|Publication number||US20100131055 A1|
|Application number||US 12/614,878|
|Publication date||May 27, 2010|
|Filing date||Nov 9, 2009|
|Priority date||Apr 24, 2003|
|Also published as||CA2523262A1, CA2523262C, DE602004023708D1, EP1615595A1, EP1615595B1, EP2133039A1, EP2133039B1, US7618447, US8221492, US20040260389, US20070260327, US20130018453, WO2004096100A1|
|Publication number||12614878, 614878, US 2010/0131055 A1, US 2010/131055 A1, US 20100131055 A1, US 20100131055A1, US 2010131055 A1, US 2010131055A1, US-A1-20100131055, US-A1-2010131055, US2010/0131055A1, US2010/131055A1, US20100131055 A1, US20100131055A1, US2010131055 A1, US2010131055A1|
|Inventors||Brian C. Case, Michael L. Garrison, Andrew Hoffa, Darin G. Schaeffer, Jacob A. Flagle|
|Original Assignee||Cook Incorporated|
|Export Citation||BiBTeX, EndNote, RefMan|
|Referenced by (30), Classifications (17)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This invention relates to medical devices, more particularly to intravascular valve prostheses and the like.
The venous system includes a series of valves that function to assist the flow of blood returning to the heart. These natural valves are particularly important in the lower extremities to prevent blood from pooling in the lower legs and feet during situations, such as standing or sitting, when the weight of the column of blood in the vein can act to prevent positive blood flow toward the heart. This condition, commonly known as ‘chronic venous insufficiency’, is primarily found in individuals in which gradual dilation of the veins, thrombotic events, or other conditions prevent the leaflets of the native valves from closing properly. This leads to significant leakage of retrograde flow such that the valve is considered ‘incompetent’. Chronic venous insufficiency is a potentially serious condition in which the symptoms can progress from painful edema and unsightly spider or varicose veins to skin ulcerations. Elevation of the feet and compression stocking can relieve symptoms, but do not treat the underlying disease. Untreated, the disease can impact the ability of individuals to perform in the workplace or maintain their normal lifestyle.
To treat venous valve insufficiency, a number of surgical procedures have been employed to improve or replace the native valve, including placement of artificial valve prosthesis. These efforts have met with limited success and have not been widely adopted as a method of treating chronic venous insufficiency. More recently, the search has been to find a suitable self-expanding or radially-expandable artificial valve that can be placed using minimally invasive techniques rather than requiring open surgery and its obvious disadvantages. Thus far, use of prosthetic venous valves has remained experimental only.
While attempts have been made to mimic the function of the natural valve, there is no expandable valve for venous transcatheter placement that includes a combination of the native structural features that individually or collectively, may prove highly advantageous or critical for a successful valve. One common problem evident from early experiences with prosthetic valves is the formation of thrombus around the base of the leaflets, probably due at least in part to blood pooling in that region. In a natural valve, the leaflets are typically located within a sinus or enlargement in the vein. There is some evidence that the pockets formed between the leaflets and the walls of the sinus create vortices of flowing blood that help flush the pocket and prevent blood from stagnating and causing thrombosis around the valve leaflets, which can interfere with the function of the valve. It is thought that the stagnating blood prevents oxygen from reaching the endothelium covering the valve cusps, leading to hypoxia of the tissues which may explain increased thrombus formation typical in that location. Expandable-frame valve prostheses typically are of a generally cylindrical in shape and lack an artificial sinus or pocket space that is sufficient for simulating these natural blood flow patterns. What is needed is an intravenously placed artificial valve that is configured to create more effective flow patterns around the valve structure to circulate the blood or bodily fluids and reduce the likelihood of stagnation and the potential clinical problems that may result.
The foregoing problems are solved and a technical advance is achieved in an illustrative valve prosthesis, such as an artificial venous valve, having a valve structure and a self-expanding or otherwise expandable support structure that upon deployment within the vein, helps create an artificial sinus or larger pocket in the vessel surrounding the valve structure of sufficient size and shape to stimulate flow patterns or vortices which facilitate clearing of the blood or other bodily fluid that would otherwise pool therein. The structural adaptations result in more turbulent flow, increased velocity of flow, larger and/or more numerous vortices, other factors, or a combination of the above that prevent stagnant, hypoxic areas from occurring around the valve structure. Furthermore, the modified flow may also contribute to helping close the leaflets to form a seal and prevent leakage of fluid back through the valve. The artificial sinus or enlarged pockets simulate the function of the natural sinus that exists at the site of most natural valves in the deep veins of the lower legs and which may explain why the problem of thrombus forming around the valve structure has been observed to be a common problem in prosthetic venous valve designs lacking such a sinus area.
In one aspect of the invention, the collapsible support structure of the valve prosthesis is expandable to a particular diameter upon deployment, with the valve prosthesis being configured such that the prosthesis includes an intermediate, substantially ‘open’ section such that the artificial sinus is created by a portion of the duct or vessel that is substantially unsupported by the support structure. The unsupported portion of the vessel can advantageously assume a diameter that is larger than the deployment diameter of the vessel-anchoring or ‘closed’ sections or portions of the collapsible support structure, thereby creating an artificial sinus as blood (or bodily fluid) exerts pressure on the unsupported portion of the vessel wall. In one exemplary embodiment, the expandable support structure comprises a first, proximal portion and a second, distal portion that are interconnected by one or more thin members or struts, such that the largely unsupported region between the first and second (proximal and distal) sections of the support structure forms an artificial sinus (proximal being defined herein as have the same positional orientation as the orifice or opening of the valve structure, which is typically toward the heart in a venous valve). The valve structure is attached about the support structure such that it is largely situated within the unsupported region forming the artificial sinus. For example, the valve structure (defined herein as one or more cooperating leaflets, tubular members, or any flexible structure adapted to seal a passageway in response to changing fluid pressure differentials thereacross) may be attached to the interconnecting members, which can comprise oppositely placed struts having attachment points, (e.g., suture or any suitable structure or method) to facilitate attachment of the valve material.
In another aspect of the invention, the expandable support structure of the valve prosthesis comprises a framework or anchoring portion having an intermediate region that includes an enlarged diameter configured to create an artificial sinus about the valve structure, which is attached inside the intermediate region. In one embodiment, the support structure is made of a superelastic material, such as nitinol, and the intermediate region comprises an expanded or bulging portion that is formed by heat setting the nitinol tubular frame around a mandril or other fixture of the desired configuration using a method well known in the medical arts. The intermediate portion expands to a diameter larger than the proximal and distal portions when the prosthesis is deployed from the delivery system, thereby producing larger pockets around the valve structure which create more effective flow patterns to reduce pooling. In another embodiment, the proximal, distal, and intermediate sections are separate, interconnected sections, such as zig-zag frame or other expandable or self-expanding support or anchoring frames. The intermediate section comprising the artificial sinus includes a first and a second radially expandable or self-expanding portions in which the adjoining ends of each are larger in diameter than the ends which adjoin the proximal and distal sections, respectively. The frustoconical shape of the respective intermediate sections can be accomplished by either forming the section into that shape (i.e., plastic deformation of a tubular prosthesis, heat setting nitinol, laser cutting a frustoconical section of tubing, etc.) or a constraining means, such as a suture or thin wire, can be used to manipulate the relative diameters by feeding the constraining means through the apices of the bend or apertures therein and applying the appropriate amount of tension to create the desired shape. Optionally, a tubular or band-like section can be positioned between opposing frustoconical sections to create a longer artificial sinus.
In yet another aspect of the invention, the proximal end of the collapsible support at which the valve structure is located is expanded (e.g flared outward) such that the expanded end or a combination of the expanded end and adjacent area of the vein forms the artificial sinus.
In still yet another aspect of the invention, the proximal and distal sections are configured to include a substantially open area between them with the valve structure being attached to the distal section such that it is positioned just below the artificial sinus. Optionally, a sleeve of a biomaterial (e.g a bioremodelable material such as small intestinal submucosa (SIS) or another collagenous extracellular matrix) or fabric can be attached over the proximal and distal sections such that it forms a seal between the prosthesis and the vessel wall, including the artificial sinus.
In still yet another aspect of the present invention, the support structure of the prosthesis is configured such that the attachment pathway (defined herein as the interface between the lateral, outer edges of the leaflets and the struts and/or vessel walls to which they are attached to establish and define the shape and configuration of the plurality of leaflets comprising the valve structure as deployed) has a first, proximal portion in which the one or more longitudinal attachment struts extending from the proximal bends or commissures that carry and support the proximal outer edges of the leaflets (and span the orifice) have a strongly longitudinal orientation with respect to the longitudinal axis of the prosthesis and valve structure, and a distal portion of the attachment pathway that extends circumferentially (laterally) and distally from the longitudinal axis to form the bottom or distal edge of the outer leaflet edge or perimeter. When viewed from the side, the support frame and attached leaflet is configured such that the angle (angle .alpha.) formed between the opposing leaflets, as carried along the proximal attachment pathway, is substantially less than the angle (angle .beta.) formed between distal attachment pathways and the vessel walls. This configuration results in leaflets having large coaptable area relative to the overall surface area, which improves sealing (including reducing the effects of retraction by the valve material) and allows for larger pockets surrounding the leaflets which, like the sinus, facilitate the creation of larger, stronger vortices of retrograde flow that help close the leaflets and clear away blood or fluid that could otherwise stagnate under conditions where the surrounding pockets are smaller in size. As used herein, the term ‘retrograde flow’ is defined as bodily fluid traveling in a distal direction (toward the feet), whether due to gravitational forces, redirection due to contact with the prosthesis or bodily lumen walls, or by some other means.
A first embodiment of this aspect of the invention includes a frame comprising a pair of longitudinal attachment struts originating from each commissure bend. The struts extend in generally longitudinal direction, diverging relatively or not at all toward the distal end of the prosthesis before more acutely diverging as they curve laterally and circumferentially away from the proximal strut portions such that the transition between the proximal and distal portions of attachment pathway comprises a bend having a radius that is distinctly smaller than that of the adjacent strut portions (the proximal portions being straight some embodiments). The distal attachment pathways converge to define the bottom outer edge of each leaflet. In a second embodiment of this aspect of the invention, the support frame of the prosthesis includes a pair of substantially parallel longitudinal attachment struts to which the leaflets are attached to form the proximal portion of the attachment pathway, and distal attachment struts extending circumferentially and laterally outward from the substantially parallel struts to form the distal portion of the attachment pathway. The support frame carrying the valve structure may be advantageously comprised of radial sections (e.g., quadrants in a bicuspid valve) that are of an identical pattern but with alternating orientation such as to provide for radial stability and better expandability characteristics. The radial section not carrying the leaflet proximal outer edges serves as lateral support structure for adding longitudinal stability and help protecting the leaflets from adhering to the vessel walls. The parallel struts provide for advantageous bending and torsional characteristics such that the frame has utility as a stent. In an alternate embodiment of the support structure, the lateral outer edges of the opposing leaflets can be attached to single longitudinal attachment strut having a pair of distal struts extending laterally outward and circumferentially to carry the bottom half of the leaflet and define the overall shape thereof. The strut may be thicker than adjacent struts and include aperture therealong for facilitating attachment of the valve structure.
In still yet another aspect of the present invention, the proximal section of the valve is wider in diameter at its proximal end, which anchors the prosthesis in the vessel, and narrower at the interface between the proximal and intermediate sections. This, in combination with a leaflet structure that maximizes pocket size, results in retrograde flow being subject to a Venturi effect which increases flow and the strength of the vortices to close the valve and clear the pockets of potentially stagnating fluids.
The configuration of the basic units of the support structure and valve structure is not particularly critical for an understanding of the invention. Numerous examples are well known in the prior art and may be found in the disclosure of Applicant's provisional application Ser. No. 60/403,783 entitled, ‘Implantable Vascular Device,’ filed Aug. 15, 2002 which is expressly incorporated by reference herein.
Embodiments of the present invention will now be described by way of example with reference to the accompanying drawings, in which:
The present invention, selected examples of which are illustrated in
It should be understood that the materials used to comprise the support structure 11 can be selected from a well-known list of suitable metals and polymeric materials appropriate for the particular application, depending on necessary characteristics that are required (self-expansion, high radial force, collapsibility, etc.). The materials used for the valve structure 12 can comprise a synthetic material or biologically-derived material appropriate for the clinical application; however, investigational studies have demonstrated that a bioremodelable material (such as an collagenous extracellular matrix (e.g., small intestinal submucosa), pericardial, or a growth factor-enhanced material may have superior anti-thrombogenic properties within the body as the native cells and tissue gradually replace the original leaflet material. The number of leaflets possible for embodiments of the present invention can be two, three, four, or any practical number, but bi-leaflet valves may prove advantageous in low-flow venous situation as compared to tri-leaflet embodiments, such the type used as heart valves which are subject to high-flow situations where thrombus formation is far less of a problem.
In the embodiments of
In the embodiments of the present invention, the anchoring portions 24 may function as stents to help the bodily passage remain patent, but their primary function is limited to engaging the bodily passage to anchor the prosthesis thereagainst. The support structure 11 and anchoring portions 24 also may be configured to be readily collapsible as with a normal vein. Since the diameters of the proximal and distal sections 15,17 generally assume a fixed diameter after deployment, the intermediate section, which is mostly unsupported or covered by structure, expands to form a bulging region of the vessel that functions as an artificial sinus 34. Although the interconnecting means 36 advantageously permit the proximal and distal sections 15,17 to be deployed together at a fixed distance from one another, it is within the scope of the invention to have the valve prosthesis 10 comprise separate unconnected sections that are deployed sequentially at an effective distance from one another to create an artificial sinus 34 therebetween. Additionally, the interconnecting means 36 can comprise suture, fabric, or some other non-rigid material to join the proximal and distal sections 15,17 and define the optimal length of the intermediate section 16, without interfering with the creation of the artificial sinus 34. To deploy a prosthesis 10 having a flexible interconnecting means 36, one of either the proximal or the distal sections 15,17 can be deployed first with the delivery system then being slowly withdrawn until the interconnecting means 36 becomes taut, whereby the opposite section is then deployed.
In the illustrative embodiment, the valve structure 12 comprises a pair of leaflets 26 that are situated in the intermediate section and attached to the proximal section 15 at two commissural points 27,28, each located at the proximal ends of the interconnecting struts 18,19, using an appropriate attachment means 30, such as suture, adhesive, fasteners, tissue welding using heat and/or pressure, etc. The leaflets 26 are attached about their distal ends 29 to the distal section 17 of the support structure 11 using the same or an other suitable attachment means 30. The valve structure 12 is configured so that it advantageously expands with the deployment of the proximal and distal sections 15,17 such that the outer edges 39 thereof contact the vessel wall sufficiently to at least substantially prevent leakage of bodily fluid around the valve structure 12. Optionally, the wall-engaging outer edges of the leaflets 26 can be reinforced with a separate frame 32 that is attached to or incorporated into the outer edges 37 to improve sealing with the vessel wall 38. An example of such a frame 32 is depicted in embodiment shown in
Another method of creating the artificial sinus 34 is depicted in
FIGS. 9,11, and 13-20 comprise embodiments of an artificial valve prosthesis 10 in which support structure 11 carrying the leaflets 26 is configured to increase the leaflet contact (coaptable) area 57 about the proximal portion of the valve structure 12 without relying on built-in slack within the material to bring the leaflets in closer proximity and provide for a extensive sealing area, longitudinally. As defined in this application, the leaflet contact area 57 comprises a longitudinal portion along the valve structure 12 in which the facing surfaces of opposing leaflets 26 (two or more) coapt or lie in close proximity to one other while in a dry or resting, neutral state (i.e., the pressure differentials across the valve orifice are essentially equalized such that the leaflets are not being forced together or apart due to external forces, such as fluid flow), when the prosthesis is an expanded or deployed configuration. The support frame 11 may be configured for maximizing the extent of the leaflet contact area 57 by including one or more longitudinal attachment struts 49,50 that define at least the proximal portion 75 of the attachment pathway 74 of each leaflet lateral outer edge 87,88 (the terms outer edge 39 and lateral outer edges 87,88 being defined herein as the area or zone along the leaflet that comprises the sealing interface). The longitudinal attachment struts 49,50/proximal attachment pathways 75 have a substantially longitudinal orientation (e.g., substantially parallel) with respect to the longitudinal axis 64 of the prosthesis (and valve structure 12). At a point generally proximate the distal end 89 of the leaflet contact area 57 (the proximal portion 96 of the leaflet), the distal portions 76 of the adjacent attachment pathways 74 (which are joined proximally about a commissural point) diverge from one another (forming a generally Y-shaped pathway configuration) and assume a much more circumferential orientation than that of the proximal portion 75 of the pathway such that the outer leaflet lateral edges 87,88 of each leaflet converge at a point lateral to the free inner edge 84 thereof to seal the passageway and form the distal portion 96 of the leaflet that defines the bottom 96 or ‘floor’ of the pocket 55 or intravascular space adjacent the outer surfaces of each of the leaflets, which generally assumes a strongly cupped or curved shape such that the leaflet assumes a generally ‘folded’ appearance due to the acutely angled attachment pathway 74 with the proximal portion of the leaflet having a strong longitudinal orientation with respect to the prosthesis and vessel and the bottom portion 96 having a strongly perpendicular orientation relative to the longitudinal axis of the vessel and prosthesis. It should be noted that the commissures 27,28, while located about the proximal end 13 of the illustrative prosthesis 10, may be located proximal thereto such that additional support structure 10 extends proximally, such as in the embodiments of FIGS. 2-8,12.
By extending or maximizing the leaflet contact area and decreasing the radius of the curvature of the leaflet (increasing curvature) about the distal portion thereof, the basal or distal portion of the pocket 35 adjacent each leaflet is enlarged to facilitate and maximize the size and/or velocity of the flow vortices 55,56 formed therein during retrograde flow. During pre-clinical investigations, these broader pockets have been shown to be especially advantageous in bi-leaflet artificial valve designs implanted in the venous system, these valves exhibiting a marked reduction in thrombus formation as compared to earlier designs. The improvement in flow dynamics for the purpose of clearing the pocket 35 of stagnant blood that can thrombose and compromise valve function or lead to other complications is depicted in a comparison of
The embodiment depicted in
The lateral arms 77,78 of the lateral support structure 53,54, that connect to the longitudinal attachment struts 49,50 each include a strut 68 that carries a proximal radiopaque marker 67 used to facilitate orientation of the device 10 and provide additional support. An identical distal strut 90 and an optional radiopaque marker 91 is located distal to the longitudinal attachment struts 49,50 and attached to the distal attachment struts 51,52 to serve a similar orientation and stabilization function. An integral barb 25 is located about the commissural bends 27,28 that interconnect the longitudinal attachment struts 49,50. The parallel longitudinal attachment struts 49,50 are also interconnected about their distal ends by a short interconnecting strut 81 such that an elongate closed cell 92 is formed. The width of cell 92 is not critical, although it may be made sufficiently narrow such that it serves to further pin or anchor the leaflets 60,61 to the struts 49,50, which could be especially advantageous in fixation if the leaflet material retracts during the remodeling process. A preferred width between the two struts 49,50 would be between 0-5 mm, with 0-3 mm being more preferred and 0-1 mm being most preferred. If the spacing is too wide, gaps may be created between the opposing leaflets which could allow for an unacceptable amount of reflux through the valve.
A similar frame design is shown in
The illustrative support structure 11 in
The amount of contactable or coaptable area 57 can be expressed in different ways. In the present invention, the length of the leaflet contact area 57 (or proximal portion 75 of the attachment pathway) in a typical venous valve prosthesis is preferably at least 2 mm and as much as 50 mm (depending on the configuration of the valve prosthesis), with a more preferred length of 5-30 mm and a most preferred range of 5-15 mm. In an average sized venous valve having a length of 25 mm, the preferred range of the leaflet contact area 57 or proximal attachment pathway 75 would be 10-80% of the prosthesis length (2.5-20 mm), assuming the valve structure 12 is generally as long as the support frame 11. A more preferred leaflet contact area 57 would comprise 30-60% with 35-55% being most preferred in a prosthesis of the same general type as depicted. The relationship between leaf contact area and the diameter of the vessel may be a factor in optimizing the functionality of the valve prosthesis 10. Preferably, the length of the longitudinal attachment struts 49,50 and/or leaflet contact area 57 is 25 to 250% of the nominal vessel diameter with a more preferred range of 25-150%.
The amount of slack in the leaflet material also helps determine how well the leaflets coapt during retrograde flow and how large of an opening they permit during antegrade flow. Preferably, but not essentially, the prosthesis is configured such that the distance formed between the leaflets in their fully open position and the vessel diameter remains preferably between 0-100% of the vessel diameter, with a more preferred range of 20-80% of the vessel diameter and a most preferred range of 50-70%. By substantially orienting the longitudinal attachment struts 49,50 with the longitudinal axis 64 of the prosthesis, less slack is necessary for optimal or extended coaptation. Not having the leaflets regularly contact the outer walls of the vessel can be especially important when using a bioremodelable material, such as an ECM, which can partially or completely adhere to the wall over time as tissue grows into the leaflets, thus compromising the functionality of the valve.
It should be noted that the support structure and valve structure shown in each of the figures in the application are merely exemplary of the numerous well-known possibilities, many others of which are disclosed in U.S. patent application Ser. No. 10/642,372 entitled, ‘Implantable Vascular Device,’ filed Aug. 15, 2003 and whose disclosure is expressly incorporated by reference herein. For example, the valve structure may comprise more than the illustrative two leaflets or comprise leaflets of other shapes and configuration. The valve structure may also comprise a non-leaflet valve such as one or more tubular sleeves or other configurations adapted to restrict fluid flow. With regard to the support structure, it may be formed from wire, cut from a section of cannula, molded or fabricated from a polymer, biomaterial, or composite material, or a combination thereof. The pattern (i.e., configuration of struts and cells) of the anchoring portion(s) that is selected to provide radial expandability to the prosthesis is also not critical for an understanding of the invention. Any other undisclosed or incidental details of the construction or composition of the various elements of the disclosed embodiment of the present invention are not believed to be critical to the achievement of the advantages of the present invention, so long as the elements possess the attributes needed for them to perform as disclosed. The selection of these and other details of construction are believed to be well within the ability of one of even rudimentary skills in this area, in view of the present disclosure. Illustrative embodiments of the present invention have been described in considerable detail for the purpose of disclosing a practical, operative structure whereby the invention may be practiced advantageously. The designs described herein are intended to be exemplary only. The novel characteristics of the invention may be incorporated in other structural forms without departing from the spirit and scope of the invention. The invention encompasses embodiments both comprising and consisting of the elements described with reference to the illustrative embodiments. Unless otherwise indicated, all ordinary words and terms used herein shall take their customary meaning as defined in The New Shorter Oxford English Dictionary, 1993 edition. All technical terms shall take on their customary meaning as established by the appropriate technical discipline utilized by those normally skilled in that particular art area. All medical terms shall take their meaning as defined by Stedman's Medical Dictionary, 27th edition.
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|International Classification||A61F2/00, A61F2/06, A61F2/24|
|Cooperative Classification||A61F2230/008, A61F2002/068, A61F2220/0016, A61F2220/0008, A61F2/2475, A61F2230/0076, A61F2250/0039, A61F2250/0037, A61F2/2418, A61F2230/0054, A61F2230/0078|
|European Classification||A61F2/24V, A61F2/24D6|