium by the valve-coupling elements preventing the distal end of the valve from migrating further proximally than edges of native leaflets of the valve. Furthermore, the valve-anchoring elements may allow movement of the native leaflets with respect to the prosthetic valve by not generally squeezing the native leaflets between the valve-coupling elements and primary structural element 130 of the prosthetic valve. In other applications of the invention, prosthetic valve support 40 comprises support-anchoring elements (such as clips), and is directly coupled to the native valve. For some such applications, no valve-anchoring elements are used; rather, implant 30 is coupled to the native valve via prosthetic valve support 40 (e.g., as described hereinbelow, such as with reference to
For some applications of the invention, the implantation of implant 30 follows an alternative order to that described with reference to
For some applications of the invention, valve-anchoring elements 64 anchor prosthetic valve 42 to the native valve in a manner that restricts both proximal and distal movement of the prosthetic valve. For such applications of the invention, deployment of prosthetic valve 42 may occur in the reverse orientation, such that, following positioning in the native valve of prosthetic valve 42 compressed in delivery tube 60, the delivery tube is moved distally (i.e., ventricularly) as prosthetic valve 42 is deployed from the delivery tube. Delivery tube 60 is then removed from the subject via the lumen of the deployed prosthetic valve. It is hypothesized that this approach facilitates maneuvering of implant components and delivery apparatus, both for delivery of implant 30 and for withdrawal of delivery apparatus. For example, this approach is hypothesized to require less space on the proximal side of the native valve (e.g., in the atrium), compared to techniques whereby the prosthetic valve is deployed from the proximal side of the native valve. An example of this approach is described with reference to
For some applications of the invention, surfaces of one or more components of implant 30 are covered at least in part with a covering (not shown). For example, surfaces of prosthetic valve support 40 and prosthetic valve 42 may be covered so as to direct substantially all blood flowing through the valve, to flow through the lumen of prosthetic valve 42. For some applications, the surface of prosthetic valve support 40 (or another component) that is placed in contact with the native valve is covered; the covering is configured to facilitate coupling of support 40 to the native valve, by enhancing fibrosis at the interface between the prosthetic valve support and the native valve.
The covering may comprise polyethylene terephthalate (e.g., polyester), polytetrafluoroethylene (e.g., Teflon, ePTFE), or pericardial tissue. Typically, a thickness of the covering is less than 0.2 mm, e.g., less than 0.1 mm, or less than 0.05 mm.
For some applications, one or more dimensions of native valve 23 (e.g., of leaflets 82, and/or of the annulus of the native valve) is measured (e.g., by using imaging techniques) prior to deployment of valve 42. Taking this measuring into account, a suitably-sized prosthetic valve is chosen to be placed in the annulus, in a manner in which a cross-sectional area of the prosthetic valve in its deployed state is less than 90% (e.g., less than 80%, or less than 60%) of the area defined by the annulus.
For some applications, the cross-sectional area of the prosthetic valve in its deployed state has a longest length of less than 25 mm, e.g., less than 20 mm, and/or more than 15 mm, e.g., 15-25 mm. For some applications, placing a prosthetic valve inside the native valve, with the dimensions of the native valve annulus and the prosthetic valve as described, facilitates sealing of the prosthetic valve with respect to the native valve, by the native valve leaflets closing around the outer surface of the prosthetic valve. In such applications, prosthetic valve 42 is implanted directly within native valve 23 (i.e., without support 40).
For some applications, prosthetic valve support 40, that is shaped to define a lumen, is placed against the annulus of native valve 23 (e.g., as described with reference to
Typically, placing a prosthetic valve inside the native valve with the dimensions of the native valve annulus, the prosthetic valve 42, and/or valve support 40 as described in the above paragraphs, facilitates sealing of the prosthetic valve with respect to the native valve. For some applications, the sealing is facilitated by the native leaflets being pushed against, and closing against, the outer surface of the frame of the valve during systole, in a similar manner to the manner in which native valve leaflets coapt during systole, in a healthy mitral valve.
Typically, as the diameter of the prosthetic valve is increased, the proportion of the native leaflets that is pushed against the outer surface of the valve during systole is increased, thereby enhancing the sealing of the native leaflets with respect to the frame of the prosthetic valve. However, beyond a given diameter, as the diameter of the prosthetic valve is increased, the native valve leaflets are pushed apart at the commissures, thereby causing retrograde leakage of blood through the commissures. Therefore, in accordance with some applications of the present invention, prosthetic valve 42, and/or valve support 40 are chosen such that the cross-sectional area of the prosthetic valve (when expanded inside the valve support) is less than 90% (e.g., less than 80%, or less than 60%) of the area defined by the annulus of native valve 23. Thus, the valve support facilitates additional sealing of the prosthetic valve with respect to the native valve, by the native valve leaflets closing around the outer surface of the prosthetic valve, while not causing retrograde leakage of blood through the commissures.
For some applications, in order to facilitate the sealing of the native valve around the outer surface of the prosthetic valve, a material is placed on the outer surface of the prosthetic valve in order to provide a sealing interface between the prosthetic valve and the native valve. For example, a smooth material that prevents tissue growth (e.g., polytetrafluoroethylene (PTFE), and/or pericardium) may be placed on the outer surface of the prosthetic valve. Alternatively or additionally, a material that facilitates tissue growth (such as polyethylene terephthalate; PET) may be placed on the outer surface of the prosthetic valve, in order to (a) act as a sealing interface between the native valve and the prosthetic valve, and (b) facilitate tissue growth around the prosthetic valve to facilitate anchoring and/or sealing of the prosthetic valve.
For some applications, one or more dimensions of native valve 23 (e.g., of leaflets 82, and/or of the annulus of the native valve) are measured (e.g., by using imaging techniques) prior to deployment of prosthetic valve 42 and/or prosthetic valve support 40. Taking this measuring into account, a suitably-sized and/or suitably-configured prosthetic valve and/or prosthetic valve support is selected for implantation. For example, a prosthetic valve or prosthetic valve support comprising tissue-engaging elements 62 with appropriate configurations and/or dimensions may be selected.
Reference is made to
For some applications of the invention, at least part of holding wire 522 is disposed in a connector 540, which further couples coupling portion 70 to upstream support portion 41. Holding wire 522 may be slidable through connector 540. For some applications, connector 540 is more rigid than holding wire 522.
Reference is made to
As described with reference to
It is hypothesized that adjusting the position of coupling portion 70 of support-anchoring elements 66f, with respect to upstream support portion 41 of prosthetic valve support 40f, allows prosthetic valve support 40f to be adapted to the anatomy of the subject during and/or subsequent to the implantation procedure.
Reference is made to
As described with reference to
It is hypothesized that adjusting the position of coupling portion 70 of support-anchoring elements 66g, with respect to upstream support portion 41 of prosthetic valve support 40g, allows prosthetic valve support 40g to be adapted to the anatomy of the subject during and/or subsequent to the implantation procedure.
Reference is made to
It is hypothesized that adjusting the position of coupling portion 70 of support-anchoring elements 66h, with respect to upstream support portion 41 of prosthetic valve support 40h, allows prosthetic valve support 40h to be adapted to the anatomy of the subject during and/or subsequent to the implantation procedure.
Reference is made to
Reference is made to
Reference is made to
Reference is now made to
Reference is made to
As described hereinabove, prosthetic valve 42 is deployed by distal movement out of delivery tube 60.
In the expanded state of support-engaging elements 424, the radially-protruding proximal portions thereof typically define a cross-sectional area, the longest dimension of which is typically longer than a transverse cross-sectional longest dimension of the lumen defined by prosthetic valve support 40. That is, in the expanded state, support-engaging elements 424 increase a longest transverse cross-sectional length of prosthetic valve 42a, such that the longest transverse cross-sectional length is longer than a longest transverse cross-sectional length of the lumen defined by prosthetic valve support 40. Thereby, the radially-protruding support-engaging elements 424 restrict proximal movement of prosthetic valve 42a with respect to prosthetic valve support 40, thereby anchoring prosthetic valve 42a to the distal side of prosthetic valve support 40, and to native valve 23.
Reference is made to
In some applications of the invention, support 142 is shaped to define a plate 148 at the proximal end of support 142. The dimensions and relative positions of support 142, tabs 146, and plate 148 may be adjusted for the specific medical device 150 to be deployed using delivery apparatus 438. Support 142 is shaped to define a plurality of conduits 492 (e.g., holes). Delivery apparatus 438 further comprises one or more control filaments, such as retrieval wires 490, slidably disposed in conduits 492. Typically, conduits 492 provide communication between a proximal side of support 142 and a circumference of the support, such that a proximal end of each retrieval wire 490 is disposed at a site proximal to delivery tube 154, and a distal end of each wire is reversibly coupled to medical device 150, retrieval wires 490 extending through conduits 492.
For some applications of the invention, retrieval wires 490 are coupled to medical device 150 by being looped around parts of the medical device (e.g., looped around a strut of the lattice structure, as shown in
Prosthetic valve 42 and pushing member 140 are disposed within the lumen of delivery tube 154. Delivery tube 154 restricts expansion of prosthetic valve 42, thereby holding the proximal portion of prosthetic valve 42 around core 144 of pushing member 140, in the configuration described herein. Coupling tabs 146 restrict movement of prosthetic valve 42 with respect to pushing member 140. Delivery tube 154 therefore facilitates coupling of prosthetic valve 42 to pushing member 140 via coupling tabs 146. In applications of the invention where pushing member 140 is shaped to define plate 148, the plate typically further facilitates this coupling by restricting proximal movement of prosthetic valve 42 with respect to the pushing member (i.e., by functioning as a cap). Thereby, in the compressed configuration thereof, prosthetic valve 42 is configured to be fixedly coupled to pushing member 140.
A control tube 152 is typically coupled at a distal end thereof to pushing member 140 (e.g., control tube 152 is coupled to support 142). Control tube 152 is shaped so as to define a lumen through which a guidewire tube 153 passes, and control tube 152 is slidable with respect to and along guidewire tube 153. Guidewire tube 153 houses guidewire 45 described hereinabove. Control tube 152 is slidably disposed within a lumen of an overtube 155.
Reference is again made to
Should it be necessary and/or desirable during deployment, until medical device 150 (e.g., prosthetic valve 42) is released from pushing member 140 (i.e., while the proximal portion of medical device 150 is crimped within delivery tube 154), the deployed, expanded portions of medical device 150 (i.e., the portions of medical device 150 that are exposed from delivery tube 154) may be drawn back into delivery tube 154 (e.g., for repositioning or withdrawal of the medical device).
Subsequent to deployment of prosthetic valve 42, should it be necessary and/or desirable, the prosthetic valve may be drawn back against support 142 (e.g., radially inward) by proximally pulling retrieval wires 490. Subsequently, prosthetic valve 42 may be drawn back, along with pushing member 140, into delivery tube 154. That is, for some applications, prosthetic valve 42 is recompressible (i.e., the expansion of prosthetic valve 42 is at least in part reversible) by proximal retraction of retrieval wires 490.
That is, (1) retrieval wires 490 are slidable through conduits 492 of core 144, and reversibly couplable to prosthetic valve 42, and (2) delivery apparatus 438 is configured to control and/or facilitate (a) expansion of prosthetic valve 42, by the retrieval wires being advanced distally through the conduits, and (b) recompression of prosthetic valve 42, by the retrieval wires being retracted proximally through the conduits.
Reference is now made to
Reference is made to
Prosthetic valve support 40a is typically covered with a covering 440, such as a fabric. Covering 440 may comprise polyethylene terephthalate (e.g., polyester), polytetrafluoroethylene (e.g., Teflon, ePTFE), or pericardial tissue. Typically, a thickness of covering 440 is less than 0.2 mm, e.g., less than 0.1 mm, or less than 0.05 mm. When support 40a is supplied and/or implanted, covering 440 typically covers support 40a such that only a first lumen 444 is open and configured to receive a prosthetic valve, and the second lumen 446 is closed. That is, the wire frame of support 40a defines two or more lumens but the covering defines only one lumen, thereby covering 440 functions as a seal 442.
In some applications of the invention, covering 440 is not disposed over second lumen 446; rather a different element functions as seal 442. For example, a weaker and/or softer material (e.g., pericardial tissue) or a removable plug may be coupled to prosthetic valve support 40a, and disposed over second lumen 446 to function as seal 442.
Implant 30, comprising prosthetic valve 42 and prosthetic valve support 40a, is implanted in native valve 23 (e.g., as described with reference to
For some applications of the invention, following the deployment of the second prosthetic valve, the first prosthetic valve (i.e., prosthetic valve 42) is disabled (e.g., sealed). For example, an expandable plug may be expanded in the lumen of the first prosthetic valve.
Prosthetic cardiac valves typically require replacement after several years (e.g., after 2-20 years, such as after 5-10 years). For example, the condition of the subject may change and/or components of the prosthetic valve (e.g., prosthetic valve leaflets) may suffer fatigue. It is hypothesized that multi-lumen prosthetic valve support 40a allows a second prosthetic valve to be implanted in the native valve, the second prosthetic valve being supported by the originally-implanted prosthetic valve support 40a. The first prosthetic valve may be sealed, for example, if the original prosthetic valve allows, or is predicted to allow, retrograde leakage. Implantation of a second prosthetic valve is hypothesized to increase the lifespan of implant 30.
Reference is made to
Prosthetic valve support 40e is typically covered with a covering 440, such as a fabric. Covering 440 may comprise polyethylene terephthalate (e.g., polyester), polytetrafluoroethylene (e.g., Teflon, ePTFE), or pericardial tissue. Typically, a thickness of covering 440 is less than 0.2 mm, e.g., less than 0.1 mm, or less than 0.05 mm. When support 40e is supplied and/or implanted, covering 440 typically covers support 40e such that secondary region 449 is closed. That is, the wire frame of support 40e defines a generally elongated lumen 448, whilst covering 440 defines a generally round primary region 447. In this manner, covering 440 functions as a seal 442 over secondary region 449.
In some applications of the invention, covering 440 is not disposed over secondary region 449; rather a different element functions as seal 442. For example, a weaker and/or softer material (e.g., pericardial tissue) or a removable plug may be coupled to prosthetic valve support 40e, and disposed over secondary region 449, so as to function as seal 442.
Implant 30, comprising prosthetic valve 42 and prosthetic valve support 40e, is implanted in native valve 23 (e.g., as described with reference to
Typically, expansion of the second prosthetic valve during deployment deforms the first prosthetic valve (i.e., a radially-expansive force of the second prosthetic valve is stronger than that of the first prosthetic valve). For example, following deployment of the second valve, the first valve may assume a lune shape or a generally semicircular shape. In some applications of the invention, the second prosthetic valve is shaped to fit into secondary region 449 without deforming the first prosthetic valve.
Prosthetic cardiac valves typically require replacement after several years (e.g., after 2-20 years, such as after 5-10 years). For example, the condition of the subject may change and/or components of the prosthetic valve (e.g., prosthetic valve leaflets) may suffer fatigue. It is hypothesized that extended-lumen prosthetic valve support 40 allows a second prosthetic valve to be implanted in the native valve, the second prosthetic valve being supported by the originally-implanted prosthetic valve support 40. The first prosthetic valve may be sealed, as described hereinabove, for example, if the original prosthetic valve allows, or is predicted to allow, retrograde leakage. Implantation of a second prosthetic valve is hypothesized to increase the lifespan of implant 30.
Reference is made to
For some applications, prosthetic valve support 40b and prosthetic valve 42 are implanted as described herein (e.g., with reference to
Reference is made to
It is hypothesized that over a period of time (e.g., a week, e.g., a month, e.g., a year) following implantation of implant 30 comprising support 40c, movement of leaflets 82 is reduced (e.g., due to tissue growth and/or calciferous deposits), such that the functionality of native valve 23 is gradually reduced, and the proportion of blood that flow through prosthetic valve 42, relative to that which flows around the prosthetic valve, is increased. That is, over time, prosthetic valve 42 takes over the function of native valve 23.
Reference is made to
Reference is made to
Reference is made to
In some applications of the invention, support-anchoring elements 66 are configured and/or arranged so as to anchor prosthetic valve support 40 to the native valve (e.g., by engaging leaflets 82, and/or commissures 84, and/or chordae tendineae 80), whilst allowing leaflets 82 to continue to function, at least in part.
In some applications of the invention, should it be necessary and/or desirable, support 40 is retrievable before it is fully deployed, by withdrawing the support proximally, back into overtube 44.
In some applications, should it be necessary and/or desirable, support 40 is retrievable after it has been fully deployed. For example, support 40 may be drawn back around and against a pushing member of delivery apparatus, recompressing support 40 for withdrawal into a delivery tube, in a similar way to the technique described with reference to
Reference is made to
For some applications, coupling portions 70 engage (e.g., are coupled to) leaflets 82 and/or commissures 84 of native valve 23 while prosthetic valve support 40 is still in a partially-deployed configuration (e.g., as described with reference to
In the applications of the invention described with reference to
Typically, adjustment and/or other manipulation of support-anchoring elements 66, comprising length-adjustable holding elements 600, may be performed prior to the implantation procedure, e.g., following imaging-based sizing of one or more dimensions of native valve 23 (e.g., of leaflets 82, and/or of the annulus of the native valve), and/or during the implantation procedure (e.g., when the prosthetic valve support is at the site of implantation).
For some applications of the invention, stretchable holding element 600q further comprises a limiting wire 604, typically coupled to upstream support portion 41 and coupling portion 70. Limiting wire 604 is generally non-elastic, and is configured to limit the expansion (i.e., stretching) of holding element 600q. For example, limiting wire may be configured to prevent overstretching of holding element 600q, e.g., to prevent failure of the holding element. Typically, limiting wire 604 is longer than the length of elastic tube 602 in the relaxed (i.e., contracted) configuration thereof, and is shorter than the length of elastic tube 602 in a maximally-expanded (i.e., maximally-stretched) configuration thereof. In the relaxed (i.e., contracted) configuration of elastic tube 602, limiting wire 604 is typically loose (e.g., generally bent, crumpled, flexed). When elastic tube 602 is expanded (i.e., stretched), limiting wire 604 typically becomes taut (e.g., generally straight), thereby limiting the expansion of elastic tube 602 to generally the length of limiting wire 604.
It is to be noted that the scope of the present invention includes the use of limiting wire 604 in combination with other length-adjustable holding elements including, but not limited to, stretchable holding element 600n, described with reference to
When spring 610 is released from restrictor 612, the spring relaxes (i.e., contracts), and provides a pulling force that sandwiches the native valve between support 40u and coupling portion 70, e.g., as described hereinabove, mutatis mutandis.
Reference is made to
Reference is again made to
Reference is again made to
Typically, telescopic holding element 600t further comprises another element (not shown), which controls and/or adjusts the sliding of the cylinders described hereinabove. For example, element 600t may comprise a tension spring, such as those described with reference to
Reference is made to
Non-limiting examples of materials which strap 630 and/or strap adjuster 632 may comprise, include polyester, PTFE (e.g., ePTFE), nylon, cotton, nitinol, stainless steel, nickel cobalt, and cobalt chrome.
Reference is made to
For some applications, a kit is provided, containing a plurality of prosthetic valve supports 40, each prosthetic valve support comprising a flexible support-anchoring element 720 having a different configuration of material 722 and filaments 724, and thereby a different flexibility (e.g., elements 720a-720f). A user typically selects a support 40 that comprises a support-anchoring element 720 of a desired configuration for a particular application.
For some applications, a kit is provided, containing (1) at least one prosthetic valve support 40 (i.e., upstream support portion 41), and (2) a plurality of flexible support-anchoring elements 720, each element 720 having a different configuration of material 722 and filaments 724, and thereby a different flexibility. A user typically (1) selects a support-anchoring element 720 of a desired configuration for a particular application, and (2) couples the selected element 720 to the upstream support portion 41.
For some applications, a kit is provided, containing (1) at least one prosthetic valve support 40 (i.e., upstream support portion 41), (2) at least one coupling portion 70, and (3) a plurality of connectors 540, each connector 540 having a different configuration of material 722 and filaments 724, and thereby a different flexibility. A user typically (1) selects a connector 540 of a desired configuration for a particular application, and (2) couples the selected connector 540 to the coupling portion 70, and to the upstream support portion 41.
Reference is made to
Inflatable support-engaging element 426 is typically coupled to prosthetic valve 42 such that the prosthetic valve is compressible (i.e., crimpable) for delivery, as described hereinabove. For some applications, inflatable support-engaging element 426 is coupled to the prosthetic valve using sutures. Typically, such sutures are arranged in a single circumferential suture line, so as to facilitate deformation (e.g., flattening) of element 426 during crimping of the prosthetic valve for delivery. For some applications, element 426 is coupled to the prosthetic valve using an adhesive.
For some applications of the invention, prosthetic valve 42j is deployed in the lumen of support 40, such that element 426 is disposed on the proximal side of support 40. It is hypothesized that, when in this position and inflated, element 426 restricts distal movement of the prosthetic valve with respect to the support.
For some applications of the invention, prosthetic valve 42j is deployed in the lumen of support 40, such that element 426 is planar with upstream support portion 41 of the support, and such that at least part of element 426 is disposed proximal to portion 41, and at least part of element 426 is disposed distal to portion 41. It is hypothesized that, when in this position and inflated, element 426: (1) applies a radially-expansive force on support 40 (i.e., supplements radially-expansive forces applied by prosthetic valve 42 on support 40), and (2) restricts proximal and distal movement of the prosthetic valve with respect to the support.
Reference is made to
Reference is made to
Reference is made to
For some applications, prosthetic valve is provisionally expanded (1) sufficiently such that elements 422 protrude into pocket 420 and prevent axial movement of prosthetic valve 42, but (2) insufficiently for radially-expansive forces to fixedly couple the prosthetic valve to prosthetic valve support 40w. In this configuration, a user may rotate the prosthetic valve to a desired orientation, before finally allowing the prosthetic valve to expand and become coupled to support 40w.
Reference is made to
Reference is made to
Reference is made to
Reference is again made to
Reference is made to
Throughout the deployment of prosthetic valve support 860, until the release of one end of drawstring 864, support 860 may be retrieved by moving drawstring 864 proximally (i.e., pulling the drawstring). Pulling the drawstring (1) tightens the loop formed by the drawstring, thereby bringing rings 866 closer to each other, and compressing the proximal portion of support 860, and (2) draws support 860 into overtube 44. Thus, a user can determine if and/or when to release support 860, throughout the deployment procedure.
Reference is made to
Apparatus 880 has a contracted configuration and an extended configuration, is typically reversibly movable between these two configurations, and is further typically movable into continuous configurations between the contracted and extended configurations.
As described hereinabove, prosthetic valve 42 typically comprises a shape-memory material, and expands toward its expanded configuration as it is exposed from delivery tube 60. In the application of the invention described with reference to
Control filaments 882 (e.g., proximal portions thereof) are distally advanceable, and proximally retractable, through a control tube 890, e.g., using a control unit external to the subject. Control filaments 882 are slidably couplable to core 886 and/or control tube 890, such as being slidable through respective conduits (e.g., holes) in the core or the control tube. The expansion of apparatus 880, and thereby that of prosthetic valve 42, is restricted and/or facilitated (e.g., controlled) by the distal advancement and/or proximal retraction of control filaments 882. In the application of the invention illustrated in
When prosthetic valve 42 is successfully positioned (i.e., when a user determines that the prosthetic valve is in the desired position), prosthetic valve 42 is released from control filaments 882, e.g., by pulling release wires 892 proximally. Release of prosthetic valve 42 allows (1) the prosthetic valve to expand further (e.g., until it couples to, and is restricted by, support 40), and/or (2) control filaments 882 to be retracted, and rail-pairs 884 to be telescopically retracted, such that apparatus 880 is retractable into delivery tube 60.
For some applications, rail-pairs 884 are biased toward moving into the contracted configuration thereof, are pulled radially outward by the expansion of prosthetic valve 42, and automatically return to the contracted configuration upon release of the prosthetic valve. For example, the rail-pairs may provide a contractive force, and the prosthetic valve may provide an expansive force that is sufficient to overcome the contractive force, and thereby to pull the rail-pairs radially outward. Upon release of the prosthetic valve, the contractive force automatically returns the rail-pairs to the contracted configuration thereof. Alternatively or additionally, rail-pairs 884 may be actively controllable (e.g., extracorporeally) by a user.
For some applications of the invention, proximal portions of control filaments 882 are coupled to each other (e.g., fixedly coupled to each other, such as adhered and/or welded to each other), such that the plurality of control filaments are synchronously distally advanceable, and synchronously proximally retractable, e.g., via a control rod and/or control unit.
For some applications of the invention, proximal portions of release wires 892 are coupled to each other (e.g., fixedly coupled to each other, such as adhered and/or welded to each other), such that the plurality of release wires are pullable synchronously, e.g., via a control rod and/or control unit, thereby facilitating synchronous release of control filaments 882.
Throughout the deployment of prosthetic valve 42 using apparatus 880, until the release of the prosthetic valve from control filaments 882, prosthetic valve 42 may be re-compressed (e.g., for repositioning and/or retrieval into delivery tube 60) by proximally retracting control filaments 882. Thus, a user can determine if and/or when to release prosthetic valve 42, throughout the deployment procedure. That is, prosthetic valve 42 is recompressible (i.e., the expansion of prosthetic valve 42 is at least in part reversible) by proximal retraction of control filaments 882.
That is, (1) control filaments 882 are slidable through conduits of core 886, and reversibly couplable to prosthetic valve 42, and (2) delivery apparatus 880 is configured to control and/or facilitate (a) expansion of prosthetic valve 42, by the control filaments being advanced distally through the conduits, and (b) recompression of prosthetic valve 42, by the control filaments being retracted proximally through the conduits.
Reference is made to
Prosthetic cardiac valves typically require replacement after a duration (e.g., after between 1 month and 10 years, such as after between 1 and 5 years). For example, the condition of the subject may change, components of the prosthetic valve (e.g., prosthetic valve leaflets, sutures, frame) may suffer fatigue, and/or tissue growth may block blood flow or otherwise interfere with prosthetic valve function.
The prosthetic valve supports described with reference to
Reference is now made to
Reference is now made to
For some applications, wire frame 672 does not extend into weak zone 670; rather the weak zone only comprises covering 440. For some applications, a stretchable and/or breakable reinforcing-wire 674 is disposed at or near inner edge 68 of upstream support portion 41 of support 40x. For some applications, wire frame 672 has a different structure in weak zone 670 than in other regions of upstream support portion 41 of support 40x. For example, wire frame 672 may comprise fewer struts in weak zone 670.
The radially-expansive force applied by balloon 678 increases the lumen of prosthetic valve 42, typically by increasing the lumen of support 40x by deforming (e.g., crushing) weak zone 670. For example, a material which weak zone 670 comprises may be compressed, broken, bent, stretched and/or torn (e.g., reinforcing wire 674 may be broken and/or covering 440 may be stretched and/or torn). Balloon 678 is subsequently removed from the subject. Typically, leaflets 660 continue to function at least in part until second prosthetic valve 42′ is deployed.
For some applications, leaflets 660 are disposed in a portion of prosthetic valve 42 that is distal (i.e., ventricular) to the portion of prosthetic valve 42 that is coupled to prosthetic valve support 40x. For these applications, balloon 678 is typically disposable in a proximal portion of valve 42, and thereby may be used to increase the lumen of prosthetic valve 42, without damaging (e.g., crushing) leaflets 660.
Reference is again made to
For some applications, a distal portion of prosthetic valve 42′ defines a cross-sectional area with a longest length that is longer than a transverse cross-sectional longest dimension of the lumen defined by prosthetic valve 42 (i.e., defined by primary structural element 130 of prosthetic valve 42). During deployment of prosthetic valve 42′, the distal portion is placed distal to the open distal end of prosthetic valve 42 (i.e., in the ventricle). Thereby, in addition to the radially-expansive force that typically couples prosthetic valve 42′ to prosthetic valve 42, the distal portion restricts proximal movement of prosthetic valve 42′ with respect to prosthetic valve 42, thereby anchoring prosthetic valve 42′ to prosthetic valve 42, and to native valve 23.
Reference is made to
For some applications, prosthetic valve 42 continues to function at least in part, and at least temporarily. That is, prosthetic valve 42 and prosthetic valve 42′ operate generally simultaneously. For some applications, prosthetic valve 42 is disabled in conjunction with deployment of prosthetic valve 42′. For example, leaflets 660 of prosthetic valve 42 may be disabled, removed and/or restrained, by using a separate device (not shown) and/or by using a part (e.g., an extending element; not shown) of prosthetic valve 42′.
For some applications, the primary structural element 130 of prosthetic valve 42′ is longer than the primary structural element of prosthetic valve 42, and the leaflets of prosthetic valve 42′ are disposed in a proximal portion of the primary structural element thereof. A distal portion of the primary structural element of prosthetic valve 42′ is deployed in the lumen of prosthetic valve 42, such that the leaflets of prosthetic valve 42 are crushed upon expansion of prosthetic valve 42′.
Reference is made to
Reference is made to
Although element 760 is described with reference to
Reference is made to
Reference is made to
Element 900 typically has (1) an open configuration, in which leaflets 82 of the native valve may be moved between the two clip elements, and (2) a closed configuration, in which the clip elements typically clamp (i.e., couple to) the leaflets. Element 900 is typically moved between the open and closed configurations thereof (i.e., is opened and closed) by moving at least one clip element between the first configuration thereof, and the other configuration thereof.
Typically, the clip elements are disposed at a distal portion of each support-anchoring element 900, and a proximal portion (e.g., a proximal end) of each element 900 is coupled to upstream support portion 41. Typically, support-anchoring elements 900 have a length (i.e., a distance from (1) the point of coupling of the element 900 to upstream support portion 41, to (2) a distal end of the element 900) of between 3 and 20 mm, (e.g., between 5 and 12 mm). Typically, the proximal portion has a length (i.e., a distance between (1) the point of coupling of element 900 to upstream support portion 41, and (2) a clip element) of between 2 and 10 mm, (e.g., between 2 and 8 mm).
Support 1040 typically comprises two support-anchoring elements 900 and two stabilizing legs 910. Typically, elements 900 and legs 910 are disposed at inner edge 68 in an alternating manner, i.e., such that each leg 910 is between two elements 900, and each element 900 is between two legs 910.
Typically, stabilizing leg 910 is longer than support-anchoring element 900. That is, a distance between (1) a coupling point 911 of upstream support portion 41 and a stabilizing leg 910 and (2) a distal end of the stabilizing leg, is typically greater than a distance between (1) a coupling point of upstream support portion 41 and an element 900 and (2) a distal end of the element 900. Typically, stabilizing leg 910 has a length of between 5 mm and 30 mm (e.g., between 5 mm and 20 mm), and a width of between 0.4 mm and 5.0 mm.
For some applications of the invention, each stabilizing leg 910 comprises a proximal portion 912 and a distal portion 914, whereby the proximal portion is coupled at coupling point 913 between the stabilizing leg and the distal portion. For some such applications, stabilizing leg 910 comprises a bend, such that an axis defined by distal portion 914 is divergent to an axis defined by the proximal portion. Typically, proximal portion 912 has a length of between 5 mm and 20 mm.
Typically, stabilizing legs 910 have a stabilizing configuration, in which they stabilize prosthetic valve support 1040 at the native valve. Typically, in the stabilizing configuration, the proximal portion 912 of each leg 910 is disposed on a plane between (1) a plane that is orthogonal to a plane defined by upstream support portion 41, and (2) a position in which the leg touches a part of upstream support portion 41 that is peripheral to inner edge 68. That is, in the stabilizing configuration, proximal portion 912 typically forms an acute angle with a portion of upstream support portion 41.
Stabilizing legs 910 are hypothesized to increase the stability of prosthetic valve support 1040 at the native valve. For example, legs 910 are hypothesized to at least partly inhibit (1) lateral rotation (i.e., rotation around an atrial-ventricular axis) of the prosthetic valve support, and/or (2) movement of the parts of upstream support portion 41 that are disposed against the proximal (e.g., atrial) side of the native valve, from moving away from, or through, the native valve. Following deployment (e.g., implantation) of prosthetic valve 42, legs 910 are further hypothesized to reduce rolling movement (e.g., movement around a lateral axis, e.g., an axis between two elements 900, such as an axis that is generally orthogonal to an axis between the stabilizing legs) of the prosthetic valve and/or implant 30, including inversion (e.g., ‘flipping’) of the implant.
For some applications of the invention, support 1040 is configured such that legs 910 and/or elements 900 are biased to reside in a particular (e.g., a pre-selected) configuration. For example, legs 910 and/or elements 900 and/or a coupling point (e.g., coupling point 911) may comprise a shape-memory material (e.g., nitinol, stainless steel, nickel cobalt, cobalt chrome, and/or titanium) or a spring mechanism. For some applications of the invention, the pre-selected configuration of legs 910 comprises the stabilizing configuration of legs 910.
For some applications of the invention, legs 910 and/or elements 900 are rotatable around coupling point 911. For example, legs 910 and/or elements 900 may be coupled to upstream support portion 41 via a hinge point (e.g., a hinge element), which may comprise a flexible material and/or moving components. For some applications of the invention, legs 910 and/or elements 900 rotate freely around coupling point 911 as far as their shape and juxtaposition allows.
For some applications where elements 900 rotate freely, following the coupling of elements 900 to leaflets 82 of the native valve, the leaflets continue to function, at least in part.
For some applications where stabilizing legs 910 rotate freely, the stabilizing legs have (1) a floating configuration, in which the stabilizing legs rotate freely, and (2) a stabilizing configuration, in which the stabilizing legs assume the pre-selected configuration, and are movable from the floating configuration to the pre-selected configuration. For some such applications, stabilizing legs assume the floating configuration when support 1040 is implanted, and are moved to the stabilizing configuration when the prosthetic valve is deployed in the lumen of the support.
Typically, support-anchoring elements 900 are coupled to leaflets 82, i.e., one element 900 is coupled to anterior leaflet 82a, and one element 900 is coupled to posterior leaflet 82p. Typically, stabilizing legs 910 are oriented toward zones (scallops) P1 and P3 of the posterior leaflet. This configuration and orientation of elements 900 and legs 910 with respect to each other, and with respect to the native valve, is hypothesized to facilitate the stable placement and coupling (i.e., implantation) of prosthetic valve support 1040 at/to the native valve, and thereby is hypothesized to facilitate the stable implantation of implant 30 at the native valve.
Stabilizing legs 910 are thereby typically oriented toward parts of posterior leaflet 82p. This configuration and orientation of elements 900 and legs 910 with respect to each other, and with respect to the native valve, is hypothesized to facilitate the stable placement and coupling (i.e., implantation) of prosthetic valve support 1040 at/to the native valve, and thereby is hypothesized to facilitate the stable implantation of implant 30 at the native valve.
Stabilizing legs 910 are thereby typically oriented toward parts of anterior leaflet 82a. This configuration and orientation of elements 900 and legs 910 with respect to each other, and with respect to the native valve, is hypothesized to facilitate the stable placement and coupling (i.e., implantation) of prosthetic valve support 1040 at/to the native valve, and thereby is hypothesized to facilitate the stable implantation of implant 30 at the native valve.
Reference is made to
Support-anchoring element 900a comprises two clip elements, such as plate 920 and plate 922, (1) coupled at a coupling point, and (2) between which, during implantation, leaflets 82 of the native valve are clamped. Typically, plate 920 is substantially immobile, and plate 922 is (1) biased to assume a first configuration, and (2) movable between the first configuration and another configuration. Typically, the first configuration of plate 922 is a closed configuration. Typically, the other configuration of plate 922 is an open configuration, whereby a portion of plate 922 that is furthest from the coupling point is disposed (1) further from plate 920 than is the same portion in the first, closed configuration, and (2) further from plate 920 than a portion of plate 922 that is closest to the coupling point. When plate 922 is in the closed configuration thereof, element 900a is in a closed configuration thereof. When plate 922 is in the open configuration thereof, element 900a is in an open configuration thereof. That is, element 900a is movable between open and closed configurations thereof, by plate 922 moving between open and closed configurations thereof.
Support-anchoring element 900a further comprises, or is coupled to, an actuator, typically comprising a pull-wire 924, which facilitates movement of plate 922 between the closed and open configurations. Pull-wire 924 is typically coupled to plate 922, and controlled from outside the subject. For example, pull-wire 924 may be coupled to plate 922, and extend to a control unit outside the body of the subject, for use by a physician. Typically, pull-wire 924 is coupled to the portion of plate 922 that is furthest from the coupling point, such that movement of the pull-wire proximally (e.g., by pulling) moves plate 922 toward the open configuration. For some applications of the invention, pull-wire 924 is slidably coupled to another part of element 900a, such as plate 920, and/or to another part of support 1040a, and/or to a part of delivery apparatus, such as core 926, as shown in
For some applications of the invention, both support-coupling elements 900a are controlled simultaneously by a user (e.g., support-coupling elements 900a are configured to operate simultaneously). For some applications, each element 900a is controllable independently. For some applications, element 900a further comprises one or more grips, such as teeth 928, which facilitate the clamping of leaflets 82 when element 900a is closed.
For some applications, following deployment of support 1040a, pull-wire 924, or a portion thereof, is decoupled from the support, or a portion thereof, (e.g., from element 900a). For example, the pull-wire may be coupled to element 900a using a lock described herein (e.g., with reference to
Reference is made to
Support-anchoring element 900b comprises two clip elements, such as plate 940 and plate 942, (1) coupled at a coupling point, and (2) between which, during implantation, leaflets 82 of the native valve are clamped. Typically, plate 940 is substantially immobile, and plate 942 is (1) biased to assume a first configuration, and (2) movable between the first configuration and another configuration. Typically, the first configuration of plate 942 is an open configuration, whereby a portion of plate 942 that is furthest from the coupling point is disposed further from plate 940 than a portion of plate 942 that is closest to the coupling point. Typically, the other configuration of plate 942 is a closed configuration, whereby a portion of plate 942 that is furthest from the coupling point is disposed closer to plate 940 than is the same portion in the first, open configuration. When plate 942 is in the closed configuration thereof, element 900b is in a closed configuration thereof. When plate 942 is in the open configuration thereof, element 900b is in an open configuration thereof. That is, element 900b is movable between open and closed configurations thereof, by plate 942 moving between open and closed configurations thereof.
Support-anchoring element 900b further comprises an actuator, typically comprising a restraint, such as cuff 944, which facilitates movement of plate 922 between the closed and open configurations. Cuff 944 is typically coupled to plate 940 and/or plate 942, and controlled from outside the subject (e.g., controlled from outside the body of the subject by a physician, such as via a control unit). Typically, cuff 944 is coupled to plate 940 via a spring 950, and is slidable over (e.g., onto and off of) at least a portion of plate 942. Support-anchoring element 900b is configured such that (1) spring 950 applies a force (i.e., a first force) to cuff 944, that slides cuff 944 over plate 942, and (2) sliding of cuff 944 over plate 942 moves the portion of plate 942 that is furthest from the coupling point closer to plate 940 (i.e., moves plate 942, and thereby element 900b, into the closed configuration). A user typically opens element 900b (e.g., so as to clamp leaflets of the native valve, e.g., as described hereinbelow with reference to
For some applications of the invention, both support-coupling elements 900b are controlled simultaneously by a user (e.g., support-coupling elements 900b are configured to operate simultaneously). For some applications, each element 900b is controllable independently. For some applications, element 900b further comprises one or more grips, such as teeth 948, which facilitate the clamping of leaflets 82 when element 900b is closed. For some applications, control rod 952 is moved distally using a pusher (not shown), disposed within delivery apparatus (e.g., overtube 1044), and typically not fixedly coupled to the control rod.
As described hereinabove, for some applications, control rod 952 is moved distally using a pusher, disposed within delivery apparatus (e.g., overtube 1044), and typically not fixedly coupled to the control rod. For such applications, the pusher remains within the delivery apparatus, and is removed with the delivery apparatus, following full deployment of prosthetic valve support 1040b.
Reference is again made to
For some applications of the invention, during the deployment (e.g., implantation) of prosthetic valve support 1040 (e.g., support 1040a, and/or support 1040b), the user (e.g., physician) may determine the quality (e.g., strength) of coupling of support-anchoring elements 900 (e.g., elements 900a, and/or 900b) by applying a force (e.g., pushing, pulling, twisting) to the device, and/or using imaging techniques to visualize the device in situ.
Typically, support-anchoring elements 900 (e.g., elements 900a and/or 900b) are operable (i.e., openable, and/or closable) repeatedly. Should coupling of elements 900 to leaflets 82 be determined to be suboptimal, elements 900 may be opened (e.g., decoupled from the leaflets) and reclosed (e.g., re-coupled to the leaflets), until optimal coupling has been achieved.
Should it be necessary and/or desirable during deployment, until prosthetic valve support 1040 (e.g., support 1040a, and/or support 1040b) is fully deployed (e.g., from overtube 1044), the deployed, expanded portions of the support (i.e., the portions of the support, including elements 900) that are exposed from the overtube may be drawn back into the overtube (e.g., for repositioning, or for withdrawal from the body of the subject).
It is to be noted that, although the support-anchoring elements described with reference to
Reference is made to
As described hereinabove, prosthetic valve 42 has (1) a compressed configuration, in which it is typically delivered, within a delivery tube (e.g., tube 60), to the implantation site (e.g., native valve 23), and (2) an expanded configuration, toward which the prosthetic valve moves during deployment. Coupling tabs 1100 are configured such that (1) in the compressed configuration of the prosthetic valve, the tabs assume a restrained configuration (
Typically, coupling tabs 1100 comprise a shape-memory material (e.g., nitinol, stainless steel, nickel cobalt, cobalt chrome, and/or titanium), and the unconstrained configuration is pre-selected by shape-setting the material.
It is hypothesized that, when prosthetic valve 42 is implanted in the native valve, coupling tabs 1100 (e.g., tabs 1100a and tabs 1100b), advantageously, disturb blood flow less than some coupling tabs that do not move into a configuration in which at least part of the tabs protrude radially from the prosthetic valve. For example, for some applications, coupling tabs 1100 protrude less far proximally into the atrium from the proximal part of primary structural element 130, and/or are disposed further peripherally to a flow of blood through the prosthetic valve. It is hypothesized that this reduced blood flow disturbance of tabs 1100 reduces the likelihood of inducing hemodynamic disorders such as thrombus formation. It is further hypothesized that this reduced proximal protrusion into the atrium, increases the available space in the atrium, thereby facilitating the delivery, removal and/or other movement of medical devices and/or delivery apparatus in the vicinity of the prosthetic valve.
For some applications of the invention, coupling tabs 1100 (e.g., coupling tabs 1100a, and/or coupling tabs 1100b) further facilitate coupling of the prosthetic valve to the prosthetic valve support (e.g., prosthetic valve support 40). As described herein, the size of the lumen of support 40 typically determines the size to which prosthetic valve 42 expands, when implanted in this lumen. Thus, when implanted and expanded in the lumen of prosthetic valve support 40, the primary structural element of prosthetic valve 42 typically has a longest transverse cross-sectional length that generally corresponds to a longest transverse cross-sectional length of the lumen of support 40. A transverse cross section of prosthetic valve 42 at the position of radially-protruding coupling tabs 1100, typically has a longest length that is greater than the longest transverse cross-sectional length of the lumen of support 40. That is, in the region of coupling tabs 1100, prosthetic valve 42 is typically wider than in other (e.g., more distal) regions of the prosthetic valve. This extra width provides axial resistance against undesired distal (e.g., ventricular) movement of prosthetic valve 42 with respect to support 40, in addition to the resistance typically provided by radially expansive forces of prosthetic valve against the support.
For some applications of the invention, coupling tabs 1100 (e.g., coupling tabs 1100a, and/or coupling tabs 1100b) increase the rigidity of prosthetic valve 42 (e.g., the rigidity of primary structural element 130 of the prosthetic valve). For example, for some applications, when primary structural element 130 is generally cylindrical, coupling tabs 1100 inhibit deformation of element 130.
Reference is made to
Tissue-engaging elements 2002 are configured to couple to leaflets 82 of the native valve, subsequent to the deployment (e.g., implantation) of prosthetic valve 2000. Typically, elements 2002 are configured to couple to the leaflets by piercing the leaflets, at least in part.
For some applications, prosthetic valve 2000 comprises two elements 2002, that are disposed at sites on the circumference of primary structural element 130 that are generally opposite each other. For some applications of the invention, prosthetic valve 2000 comprises more than two (e.g., four or more, such as six or more) elements 2002, that are disposed circumferentially around primary structural element 130.
For some applications, tissue-engaging elements 2002 protrude generally orthogonally to the outer surface of primary structural element 130 (i.e., generally straight outward laterally from element 130). For some applications, elements 2002 protrude at an acute angle from the outer surface of primary structural element 130. For example, and as illustrated in
Immediately following the implantation of support 2030 and prosthetic valve 2000, leaflets 82 of the native valve typically continue to function, at least in part. For example, support-anchoring elements 2032 may be configured to rotate around a coupling point with upstream support portion 41 of the prosthetic valve, so as to allow the leaflets to continue to function, at least in part (e.g., as described herein for several support-anchoring elements). When leaflets 82 move against prosthetic valve 2000 (e.g., during systole), tissue-engaging elements 2002 couple to (e.g., by piercing) the leaflets.
For some applications of the invention, tissue-engaging elements 2032 are configured to move leaflets 82 against prosthetic valve 2000, and thereby onto tissue-engaging elements 2002. For example, elements 2032 may be configured to move toward each other, such that following implantation of prosthetic valve support 2030 and coupling of elements 2032 to leaflets 82, when prosthetic valve 2000 is deployed in the lumen of support 2030, elements 2032 push leaflets 82 against the prosthetic valve.
It is hypothesized that such coupling of leaflets 82 to elements 2002, and thereby to prosthetic valve 2000, facilitates (1) stable implantation of implant 30 in the native valve, and/or (2) sealing of leaflets 82 around the prosthetic valve, thereby inhibiting retrograde leakage of blood between the leaflets and the implant.
Reference is made to
Reference is now made to
Prosthetic valve support 1122 is typically delivered to, and deployed at, native valve 23, as described herein for other prosthetic valve supports. Support-anchoring elements 1124 are typically coupled to leaflets 82 of the native valve, as described herein for other support-anchoring elements. Subsequent to the deployment and coupling of support 1122 to the native valve, prosthetic valve 1120 is deployed in the lumen of the prosthetic valve support, as described herein for other prosthetic valves. As prosthetic valve 1120 expands, barbs 1126 engage and couple to the prosthetic valve, typically by protruding into voids defined by the prosthetic valve. For some applications of the invention, elements 1124 are configured to assume a pre-selected configuration, such as that shown in
Typically, barbs 1126 are configured to protrude into the voids defined by prosthetic valve 1120, but to not protrude further into the prosthetic valve, e.g., into the lumen defined by the prosthetic valve. Typically, prosthetic valve 1120 comprises a wire frame, and a covering 1128, which covers at least part of the inner surface of the prosthetic valve (i.e., the walls of the lumen), so as to facilitate blood flow through the prosthetic valve. Typically, barbs 1126 are dimensioned so as to protrude into the voids defined by the prosthetic valve, but to not protrude into and/or through covering 1128. That is, prosthetic valve 1120 and prosthetic valve support 1122 are configured so as to be couplable to each other using barbs 1126, without the barbs contacting (and possibly damaging) covering 1128.
For some applications of the invention, and as illustrated in
Reference is now made to
The structure, function and implantation method of prosthetic valve support 1132 and prosthetic valve 1130, are typically similar to those of prosthetic valve support 1122 and prosthetic valve 1120. However, each support-anchoring element 1134 of prosthetic valve support 1132 typically comprises no more than 4 barbs 1136 (e.g., 2 barbs 1136). Prosthetic valve 1130 comprises a wire frame, and a covering 1138, which covers at least part of the inner surface of the prosthetic valve (i.e., the walls of the lumen), so as to facilitate blood flow through the prosthetic valve. Typically, the inner surface of a portion (e.g., a distal portion 1139) of prosthetic valve 1130 is not covered with covering 1138. Typically, barbs 1136 are positioned and/or configured to engage and couple distal portion 1139. That is, prosthetic valve 1130 and prosthetic valve support 1132 are configured so as to be couplable to each other using barbs 1136, without the barbs contacting (and possibly damaging) covering 1138.
Reference is now made to
Prosthetic valve support 1142 comprises one or more support-anchoring elements 1144, which, for some applications of the invention, comprise, and/or are analogous to, (1) other support-anchoring elements described herein (e.g., support-anchoring elements 66), and/or (2) tissue-engaging elements 62. Support-anchoring elements 1144 comprise a coupling lead 1146 (e.g., a coupling wire) and a stopper 1147, which is slidably coupled to the coupling lead. Coupling lead 114 and stopper 1147 comprise the coupling functionality for coupling the support-anchoring elements of the prosthetic valve support to the prosthetic valve. One end (e.g., a distal end) of coupling lead 1146 is typically coupled to element 1144, and portion (e.g., a proximal portion) of the coupling lead is slidably coupled to prosthetic valve 1140. For some applications of the invention, prosthetic valve 1140 is shaped to define an eyelet (not shown), through which coupling lead is slidable.
For some applications of the invention, coupling leads 1146 facilitate rotational orientation of prosthetic valve 1140 with respect to support 1142 during deployment of the prosthetic valve in the lumen of the support. For example, coupling leads 1146 may act as guidewires, along which the prosthetic valve is slid during deployment thereof.
For some applications of the invention, prosthetic valve 1140 is coupled to prosthetic valve support 1142 using coupling leads 1146 and stoppers 1147 (i.e., stoppers 1147 are slid distally, sandwiching the portions of the prosthetic valve between the stoppers and elements 1144) before the prosthetic valve is fully deployed. For example, this coupling may be performed when the prosthetic valve is semi-deployed from delivery tube 60, i.e., when a proximal portion of the prosthetic valve is still compressed within the delivery tube.
Coupling of prosthetic valve 1140 to elements 1144 with coupling lead 1146 is hypothesized to inhibit lateral rotation (e.g., rotation around an atrial-ventricular axis), and/or axial movement, of the prosthetic valve, with respect to the support.
Following coupling of prosthetic valve 1140 to support-anchoring elements 1144, a proximal portion of coupling lead 1146 is typically subsequently removed from the subject.
Reference is made to
Reference is made to
Reference is now made to
For some applications of the invention, second portion 1192 is shaped to define at least part of a trough, and the surface of the second portion that is disposed further from the inner surface of the tubular member, comprises a surface of the trough.
As is described hereinbelow, coupling lead 1180 is typically coupled to a medical device 150 and facilitates (1) coupling of medical device 150 to delivery apparatus during delivery of the medical device and (2) decoupling of medical device 150 from the delivery apparatus following implantation of device 150.
Reference is now made to
Reference is made to
Stabilizing element 1062 is hypothesized to increase the stability of prosthetic valve support 1060 at the native valve. For example, stabilizing element 1062 is hypothesized to at least partly inhibit lateral rotation (e.g., rotation around an atrial-ventricular axis, e.g., ‘yaw’) of the support and/or support-anchoring elements. Following deployment (e.g., implantation) of the prosthetic valve, stabilizing element 1062 is further hypothesized to reduce rolling movement (e.g., movement around a lateral axis, e.g., an axis between two elements 900, e.g., ‘pitch’ and ‘roll’) of the prosthetic valve and/or implant 30, including inversion (e.g., ‘flipping’) of the implant.
For some applications of the invention, stabilizing element 1062 is further hypothesized to stabilize elements 900 during deployment of the elements, e.g., by facilitating coupling thereof to delivery apparatus.
For some applications of the invention, stabilizing element 1062 is configured (e.g., dimensioned) such that, when the prosthetic valve is expanded within the opening of the stabilizing element, the stabilizing element limits the expansion of the distal portion of primary structural element 130 of the prosthetic valve. That is, for some applications, the cross-sectional area defined by the primary structural element 130 of the prosthetic valve, upon expansion of the prosthetic valve, is determined by the cross-sectional area of the opening of the stabilizing element. For some applications, the cross-sectional area of the opening of the stabilizing element is substantially equal to the cross-sectional area of the lumen defined by upstream support portion 41, thereby the expansion of both the distal and proximal portions of the primary structural element are limited to the same diameter, thereby facilitating the primary structural element to assume a cylindrical shape.
For applications where stabilizing element 1062 limits the expansion of prosthetic valve 42, a radially-expansive force is thereby applied by prosthetic valve 42 to stabilizing element 1062. The radially-expansive force typically couples the prosthetic valve to the stabilizing element. That is, for some applications, prosthetic valve 42 is couplable to the stabilizing element. For some applications, the prosthetic valve is coupled to the stabilizing element by alternative or additional means. For example, the stabilizing element may comprise barbs and/or hooks, which facilitate coupling to the prosthetic valve.
For some applications of the invention, at least part (e.g., an inner surface) of stabilizing element 1062 comprises a friction coating, that is configured to increase friction, and thereby coupling, between the stabilizing element and the prosthetic valve.
For some applications of the invention, at least part of stabilizing element 1062 is shaped to define ridges, which are configured (e.g., dimensioned) to protrude between struts of the lattice structure of the prosthetic valve (i.e., into voids defined by the lattice structure). The protruding parts facilitate coupling of the stabilizing element to the prosthetic valve, e.g., by inhibiting axial movement of the prosthetic valve through the opening defined by the stabilizing element.
For some applications of the invention, a soft (e.g., crushable) material is disposed on the inner surface of stabilizing element 1062 (e.g., the stabilizing element comprises the soft material). When prosthetic valve 42 expands, and applies radially-expansive force to the stabilizing element, (1) the struts of the lattice structure of the prosthetic valve compress (e.g., crush) the parts of the soft material against which the struts apply the force, and (2) the parts of the soft material that are disposed between the struts (i.e., that are disposed at voids defined by the lattice structure), form ridges that protrude between the struts (i.e., protrude into the voids). The protruding parts of the soft material facilitate coupling of the stabilizing element to the prosthetic valve, e.g., by inhibiting axial movement of the prosthetic valve through the opening defined by the band, such as by increasing friction.
For some applications of the invention, prosthetic valve 42 (e.g., the primary structural element of prosthetic valve 42) is shaped to define a circumferential groove that is configured (e.g., dimensioned) to receive stabilizing element 1062. That is, for some applications of the invention, stabilizing element 1062 is configured (e.g., dimensioned) to be placeable in a circumferential groove defined by prosthetic valve 42. When prosthetic valve 42 is deployed, and expands in the opening defined by stabilizing element 1062, stabilizing element 1062 is disposed in the groove, thereby further facilitating coupling of the stabilizing element to the prosthetic valve, e.g., by inhibiting axial movement of the prosthetic valve through the opening defined by the stabilizing element.
It is to be noted that, although stabilizing element 1062 is described with reference to
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Reference is now made to
It is to be noted that implants 30 described herein may be implanted using the method described hereinabove with reference to
Reference is made to
Wings 100 typically increase a ratio of surface area of the support to annular tissue. Wings 100 typically protrude between 5 mm and 40 mm (e.g., between 10 mm and 30 mm) from outer edge 69 of the support. Prosthetic valve support 4040b comprises two wings, as shown in
In some applications of the invention, prosthetic valve support 40 (e.g., prosthetic valve supports 4040a, 4040b, 4040c) comprises barbs 102, which protrude into the lumen defined by support 40. During the expansion of prosthetic valve 42 within the lumen of support 40, as described hereinabove, barbs 102 protrude into and engage prosthetic valve 42. Barbs 102 thereby facilitate coupling between support 40 and prosthetic valve 42 in addition to the radial forces between support 40 and prosthetic valve 42. In some applications of the invention, some or all of barbs 102 may be curved, as shown in the enlarged images of
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As illustrated in
In
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Reference is now made to
The lattice structure of prosthetic valve 42b further defines a plurality of voids 126. Shapes 128 are typically arranged in columns 118, each shape connected to the next in each column. In some regions of the prosthetic valve, there is a separation 124 between a distal shape and an adjacent shape (e.g., between the final shape in a column and a respective penultimate shape in the column that is longitudinally proximal to the distal quadrilateral). This separation 124 allows a portion of the shape to move or be moved out of the plane of the lattice, thereby protruding from primary structural element 130 of prosthetic valve 42b when the distal portion of prosthetic valve 42b is expanded. The protruding portion of shapes 128 thereby form integral anchors 300, which are typically configured to anchor prosthetic valve 42b to native valve 23. Valve-anchoring elements 64 are thereby formed from integral parts of the lattice structure that forms prosthetic valve 42b, and are disposed between a proximal end 251 and a distal end 252 of primary structural element 130 of prosthetic valve 42b. That is, prosthetic valve 42b has a functional length (i.e., a length selected so as to facilitate prosthetic valve function), and integral anchors 300 typically do not increase the length of prosthetic valve 42b to be greater than the functional length.
Reference is made to
Reference is now made to
As described hereinabove, prosthetic valve 42 is deployed by distal movement out of delivery tube 60.
Reference is now made to
Typically, the anchoring of the prosthetic valve and/or the capturing of leaflets of the native valve are performed while prosthetic valve 42b is partially deployed from delivery tube 60, as shown in
Reference is made to
Integral anchors 310 are similar in form and function to integral anchors 300, and are typically formed by separations 124 in the lattice structure of structural element 130, as described with reference to
As described hereinabove, prosthetic valve 42 is deployed by distal movement out of delivery tube 60.
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Reference is now made to
Reference is now made to
Reference is now made to
Reference is made to
As described hereinabove, valve-anchoring elements 64 typically have a constrained configuration for delivery, and an unconstrained configuration whereby they protrude radially from primary structural element 130 of prosthetic valve 42. For some applications, in the constrained configuration of elements 64, during delivery, elements 64 are typically but not necessarily disposed distal to the generally-cylindrical structure of valve 42 at an angle that is between 165 and 180 degrees with respect to the generally-cylindrical structure. In order to achieve these constrained and unconstrained configurations for prosthetic valve 42d, comprising twisted anchors 320, a distal portion of prosthetic valve 42d is typically torsionally bent to define twisted anchors 320. For some applications of the present invention, in order to achieve these configurations for prosthetic valve 42d comprising twisted anchors 320, a distal portion of prosthetic valve 42d is typically bent to define twisted anchors 320.
The material comprising the lattice structure of prosthetic valve 42 has a depth 242 and each strut of the lattice structure has a width 244 (shown in
It is hypothesized that this configuration allows a greater bend angle to be imparted, such that twisted anchors 320 can (1) be disposed distal to (e.g., planar with) primary structural element 130 of prosthetic valve 42d when the twisted anchors are in their constrained configuration (i.e., when compressed in delivery tube 60 for delivery) as shown in
It is to be noted, that during delivery of prosthetic valve 42d toward mitral valve 24, valve 42d is crimped within delivery tube 60 such that anchors 320 assume a constrained and compressed state within tube 60.
Reference is now made to
Reference is now made to
Reference is now made to
In some applications of the invention, twisted anchors 320 comprise more than one bending region 240. For such applications, the material comprising prosthetic valve 42d is bent and twisted in each respective bending region, as described with reference to
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Reference is now made to
It is to be noted that the scope of the present invention includes a first loop-shaped valve-anchoring element 200a being larger than second loop-shaped valve-anchoring element 200b, such that second loop-shaped element 200b is disposable within and/or passable through a space defined by the larger loop shape of first loop-shaped valve-anchoring element 200a.
As described hereinabove, valve-anchoring elements 64 have a constrained and compressed configuration for delivery of prosthetic valve 42e (as shown in
Loop-shaped valve-anchoring elements 200 are shown in
In some applications of the invention, in the unconstrained configuration, a rounded end of second valve-anchoring element 200b of each pair 132 is disposed more proximally than a rounded end of first valve-anchoring element 200a. In such applications, movement of valve-anchoring elements 200 from the constrained configuration to the unconstrained configuration comprises movement of the rounded ends of the second valve-anchoring elements 200b of each pair 132 proximally past the respective rounded ends of the first valve anchoring elements 200a of each pair 132.
In either application, movement of valve-anchoring elements 200 from the constrained configuration to the unconstrained configuration allows elements 200a and 200b to capture material (e.g., leaflets 82 of the native valve) between them, i.e., in a manner in which elements 200a and 200b function together as a clip 65a.
Typically, following the deployment of elements 200b at the respective ventricular surfaces of leaflets 82, elements 200a are positioned within tube 60 in a manner in which during their expansion from within tube 60, elements 200a move toward respective atrial surfaces of leaflets 82. For some applications, following the deploying of elements 200b, valve 42e is pulled proximally (e.g., by pulling proximally on both valve 42e and tube 60) in order to adjust the positioning of valve 42e with respect to leaflets 82 and so as to ensure that, once deployed from within tube 60, elements 200a will press against respective atrial surfaces of leaflets 82.
Reference is made to
Typically, during advancement of valve 42f, valve 42f is crimped within delivery tube 60.
It is to be noted that the technique described with reference to
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Reference is made to
For some applications of the invention, it is hypothesized that the anchoring of support 40 to the native valve by support-anchoring elements 66 may be sufficient to anchor implant 30 to the native valve, thereby minimizing or even eliminating the need for supplemental anchoring of implant 30 by valve-securing elements 64. Therefore, for such applications of the invention, prosthetic valve 42 does not comprise valve-anchoring elements 64. In some such applications of the invention, leaflets 82 of the native valve are allowed to function, at least in part, following implantation of the prosthetic valve.
Reference is now made to
During delivery of support 4040d to the native valve, support 4040d is crimped within overtube 44, as described hereinabove with reference to support 40 of
In some applications of the invention, fixed anchors 330 comprise coupling-portion 70 configured to engage tissue of the native valve. Coupling-portion 70 is illustrated as an extension of fixed anchors 330 such that fixed anchors 330 assume a generally L-shape. In other applications of the invention, coupling-portion 70 may be disposed differently (e.g., at an angle other than the angle as shown), or may comprise clips 65a or 65b, or another means for engaging native valve 23. In some applications of the invention, fixed anchors 330 do not comprise a coupling-portion.
Reference is now made to
Reference is now made to
Anchoring prosthetic valve support 4040d is anchored to native valve 23 in a different orientation to that described with reference to
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Hinged anchors 340 are typically coupled to prosthetic valve support 40 via a hinge point 72. Hinge point 72 may comprise a flexible material and/or moving components. For some applications of the invention, hinged anchors 340 rotate freely around hinge point 72 as far as their shape and juxtaposition allows. For some applications of the invention, hinged anchors 340 are biased to reside in a particular configuration. For example, hinged anchors 340 and/or hinge point 72 and/or prosthetic valve support 40 may comprise a shape-memory material (e.g., nitinol) or a spring mechanism, configured to push hinged anchors 340 radially outward.
The use of hinge points 72 for coupling support-anchoring elements 66 to prosthetic valve support 40 is hypothesized to provide one or more of the following advantages: (1) Improving compressibility of prosthetic valve support 40, for transcatheter delivery. (2) Improving movement of native leaflets 82 following deployment of prosthetic valve support 40 to the native valve. (3) Increasing adjustability of the dimensions and configuration of support-anchoring elements 66.
Reference is now made to
Reference is made to
For some applications of the invention, prosthetic valve support 4040f is configured such that clamping hinged anchors 350 are biased to extend radially inward (i.e., toward each other). This configuration is illustrated by the upper panel of
Reference is again made to
Reference is now made to
Reference is made to
In the application of the invention described with respect to
Prosthetic valve 42 and pushing member 140a are disposed within the lumen of delivery tube 154. Delivery tube 154 restricts expansion of prosthetic valve 42, thereby holding the proximal portion of prosthetic valve 42 around core 144 of pushing member 140a, in the configuration described herein. Coupling tabs 4146 restrict movement of prosthetic valve 42 with respect to pushing member 140a. Delivery tube 154 therefore facilitates coupling of prosthetic valve 42 to pushing member 140a via coupling tabs 4146. In applications of the invention where pushing member 140a is shaped to define plate 4148, the plate typically further facilitates this coupling by restricting proximal movement of prosthetic valve 42 with respect to the pushing member (e.g., by functioning as a cap).
A control tube 4152 is coupled at a distal end thereof to pushing member 140a (e.g., control tube 4152 is coupled to support 4142a). Control tube 4152 is shaped so as to define a lumen through which a guidewire tube 4153 passes, and control tube 4152 is slidable with respect to and along guidewire tube 4153. Guidewire tube 4153 houses guidewire 45 described hereinabove. Control tube 4152 is slidably disposed within a lumen of an overtube 4155.
Reference is again made to
Should it be necessary and/or desirable during the procedure, until medical device 150 (e.g., prosthetic valve 42) is released from pushing member 140a (i.e., while the proximal portion of medical device 150 is crimped within delivery tube 154), the remaining portions of medical device 150 may be drawn back into delivery tube 154 (e.g., for repositioning or withdrawal of the medical device).
Reference is now made to
In the application of the invention described with reference to
It is hypothesized that utilization of pushing member 140a, comprising coupling tabs 4146 that are disposable in voids 4126 defined by an expandable medical device 150, (1) reduces the overall length of the apparatus (i.e., the combined lengths of medical device 150 and delivery tube 154) being advanced into the subject, and/or (2) reduces the requirement for additional components of medical device 150 which function as coupling structures of medical device 150. That is, medical device 150 has an integral coupling system by which voids 4126 are coupled to tabs 4146. The applications of the invention described with reference to
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Reference is now made to
Prior to delivery, prosthetic valve 42 is compressed (e.g., crimped) such that all coupling tabs 220 are disposed in respective troughs 222. Prosthetic valve 42 and pushing member 140b are disposed within the lumen of delivery tube 154. Delivery tube 154 restricts expansion of prosthetic valve 42, thereby holding coupling tabs 220 in troughs 222, in the configuration described herein. Coupling tabs 220 restrict movement of prosthetic valve 42 with respect to pushing member 140b. Delivery tube 154 therefore facilitates coupling of prosthetic valve 42 to pushing member 140b via coupling tabs 220. As described with reference to
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Reference is now made to
A coupling lead 4180 (e.g., a coupling wire) is disposable in trough 176, and is reversibly couplable thereto (and thereby to lock 170), as described hereinbelow. As is described hereinbelow, coupling lead 4180 is coupled to a medical device 150 and facilitates (1) coupling of medical device 150 to a delivery mechanism during delivery of the medical device and (2) decoupling of medical device 150 from the delivery mechanism following implantation of device 150. Typically, a region at an end of coupling lead 4180 is shaped to define a stopper 182, which is thicker than other regions of the coupling lead, and is configured to be disposable in widened part 178 of trough 176, typically when tubular member 4172 surrounds plug 174. Alternatively, stopper 182 may comprise a distinct component that is coupled to coupling lead 4180. Trough 176, coupling lead 4180, widened part 178, and stopper 182 are dimensioned such that when the coupling lead and the stopper are disposed in trough 176, plug 174 remains disposable in, and slidable through, tubular member 4172.
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Reference is now made to
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In the application of the invention illustrated in
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Reference is now made to
For some applications of the present invention, the other end of coupling lead 4180 is attached to a portion of holding member 4046. In such applications, withdrawal of coupling lead 4180 typically comprises withdrawing holding member 4046 proximally.
For some applications of the invention, the other end of coupling lead 4180 is attached to a portion (e.g., an outer surface of) of plug 174. For such applications, withdrawal of coupling lead 4180 may comprise withdrawing the plug into tubular member 4172 (i.e., holding member 4046).
In either application, following the decoupling of holding members 4046 and wires 4180 from device 150, medical device 150 is typically left at the site of implantation.
Reference is made to
Reference is now made to
The applications of the invention described with reference to
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Reference is now made to
Reference is now made to
The applications of the invention described with reference to
Reference is made to
Prosthetic valve 42 may be coupled to one or more valve-anchoring elements 64, comprising loop-shaped valve-anchoring elements 200, stick-shaped valve-anchoring elements 202, or a combination thereof, in order to facilitate deployment of prosthetic valve 42 and coupling of the prosthetic valve to native heart valve 23. For example, stick-shaped valve-anchoring elements 202 may be used in areas of heart valve 23 in which chordae tendineae 80 are disposed more densely, whereas loop-shaped valve-anchoring elements 200 may be used to capture relatively exposed regions of leaflets 82. Loop-shaped valve-anchoring elements 200 and stick-shaped valve-anchoring elements 202 are illustrated here as fixed anchors. In some applications of the invention, elements 200 and 202 may be alternatively or additionally used as hinged anchors (e.g., hinged anchors 340) and/or clamping hinged anchors (e.g., clamping hinged anchors 350), as described hereinabove.
Reference is now made to
For some applications, diameter d of the prosthetic valve is less than 25 mm, e.g., less than 20 mm, and/or more than 15 mm, e.g., 15-25 mm. For some applications, placing a prosthetic valve inside the native valve, with the dimensions of the native valve annulus and the prosthetic valve as described, facilitates sealing of the prosthetic valve with respect to the native valve, by the native valve leaflets closing around the outer surface of the prosthetic valve. In such applications, prosthetic valve 42 is implanted directly within native valve 23 (i.e., without support 40).
For some applications, a prosthetic valve support 40, that is shaped to define a lumen, is placed against the annulus of native valve 23 (e.g., as described with reference to
Typically, placing a prosthetic valve inside the native valve with the dimensions of the native valve annulus, the prosthetic valve 42, and/or valve support 40 as described in the above paragraphs, facilitates sealing of the prosthetic valve with respect to the native valve. For some applications, the sealing is facilitated by the native leaflets being pushed against, and closing against, the outer surface of the frame of the valve during systole, in a similar manner to the manner in which native valve leaflets coapt during systole, in a healthy mitral valve.
Typically, as the diameter d of the prosthetic valve is increased, the proportion of the native leaflets that is pushed against the outer surface of the valve during systole is increased, thereby enhancing the sealing of the native leaflets with respect to the frame of the prosthetic valve. However, beyond a given diameter, as the diameter d of the prosthetic valve is increased, the native valve leaflets are pushed apart at the commissures, thereby causing retrograde leakage of blood through the commissures. Therefore, in accordance with some applications of the present invention, prosthetic valve 42, and/or valve support 40 are chosen such that the cross-sectional area of the prosthetic valve (when expanded inside the valve support) is less than 90% (e.g., less than 80%, or less than 60%) of area A1 of native valve 23. Thus, the valve support facilitates additional sealing of the prosthetic valve with respect to the native valve, by the native valve leaflets closing around the outer surface of the prosthetic valve, while not causing retrograde leakage of blood through the commissures.
For some applications, in order to facilitate the sealing of the native valve around the outer surface of the prosthetic valve, a material is placed on the outer surface of the prosthetic valve in order to provide a sealing interface between the prosthetic valve and the native valve. For example, a smooth material that prevents tissue growth (e.g., polytetrafluoroethylene (PTFE), and/or pericardium) may be placed on the outer surface of the prosthetic valve. Alternatively or additionally, a material that facilitates tissue growth (such as polyethylene terephthalate; PET) may be placed on the outer surface of the prosthetic valve, in order to (a) act as a sealing interface between the native valve and the prosthetic valve, and (b) facilitate tissue growth around the prosthetic valve to facilitate anchoring and/or sealing of the prosthetic valve.
Reference is made to
In the fully uncompressed configuration thereof, upstream support portion 2041 typically has an outer perimeter 2069 of length between 125 and 190 mm (e.g., between 140 and 170 mm, such as between 140 and 150 mm), and an inner perimeter 2068 (that defines opening 2045) of length between 62 and 105 mm (e.g., between 65 and 80 mm, such as between 75 and 80 mm). When upstream support portion 2041 is annular, the upstream support portion, in the fully uncompressed configuration thereof, typically has an outer diameter d10 (e.g., a greatest outer diameter) of between 40 and 80 mm (e.g., between 40 and 70 mm, such as between 40 and 60 mm), and an inner diameter d11 (e.g., a greatest inner diameter) of between 20 and 35 mm (e.g., between 23 and 32 mm, such as between 25 and 30 mm). That is, opening 2045 typically has a diameter of between 20 and 35 mm (e.g., between 23 and 32 mm, such as between 25 and 30 mm). Typically, outer perimeter 2069 has a length that is at least 10% (e.g., at least 50%, such as at least 80%) greater than inner perimeter 2068.
In the fully uncompressed configuration thereof, upstream support portion 2041 is typically (but not necessarily) generally flat (e.g., laminar, and/or planar). For some applications, in the fully uncompressed configuration, portion 2041 assumes a frustoconical shape, typically arranged from the generally flat composition of the portion. Portion 2041 has a thickness of less than 5 mm, such as less than 2 mm. Opening 2045 has a depth (e.g., a height) d12 from an upstream side 2047 of the upstream support portion to a downstream side 2049 of the upstream support portion. Depth d12 of opening 2045 is less than 5 mm, such as less than 2 mm. Typically, therefore, inner diameter d11 is more than 4 times (e.g., more than 6 times, such as more than 10 times) greater than depth d12. That is, opening 2045 is more than 4 times (e.g., more than 6 times, such as more than 10 times) wider than it is deep. Typically, in the fully uncompressed configuration, upstream support portion 2041 has a total height of less than 10 mm (e.g., less than 5 mm, such as less than 2 mm).
Typically, inner perimeter 2068 comprises, or is defined by, a free inner edge of upstream support portion 2041. That is, opening 2045 resembles a hole cut out of a lamina (e.g., out of a disc). For some applications, inner perimeter 2068 comprises, or is defined by, a curved and/or folded inner edge of upstream support portion 2041. If the inner perimeter of upstream support portion 2041 comprises, or is defined by, a curved or folded edge, then a radius of curvature of the curved or folded edge is typically less than 2.5 mm, such as less than 1 mm. That is, the curve or fold of the edge is generally sharp, such that when viewed from within opening 2045, the curved or folded edge looks generally like a free edge.
It is to be noted that, for simplicity, upstream support portion 2041 is generally described herein in terms of symmetrical geometric shapes (e.g., ellipse and frustum), but that the upstream support portion may assume a symmetrical or an unsymmetrical shape.
Prosthetic valve 2042 comprises a generally tubular (e.g., cylindrical) primary structural element 2130, shaped to define a lumen 2043 therethrough, and at least one check valve element (not shown), configured to regulate blood flow through the prosthetic valve. Typically, the check valve element comprises one or more prosthetic valve leaflets, disposed in lumen 2043, and coupled (e.g., sutured) to the primary structural element. For some applications of the invention, the check valve element comprises a ball, disc, or other check valve component. For some applications of the invention, prosthetic valve 2042 comprises a commercially-available stent-based prosthetic valve.
Prosthetic valve 2042 is configured to be placeable in opening 2045 of support 2040, and couplable to the support by being expandable within this opening, e.g., as described in more detail hereinbelow. Typically, support 2040 comprises tissue-engaging elements (e.g., support-anchoring elements), such as those described herein (not shown in
In the fully uncompressed configuration thereof, prosthetic valve 2042 typically has a perimeter 2051 of length between 62 and 110 mm (e.g., between 70 and 90 mm, such as between 80 and 90 mm), and a height d14, (i.e., a length from an upstream end to a downstream end) of between 15 and 40 mm (e.g., between 20 and 35 mm, such as between 25 and 25 mm). When structural element 2130 is cylindrical, prosthetic valve 2042, in the fully uncompressed configuration thereof, typically has a diameter d13 of between 20 and 35 mm (e.g., between 25 and 35 mm, such as between 25 and 30 mm). Typically, support 2040 and prosthetic valve 2042 are configured and/or selected (e.g., paired), such that perimeter 2051 is slightly (e.g., between 1 and 15 mm, such as between 1 and 7 mm) greater than perimeter 2068, and/or that diameter d13 is slightly (e.g., between 1 and 5 mm, such as between 1 and 3 mm) greater than diameter d11.
In the respective fully uncompressed configurations thereof, height d14 of prosthetic valve 2042 is typically at least 1.5 times greater (e.g., at least 3 times greater, such as at least 5 times greater) than the total height of upstream support portion 2041.
Typically, support 2040 comprises a lattice structure which defines a plurality of struts 2120, typically in a repeating arrangement, and a plurality of voids between the struts. Typically, upstream support portion 2041 comprises the lattice structure of support 2040. Typically, prosthetic valve 2042 comprises a lattice structure which defines a plurality of struts 2124, and a plurality of voids between the struts. Support 2040 and prosthetic valve 2042 typically have shape-memory (e.g., resilient, pseudoelastic and/or superelastic) properties. Typically, struts 2120 and/or struts 2124 comprise a shape-memory (e.g., resilient, pseudoelastic and/or superelastic) material, such that support 2040 and/or prosthetic valve 2042 are compressible when a compressive force is applied (e.g., prior to implantation), and re-expandable when the compressive force is removed (e.g., during implantation), as described hereinbelow. Non-limiting examples of materials that the support (e.g., struts 2120) and/or prosthetic valve (e.g., struts 2124) may comprise include nickel-titanium (Nitinol), stainless steel, nickel cobalt, cobalt chrome, titanium, tantalum, and palladium.
Typically, support 2040 and/or prosthetic valve 2042 are at least in part covered with a covering 2440 (for clarity, covering 2440 is only shown on support 2040). Non-limiting examples of materials that covering 2440 may comprise include polyethylene terephthalate (e.g., polyester), polytetrafluoroethylene (e.g., Teflon, ePTFE), and pericardial tissue. For some applications, covering 2440 comprises a fabric. Typically, a thickness of the covering is less than 0.5 mm, such as less than 0.2 mm, e.g., less than 0.1 mm, or less than 0.05 mm. In
For some applications of the invention, covering 2440 is configured to facilitate blood flow through the prosthetic valve, e.g., to channel blood through lumen 2043 defined by prosthetic valve 2042, and/or to prevent leakage (1) between the prosthetic valve and support 2040, and/or (2) between implant 2030 and the native valve. For some applications of the invention, the covering is configured to mask sharp and/or hard surfaces (e.g., metal surfaces, such as surfaces of struts 2120 and/or 2124), and thereby to protect native tissues from being damaged by such surfaces. For some applications of the invention, the covering is configured to facilitate (e.g., to enhance) coupling between support 2040 and prosthetic valve 2042 (e.g., as described hereinbelow), such as by increasing friction. For some applications of the invention, the covering is configured to facilitate (e.g., to encourage) growth of tissue (e.g., fibrosis) over one or more components of implant 2030.
In the compressed configuration thereof, upstream support portion 2041 typically has (e.g., perimeters 2068b and 2069b have) a perimeter of length between 9 and 30 mm (e.g., between 15 and 25 mm, such as between 18 and 22 mm), and a height d15 of between 11 and 30 mm (e.g., between 15 and 30 mm, such as between 15 and 25 mm). When upstream support portion 2041, in the compressed configuration thereof, is cylindrical, portion 2041 typically has a diameter of between 3 and 9 mm (e.g., between 5 and 8 mm, such as between 6 and 7 mm).
In the compressed configuration thereof, prosthetic valve 2042 is typically generally cylindrical. Compression of the prosthetic valve typically comprises inwardly-radial compression, such that the component is narrower and taller in the compressed configuration than in the fully uncompressed configuration thereof. In the compressed configuration thereof, prosthetic valve 2042 typically has a perimeter 2051b (a compressed perimeter 2051) of between 9 and 30 mm (e.g., between 10 and 20 mm, such as between 15 and 20 mm), and a height d16 of between 16 and 41 mm (e.g., between 20 and 35 mm, such as between 20 and 30 mm). When prosthetic valve 2042, in the compressed configuration thereof, is cylindrical, prosthetic valve 2042 typically has a diameter of between 2 and 9 mm (e.g., between 3 and 8 mm, such as between 3 and 6 mm).
Support 2040 (e.g., portion 2041) and prosthetic valve 2042 typically have shape-memory properties, and are compressed (e.g., crimped) into their respective compressed configurations prior to (e.g., immediately prior to) the implantation procedure. Typically, the support and prosthetic valve are retained (e.g., ‘constrained’) in this configuration by a constraining member, such as an overtube, a delivery tube, and/or other delivery apparatus. Support 2040 and prosthetic valve 2042 are typically subsequently expanded (e.g., ‘deployed’) close to the site of implantation by releasing the constraining (e.g., compressive) force (e.g., by removing the constraining member). That is, the compressed configurations of prosthetic valve support 2040 (e.g., of upstream support portion 2041) and prosthetic valve 2042, described with reference to
So as to provide the radially-expansive force, and as described hereinabove, prosthetic valve 2042 and support 2040 (e.g., portion 2041) are typically configured and/or selected (e.g., paired) such that perimeter 2051 of prosthetic valve 2042, in the fully uncompressed configuration thereof, is slightly greater than inner perimeter 2068 of portion 2041. When prosthetic valve 2042 is expanded within opening 2045, portion 2041 (e.g., inner perimeter 2068) thereby restricts the full expansion of prosthetic valve 2042. Therefore, in the coupled configuration shown in
As described hereinabove (e.g., with reference to
For some applications, the prosthetic valve is couplable to the upstream support portion at a continuum of positions along the axial length of the prosthetic valve. That is, a physician can couple the prosthetic valve to the support at a continuum of depths within the support. For example, in applications in which the prosthetic valve is configured to be coupled to the upstream support portion solely by the radially-expansive force, the prosthetic valve may be coupled to the upstream support portion at a continuum of positions along the length of the prosthetic valve.
As described hereinabove, the lattice structures of prosthetic valve 2042 and portion 2041 typically define a repeating arrangement of struts, e.g., a repeating arrangement of shapes. For some applications, and as shown in
Typically, the arrangement of repeating circumferential voids defined by the lattice structure of the prosthetic valve is repeated axially, thereby defining a prismatic (e.g., cylindrical) shape of the prosthetic valve. For some applications, the prosthetic valve is thereby couplable to the upstream support portion at a plurality of positions along the axial length of the prosthetic valve. That is, a physician can couple the prosthetic valve is couplable to the upstream support portion at a plurality of depths within the support. For example, in applications in which when a circumferential arrangement of voids is repeated four times along the axial length of the prosthetic valve, the prosthetic valve is typically couplable to the upstream support portion at four positions along the axial length of the prosthetic valve.
It is noted that, for some applications, the above descriptions of prosthetic valve 2042 and support 2040 are applicable to (e.g., the applications described above are combinable with) other embodiments of prosthetic valves and prosthetic valve supports described herein.
Reference is made to
Typically, clips 2900 are articulatably coupled to portion 2041. That is, typically, clips 2900 can move, at least in part, with respect to portion 2041. Typically, each clip 2900 is coupled to portion 2041 via a connector 2540, which facilitates this movement. Typically, but not necessarily, connector 2540 comprises a flexible material, such as a fabric and/or polymer. For some applications, connector 2540 comprises one or more hinge points, to facilitate the movement of the clips.
Each clip 2900 typically comprises two or more clip elements, such as a clip arm 2920 and a clip arm 2922, movable with respect to each other. Typically, the clip arms are articulatably-coupled at an articulation point 2921, and are movable with respect to each other by the relative angular disposition of the clip arms being controllable. Typically, clip 2900 is configured to be biased (e.g., pre-set, such as shape-set) to be in a closed configuration, such that arms 2920 and 2922 are relatively disposed at a generally small angle (e.g., less than 45 degrees, such as less than 20 degrees, such as less than 5 degrees) to each other. For some applications, in the closed configuration of clip 2900, arms 2920 and 2922 touch each other at a site that other than the articulation point. Each clip 2900 is configured to be couplable to a native leaflet 2082 of the native valve by enveloping the native leaflet when the clip is in the open configuration thereof, and clipping the leaflet between the clip arms when the clip subsequently moves toward the closed configuration thereof.
Typically, arm 2920 is substantially immobile, and arm 2922 is (1) biased to assume a first configuration, and (2) movable between the first configuration and another configuration. Typically, the first configuration of arm 2922 is a closed configuration. Typically, the other configuration of arm 2922 is an open configuration, whereby a portion of arm 2922 that is furthest from articulation point 2921 is disposed (1) further from arm 2920 than is the same portion in the first, closed configuration, and (2) further from arm 2920 than a portion of arm 2922 that is closest to the articulation point. That is, an angular disposition of arm 2922 to arm 2920 is greater when arm 2922 is in the open configuration thereof, than when arm 2922 is in the closed configuration thereof. When arm 2922 is in the closed configuration thereof, clip 2900 is in the closed configuration thereof. When arm 2922 is in the open configuration thereof, clip 2900 is in the open configuration thereof. That is, clip 2900 is movable between open and closed configurations thereof, by arm 2922 moving between open and closed configurations thereof.
Clip 2900 further comprises a clip-controller interface, typically comprising a pull-wire 2924, which facilitates movement of arm 2922 between the closed and open configurations, i.e., relative angular movement of arms 2920 and 2922. Pull-wire 2924 is typically coupled to arm 2922, and controlled from outside the body of the subject. For example, pull-wire 2924 may be coupled to arm 2922, and extend to a clip controller (e.g., clip controller 2930, described with reference to
For some applications of the invention, both clips 2900 are controlled simultaneously by a user (e.g., clips 2900 are configured to operate simultaneously). For some applications, each clip 2900 is controllable independently. For some applications, clip 2900 further comprises one or more grips, such as teeth 2928, which facilitate the clamping of leaflets 2082 when clip 2900 is closed. For some applications, clips 2900 may alternatively or additionally be directly coupled to the prosthetic valve, and configured to couple the prosthetic valve directly to the native valve.
Reference is made to
Prosthetic valve support 2040b is implanted using support-delivery apparatus, such as support-delivery apparatus 2960. As described hereinabove with reference to
Typically, at least part of plug 2174 (e.g., restricting portion 2190) is dimensioned so as to fit tightly in the lumen of tubular member 2172, in a manner in which an outer surface of plug 2174 (e.g., an outer surface of portion 2190) is disposed very close to an inner surface of tubular member 2172, i.e., such that little space exists between the at least part of the plug and the tubular member. For example, the widest space between portion 2190 and member 2172 may be smaller than a thickness of pull-wire 2924. Typically, a surface of second portion 2192 is disposed further from the inner surface of tubular member 2172, than is the surface of the at least part of portion 2190.
Controller 2930 typically has at least three controller configurations, each configuration having a different relative disposition of plug 2174 within tubular member 2172. In a first controller configuration, plug 2174 is disposed at a first longitudinal position within tubular member 2172. In a second controller configuration, the plug is disposed at a second longitudinal position within the tubular member, the second position being more proximal (e.g., closer to a position outside the body; typically upstream) than the first longitudinal position. In a third controller configuration, the plug is disposed at a third longitudinal position, distal (e.g., downstream) to the first longitudinal position, such that at least restricting portion 2190 is disposed outside of (e.g., distal to) the tubular member.
Controller 2930 has at least one locking configuration, in which (1) at least part of restricting portion 2190 is disposed inside the lumen of tubular member 2172, and (2) pull-wire 2924, when coupled to the controller, is generally not decouplable from the controller. Typically, the first and second controller configurations, described hereinabove, are locking configurations. Controller 2930 further has at least one open configuration, in which (1) at least restricting portion 2190 is disposed outside the lumen of tubular member 2172, and (2) pull-wire 2924 is decouplable from the controller. Typically, the third controller configuration, described hereinabove, is an open configuration.
Typically, and as shown in
Controller 2930 is typically controlled (e.g., the configurations of the controller, such as the disposition of plug 2174 within tubular member 2172, are typically selected), via a control rod 2175, using an extracorporeal controller, such as a control handle 2932, typically disposed at a proximal end of support-delivery apparatus 2960. Control handle 2932 comprises at least one adjuster 2934, each adjuster configured to control at least one clip 2900 of prosthetic valve support 2040b. Typically, control handle 2932 comprises two adjusters 2934, each adjuster configured to independently control one clip 2900. For clarity, however, adjusters 2934 are shown operating simultaneously. Typically, but not necessarily, adjuster 2934 has pre-defined positions in which it can reside, each pre-defined position of the adjuster corresponding to a respective configuration of controller 2930. That is, moving adjuster 2934 between the pre-defined positions thereof, moves controller 2930 between the configurations thereof. For illustrative purposes only, example pre-defined positions (A), (B) and (C) are indicated.
During delivery of support 2040b, and as shown in
For some applications, visualization (e.g., imaging) techniques such as ultrasound are used to facilitate and/or confirm the coupling of clips 2900 to leaflets 2082. For example, an echocardiogram may be used to observe native leaflets 2082, and movement thereof. For some applications, coupling of both native leaflets by clips 2900 is accompanied by a generally lemniscate (e.g., ‘
For some applications of the invention, clips 2900 further comprise a securing element (not shown), configured to secure the clips in the closed configuration, following coupling of the clips to the native leaflets. For some applications of the invention, the securing element is configured to secure the clips in one or a pre-defined selection of closed configurations (e.g., in a partially-closed configuration).
Reference is made to
Movement of controller 2930 into the third position thereof (i.e., moving at least part of plug 2174 outside of tubular member 2172) allows pull-wire 2924 to decouple from the controller. For some applications, pull-wire 2924 is configured to automatically decoupled from the controller when the controller moves into the third position. For example, the pull-wire may comprise a shape-memory (e.g., resilient, pseudoelastic and/or superelastic) material configured to lift the loop of the pull-wire away (e.g., laterally away) from plug 2174 when restricting portion 2190 moves outside of the tubular member. Non-limiting examples of materials that pull-wire 2924 may comprise include nickel-titanium (Nitinol), stainless steel, nickel cobalt, cobalt chrome, titanium, tantalum, palladium, polyester, PTFE, nylon, and cotton. For some applications of the invention, pull-wire 2924 is biodegradable (e.g., bioabsorbent).
Reference is now made to
Immediately prior to the release of prosthetic valve support 2040b from the overtube, the total length of overtube 2044 and support 2040b may be double or more than that of the overtube or support alone. For some applications, this extra length can hinder the movement and/or removal of the overtube from the body of the subject. For some applications, overtube 2044 comprises a flexible and/or soft material, such as a fabric or polymer, thereby becoming flexible as support 2040b is removed from within the overtube. It is hypothesized that this composition/configuration of overtube 2044 facilitates deployment of support 2040b, and removal of the overtube from the body of the subject.
The two phases illustrated in
Reference is now made to
Upstream support portion 2041 and clips 2900 are typically configured such that, when support 2040b is implanted at the native valve, upstream support portion inhibits downstream (e.g., ventricular) movement of support 2040b, and clips 2900 inhibit upstream (e.g., atrial) movement of the support. Typically, clips 2900 are configured to couple the prosthetic valve support to the native valve such that upstream support portion 2041 is in contact with the upstream side of the native valve (e.g., with the upstream side of the native annulus). For some applications, clips 2900 are the only component of prosthetic valve support 2040b that inhibits upstream movement of prosthetic valve support.
The dimensions of upstream support portion 2041 in the implanted configuration thereof are typically similar to those of the same portion in the fully uncompressed configuration thereof, with any difference between the configurations typically due to the portion being implanted. For example, in some applications in which upstream support portion 2041 is generally flat in the fully uncompressed (e.g., unconstrained uncompressed) configuration thereof, when support 2040b is implanted at the native valve, clips 2900 apply a downstream force to inner perimeter 2068 of upstream support portion 2041, thereby inducing portion 2041 to assume a frustoconical shape in the implanted configuration thereof. When upstream support portion 2041 is generally frustoconical in the implanted configuration thereof, a surface of portion 2041 typically has an angle of less than 60 degrees (e.g., less than 45 degrees) from a plane of the smaller base of the frustum. (As shown in
Thus, in general, as shown in and described with reference to
When implanted at the native valve, and thereby in the implanted configuration thereof, no part of upstream support portion 2041 is disposed downstream of native leaflets 2082 (e.g., no part of portion 2041 is disposed in ventricle 2028). Typically, when prosthetic valve support 2040b is implanted at the native valve, no part of support 2040b that circumscribes a space (e.g., opening 2045) is disposed downstream of the native leaflets. For some applications, when prosthetic valve support 2040b is implanted at the native valve, no part of support 2040b that circumscribes a space is disposed downstream of the native annulus.
When implanted at the native valve, and thereby in the implanted configuration thereof, a height (i.e., a length along an upstream-to-downstream axis ax1 from a most upstream end to a most downstream end) of upstream support portion 2041, is typically less than 20 mm (e.g., less than 10 mm, such as less than 5 mm). Typically, when prosthetic valve support 2040b is implanted at the native valve, no part of the support that circumscribes a space has a height of more than 20 mm. For some applications, when prosthetic valve support 2040b is implanted at the native valve, no part of the support that circumscribes a space has a height of more than 10 mm. For some applications, when prosthetic valve support 2040b is implanted at the native valve, no part of the support that circumscribes a space has a height of more than 5 mm.
As described hereinabove with reference to
As regions of prosthetic valve 2042 are successively exposed as they exit delivery tube 2060, they expand (e.g., radially). When delivery tube 2060 is withdrawn in the downstream direction, the upstream end of the prosthetic valve is exposed, and expands, thereby coupling the prosthetic valve to the upstream support portion of prosthetic valve support 2040b, as shown in
As shown in
Once delivery tube 2060 is fully withdrawn from prosthetic valve 2042, and the prosthetic valve is fully deployed (e.g., in the implanted configuration thereof), delivery tube 2060 is removed from the body of the subject. For some applications, when the delivery tube is withdrawn in the downstream direction (e.g., ventricularly), it is removed from the body via the lumen of the prosthetic valve, as shown in
As described hereinabove (e.g., with reference to
It is thereby hypothesized that, following implantation of prosthetic valve support 2040b, the heart of the subject is able to continue pumping blood sufficiently to support the subject for longer than a minute, e.g., longer than 2 minutes, e.g., longer than 5 minutes, such as longer than an hour. It is thereby hypothesized that a period of generally normal physiological activity of the subject of up to a minute, e.g., up to 2 minutes, e.g., up to 5 minutes, such as up to an hour, between implantation of support 2040b and implantation of prosthetic valve 2042 (e.g., as described with reference to
Reference is again made to
Reference is made to
Reference is now made to
Stabilizing element 3062 is hypothesized to increase the stability of prosthetic valve support 2040c at the native valve. For example, element 3062 is hypothesized to at least partly inhibit lateral movement (e.g., rotation around an atrial-ventricular axis, e.g., ‘yaw’) of the support and/or clips, when the support is implanted at the native valve. Element 3062 is further hypothesized to reduce rolling movement (e.g., movement around a lateral axis, e.g., an axis between two clips 2900, e.g., ‘pitch’ and ‘roll’) of implant 2030c, including inversion (e.g., ‘flipping’) of the implant, following deployment (e.g., implantation) of prosthetic valve 2042.
For some applications of the invention, stabilizing element 3062 is further hypothesized to stabilize clips 2900 during deployment of the elements, e.g., by facilitating coupling thereof to delivery apparatus, such as apparatus 2960.
For some applications of the invention, a similar generally lemniscate configuration is formed by element 3062 when prosthetic valve support 2040c is coupled to delivery apparatus, during delivery to the native valve (e.g., as described for support 2040b with reference to
Similarly to support 2040b (described with reference to
When implanted at the native valve, and thereby in the implanted configuration thereof, no part of stabilizing element 3062 is disposed upstream of native leaflets 2082 (e.g., no part of element 3062 is disposed in atrium 2026). Typically, when prosthetic valve support 2040c is implanted at the native valve, no part of support 2040c that circumscribes a space (e.g., portion 2041, which circumscribes opening 2045 and/or element 3062, which circumscribes opening 3064) traverses (e.g., fully traverses) the native annulus.
When implanted at the native valve, and thereby in the implanted configuration thereof, a height (i.e., a length along an upstream-to-downstream axis ax2 from a most upstream part to a most downstream part) of stabilizing element 3062, is typically less than 20 mm (e.g., less than 10 mm, such as less than 5 mm). For example, stabilizing element 3062 typically has a thickness of less than 20 mm (e.g., less than 10 mm, e.g., less than 5 mm, such as less than 1 mm). Typically, when prosthetic valve support 2040c is implanted at the native valve, no part of the support that circumscribes a space has a height of more than 20 mm. For some applications, when prosthetic valve support 2040c is implanted at the native valve, no part of the support that circumscribes a space has a height of more than 10 mm. For some applications, when prosthetic valve support 2040c is implanted at the native valve, no part of the support that circumscribes a space has a height of more than 5 mm.
For some applications of the invention, stabilizing element 3062 is configured (e.g., dimensioned) such that, when the prosthetic valve is expanded within the opening of the stabilizing element, the stabilizing element restricts the full expansion of the downstream portion of the prosthetic valve. That is, for some applications, upon expansion of the prosthetic valve, a transverse cross-sectional dimension (e.g., area) defined by a downstream portion of the prosthetic valve is determined (e.g., restricted) by a transverse cross-sectional dimension (e.g., area) of opening 3064 of the stabilizing element. For some applications, one or more dimensions of opening 3064, defined by stabilizing element 3062, are substantially equal to one or more dimensions of opening 2045, defined by upstream support portion 2041. For some such applications, the expansion of both the downstream and upstream portions of the prosthetic valve are restricted to substantially the same transverse cross-sectional dimensions, thereby facilitating the primary structural element of the prosthetic valve to assume a generally prismatic (e.g., generally cylindrical) shape.
For applications where stabilizing element 3062 limits the expansion of prosthetic valve 2042, a radially-expansive force is thereby applied by prosthetic valve 2042 to stabilizing element 3062. The radially-expansive force typically couples the prosthetic valve to the stabilizing element. That is, for some applications, prosthetic valve 2042 is couplable to the stabilizing element. For some applications, the prosthetic valve is coupled to the stabilizing element by alternative or additional means. For example, the stabilizing element may comprise barbs and/or hooks, which facilitate coupling to the prosthetic valve.
For some applications of the invention, at least part (e.g., an inner surface) of stabilizing element 3062 comprises a friction coating that is configured to increase friction and, thereby, coupling between the stabilizing element and the prosthetic valve.
For some applications of the invention, at least part of stabilizing element 3062 is shaped to define ridges, which are configured (e.g., dimensioned) to protrude (e.g., interpose) within corresponding voids defined by the lattice structure of the prosthetic valve. The ridges facilitate coupling of the stabilizing element to the prosthetic valve, e.g., by inhibiting axial movement of the prosthetic valve through opening 3064.
For some applications of the invention, a soft (e.g., crushable) material is disposed on the inner surface of stabilizing element 3062 (e.g., the stabilizing element comprises the soft material). When prosthetic valve 2042 expands, and applies radially-expansive force to the stabilizing element, (1) the struts of the lattice structure of the prosthetic valve compress (e.g., crush) the parts of the soft material against which the struts apply the force, and (2) the parts of the soft material that are disposed between the struts (i.e., that are disposed at voids defined by the lattice structure), form ridges that protrude between the struts (i.e., protrude into the voids). The protruding parts of the soft material facilitate coupling of the stabilizing element to the prosthetic valve, e.g., by inhibiting axial movement of the prosthetic valve through opening 3064, such as by increasing friction.
For some applications of the invention, prosthetic valve 2042 (e.g., the primary structural element of prosthetic valve 2042) is shaped to define a circumferential groove that is configured (e.g., dimensioned) to receive stabilizing element 3062. That is, for some applications of the invention, stabilizing element 3062 is configured (e.g., dimensioned) to be placeable in a circumferential groove defined by prosthetic valve 2042. When prosthetic valve 2042 is deployed, and expands within opening 3064, element 3062 is disposed in the groove, thereby further facilitating coupling of the stabilizing element to the prosthetic valve, e.g., by inhibiting axial movement of the prosthetic valve through the opening 3064.
Reference is made to
After clips 2900 have been coupled to native leaflets 2082, delivery tube 2976 is withdrawn distally (e.g., atrially) from upstream support portion 2041, such that downstream end 2053 of portion 2041 is exposed, and expands to define inner perimeter 2068 as described hereinabove, mutatis mutandis. As successively more distal (e.g., upstream) parts of portion 2041 are exposed as they exit delivery tube 2976, they expand (e.g., radially). When portion 2041 is sufficiently exposed from the delivery tube (e.g., when upstream end 2055 is exposed from the delivery tube), upstream end 2055 expands to define outer perimeter 2068, as described hereinabove, mutatis mutandis. As shown in
Once prosthetic valve 2042 is completely exposed (e.g., deployed), the prosthetic valve thereby assumes its implanted configuration, as described hereinabove. Support-delivery apparatus 2980 (including delivery tube 2986) is subsequently withdrawn from the body of the subject.
Reference is made to
Reference is again made to
Reference is again made to
For some applications of the invention, following implantation at the native valve, no part of the prosthetic valve support that circumscribes a space, traverses the native leaflets and/or annulus. For example, following implantation, the upstream support portions described hereinabove (e.g., upstream support portions 41 and 2041) are typically disposed only upstream of the native leaflets and/or annulus. Similarly, for applications in which the prosthetic valve support comprises a stabilizing element (e.g., stabilizing element 1062 or 3062), following implantation, the stabilizing element is typically disposed only downstream to the native leaflets and/or annulus. It is hypothesized that this advantageously facilitates continued function of the native leaflets following implantation of the prosthetic valve support, and prior to the implantation of a prosthetic valve, as described hereinabove.
Typically, the perimeter (e.g., the circumference) of the spaces defined by the upstream support portions and stabilizing elements described hereinabove, is greater than 60 mm. Typically, the upstream support portions and stabilizing elements have respective heights of less than 10 mm. For some applications of the invention, no part of the prosthetic valve support that circumscribes a space that has a perimeter that is greater than 60 mm, has a height (e.g., a depth) that is greater than 10 mm. For example, prosthetic valve supports that do not comprise a cylindrical element (e.g., cylindrical element 90 or 690), do not comprise a part that (1) circumscribes a space that has a perimeter that is greater than 60 mm, and (2) has a height (e.g., a depth) that is greater than 10 mm.
Reference is again made to
(1) Any of the prosthetic valves described hereinabove (including features and/or components thereof) may be used in combination with any of the prosthetic valve supports (including features and/or components thereof) described hereinabove (e.g., any of the prosthetic valve supports described hereinabove may be used to facilitate implantation of any of the prosthetic valves described hereinabove), mutatis mutandis;
(2) any of the prosthetic valve supports described hereinabove may comprise any of the upstream support portions, tissue-engaging elements (e.g., support-anchoring elements and/or clips), connectors (e.g., flexible and/or length-adjustable connectors), holding wires and/or stabilizing elements described hereinabove, mutatis mutandis;
(3) any of the prosthetic valves or prosthetic valve supports described hereinabove may comprise any of the coupling functionalities (e.g., barbs, coupling leads and/or support-engaging elements) described hereinabove, for coupling a prosthetic valve support (e.g., support-anchoring elements thereof) to a prosthetic valve, mutatis mutandis;
(4) any of the tissue-engaging elements, and/or elements thereof, described hereinabove may be used in combination with any one of prosthetic valve supports or prosthetic valves described herein, mutatis mutandis. For example, tissue-engaging elements (e.g., support-anchoring elements) that are described hereinabove for coupling a prosthetic valve support to the native valve, may be alternatively or additionally used to couple a prosthetic valve to the native valve (the tissue-engaging element thereby acting as a valve-anchoring element), mutatis mutandis. Similarly, tissue-engaging elements (e.g., valve-anchoring elements) that are described hereinabove for coupling a prosthetic valve to the native valve, may be alternatively or additionally used to couple a prosthetic valve support to the native valve (the tissue-engaging element thereby acting as a support-anchoring element), mutatis mutandis;
(5) any of the implantation techniques described hereinabove (e.g., those described with reference to
(6) any of the delivery apparatus described hereinabove (e.g., those described with reference to
(7) any of the techniques and apparatus described hereinabove (e.g., those described with reference to
Reference is again made to
Reference is again made to
For some applications, the prosthetic valve support (e.g., the upstream support portion thereof) is not covered with the covering, and is configured to allow flow of blood therethrough. For example, the prosthetic valve support may be configured to allow flow of blood through the interface between the valve support and the prosthetic valve, in order to accommodate antegrade flow of blood between the subject's atrium and the subject's ventricle that is greater than can be accommodated by blood flowing through the prosthetic valve alone. For some such application of the invention, the prosthetic valve support is not covered with the covering and is configured to support prosthetic valve, such that the leaflets of the native valve (1) move in response to the beating of the heart, (2) coapt with each other and/or with the primary structural element of the prosthetic valve, and (3) inhibit (e.g., prevent) retrograde flow of blood through the prosthetic valve support.
Reference is yet again made to
Reference is made to
Reference is again made to
It will be appreciated by persons skilled in the art that the present invention is not limited to what has been particularly shown and described hereinabove. Rather, the scope of the present invention includes both combinations and subcombinations of the various features described hereinabove, as well as variations and modifications thereof that are not in the prior art, which would occur to persons skilled in the art upon reading the foregoing description.
This application is a Continuation of U.S. Ser. No. 16/881,350 to HaCohen, filed May 22, 2020, which published as US 2020/0330221 and which is a Continuation of U.S. Ser. No. 16/460,313 to Gross et al., filed Jul. 2, 2019 (now U.S. Pat. No. 10,695,173), which is a Continuation of U.S. Ser. No. 16/045,059 to Gross et al., filed Jul. 25, 2018 (now U.S. Pat. No. 10,376,361), which is a Continuation of U.S. Ser. No. 15/213,791 to Gross et al., filed Jul. 19, 2016 (now U.S. Pat. No. 10,245,143), which is a Continuation of U.S. Ser. No. 14/237,264 to Gross et al., filed May 23, 2014 (now abandoned), which published as US 2014/0324164 and which is the US National Phase of PCT Application IL2012/000292 to Gross et al., filed Aug. 5, 2012, which published as WO 2013/021374 and which: (1) claims priority from: U.S. 61/515,372 to Gross et al., filed Aug. 5, 2011;U.S. 61/525,281 to Gross et al., filed Aug. 19, 2011;U.S. 61/537,276 to Gross et al., filed Sep. 21, 2011;U.S. 61/555,160 to Gross et al., filed Nov. 3, 2011;U.S. 61/588,892 to Gross et al., filed Jan. 20, 2012; andU.S. Ser. No. 13/412,814 to Gross et al., filed Mar. 6, 2012, (now U.S. Pat. No. 8,852,272) all of which are incorporated herein by reference; and(2) is a Continuation-In-Part of U.S. Ser. No. 13/412,814 to Gross et al., filed Mar. 6, 2012 (now U.S. Pat. No. 8,852,272). This application is related to International Patent Application IL2012/000293 to Gross et al., entitled, “Percutaneous mitral valve replacement and sealing,” filed Aug. 5, 2012, which published as WO 2013/021375.
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| 20210401573 A1 | Dec 2021 | US |
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