1. The Field of the Invention
The present invention relates to an endoprosthesis deliverable and deployable within a body vessel of a human or animal. More particularly, the invention relates to an interconnected, segmented endoprosthesis.
2. The Relevant Technology
Stents, grafts, and a variety of other endoprostheses are well known and used in interventional procedures, such as for treating aneurysms, for lining or repairing vessel walls, for filtering or controlling fluid flow, and for expanding or scaffolding occluded or collapsed vessels. Such endoprostheses can be delivered and used in virtually any accessible body lumen of a human or animal, and can be deployed by any of a variety of recognized means. One recognized indication of an endoprosthesis, such as a stent, is for the treatment of atherosclerotic stenosis in blood vessels. For example, after a patient undergoes a percutaneous transluminal coronary angioplasty or similar interventional procedure; a stent is often deployed at the treatment site to improve the results of the medical procedure and reduce the likelihood of restenosis. The stent is configured to scaffold or support the treated blood vessel; if desired, it can also be loaded with a beneficial agent so as to act as a delivery platform to reduce restenosis or the like. Other suitable examples of medical conditions for which endoprostheses are an appropriate treatment include, but are not limited to, arterial aneurysms, venous aneurysms, coronary artery disease, peripheral artery disease, peripheral venous disease, chronic limb ischemia, blockage or occlusion of the bile duct, esophageal disease or blockage, defects or disease of the colon, tracheal disease or defect, blockage of the large bronchi, blockage or occlusion of the ureter, or blockage or occlusion of the urethra.
An endoprosthesis, such as a stent, is typically delivered by a catheter delivery system to a desired location or deployment site inside a body lumen of a vessel or other tubular organ. The intended deployment site may be difficult to access by a physician and often involves traversing the delivery system through a tortuous luminal pathway. Thus, it can be desirable to provide the endoprosthesis with a sufficient degree of flexibility during delivery to allow advancement through the anatomy to the deployment site. Moreover, it may be desirable for the endoprosthesis to retain structural integrity while flexing and bending during delivery so that cracks do not form.
Current stent design, typically are composed of a series of repeated rings that are connected in series. The stent in a Superficial Femoral Artery (SFA) application undergoes longitudinal, bending, torsional, tensional and radial cyclical loading that can lead to fatigue failures. The stent connection sections or connection elements that join the rings also transmit stress from ring to ring under longitudinal, bending, or torsional loading. In addition, when the stent goes around a curve the connecting elements or sections require the portions of the ring apposed to the outside of the curve to lengthen and the portions of the ring apposed to the inside of the curve to shorten. Lengthening and shortening portions of the ring increase the maximum stress because the ring cannot expand evenly promoting fatigue failures. Current endoprosthesis designs which are subjected to these forces often fail. Failure can result in crack formation and possible stent fracture. In the event of stent fracture, the sharp edges may puncture the vessel, muscle tissue or cause bleeding. Consequently, the fractured stent may cause thrombus formation or blockage within the vessel.
Generally, the present invention includes a segmented endoprosthesis having joined segments. The segments are typically distinct and distinguishable from each other by each segment having a unique configuration different from at least one other segment. Additionally, the segments can be coupled together by various processes well known for interconnecting the materials of endoprostheses.
In one embodiment, the present invention includes a segmented endoprosthesis that has first and second annular elements jointed together via a plurality of couplings. The first annular element can have a plurality of first integrating members on a first longitudinal end. Also, the first annular element can be defined as having a first characterization as described herein. The second annular element can have a plurality of second integrating members on a second longitudinal end. The second integrating members of the second longitudinal side of the second annular element can be disposed adjacent to corresponding first integrating members of the first longitudinal side of the first annular element. Also, the second annular element can be defined as having a second characterization that is the same or different from the first characterization of the first annular element. The plurality of couplings are disposed between and coupling the plurality of first integrating members of the first annular element together with the plurality of second integrating members of the second annular element so as to form the segmented endoprosthesis.
In one aspect, the above-described endoprosthesis can have the first and second characterization types being at least one of material composition, length, diameter, wall thickness, flexibility, shape, structure, drug loading, drug type, shape memory, austenite finish temperature, radial force, or strut elements, and combinations thereof. Such characterization types being the same or different between the first annular element and the second annular element. In another aspect, the couplings can include at least one of a brazing, metallurgical bond, weld, sleeve, mechanical bond (e.g., swaging and/or crimping), or an adhesive. In another aspect, the first and second integrating members include at least one of blunt joinery elements, overlay joinery elements, complementary male and female joinery elements, or complementary finger joinery elements.
In another aspect, the endoprosthesis can be defined by the following: first integrating members each having a first coating; the second integrating members each having a second coating; and the plurality of couplings each comprising the first coating and the second coating. In another aspect, the first coatings and second coatings are comprised of a polymer and each coupling is an adhesive. In another aspect, first coatings and second coatings are comprised of the same polymer and form a sleeve coupling. In another aspect, the first coatings and second coatings can include a metal or a metallic coating. In yet another aspect the metal or metallic coatings can include a radiopaque metal such as gold, tantalum, platinum, rhenium, palladium, or another radiopaque metal or combination of metals.
In one embodiment, the present invention includes a segmented endoprosthesis having a primary annular element coupled to a first end annular element and a second end annular element. The primary annular element can be defined by a primary length and have a plurality of primary integrating members on both first and second longitudinal ends. The primary annular element can have a primary characterization. The first end annular element can be defined by a first length and have a plurality of first integrating members on an integrating longitudinal side. The first integrating members of the first end annular element can be disposed adjacent to corresponding primary integrating members of the first longitudinal side of the primary annular element. The first end annular element can have a first characterization that is the same or different from the primary characterization of the primary annular element. The second end annular element can be defined by a second length and have a plurality of second integrating members on an integrating longitudinal side. The second integrating members of the integrating longitudinal side of the second end annular element can be disposed adjacent to corresponding primary integrating members of the second longitudinal side of the primary annular element. The second end annular element can have a second characterization that is the same or different from the primary characterization of the primary annular element. A first plurality of first couplings can be disposed between and couple the plurality of primary integrating members of the primary annular element on the first longitudinal side with the plurality of first integrating members of the first end annular element. A second plurality of second couplings can be disposed between and couple the plurality of primary integrating members of the primary annular element on the second longitudinal side with the plurality of second integrating members of the second end annular element. As such, the first plurality of first couplings and second plurality of second couplings can form the primary annular element into a segmented endoprosthesis with the first end annular element and second end annular element.
In one aspect, the above-described endoprosthesis can have the first and second characterization types being at least one of material composition, length, diameter, wall thickness, flexibility, shape, structure, drug loading, drug type, shape memory, austenite finish temperature, radial force, or strut elements. In another aspect, any of the couplings can include at least one of a brazing, metallurgical bond, weld, sleeve, mechanical bond (e.g., swaging and/or crimping), or an adhesive. In another aspect, the first and second integrating members include at least one of blunt joinery elements, overlay joinery elements, complementary male and female joinery elements, or complementary finger joinery elements.
In another aspect, the endoprosthesis can be defined by the following: the primary integrating members each having a primary coating; the first integrating members each having a first coating; the second integrating members each having a second coating; the first plurality of first couplings each including the first coating and the primary coating; and the second plurality of second couplings each including the primary coating and the second coating. In another aspect, the primary coatings, first coatings, and/or second coatings can include a polymer and each of the first couplings and second couplings can be a compatible adhesive. In another aspect, the primary coatings, first coatings, and second coatings can include the same polymer and form the first and second couplings as sleeves. In another aspect, the primary coatings, first coatings, and second coatings can include a metal or a metallic coating. In yet another aspect the metal or metallic coatings can include a radiopaque metal such as gold, tantalum, platinum, rhenium, palladium, or another radiopaque metal or combination of metals.
In one embodiment, the present invention includes a method of manufacturing a segmented endoprosthesis. Such a method can include the following: providing a first annular element as described herein; providing a second annular element as described herein; adjacently disposing said plurality of first integrating members with said plurality of second integrating members; and coupling the first annular element with the second annular element by forming a plurality of couplings between the plurality of first integrating members of the first annular element with the plurality of second integrating members of the second annular element so as to form the segmented endoprosthesis.
In one aspect, the method can include at least one of the following: brazing the first integrating members to the second integrating members in order to form the plurality of couplings; metallurgically bonding the first integrating members to the second integrating members in order to form the plurality of couplings; welding the first integrating members to the second integrating members in order to form a weld; mechanically bonding (e.g., swaging and/or crimping) the first integrating members to the second integrating members in order to form the plurality of couplings; adhering the first integrating members to the second integrating members with an adhesive; preparing the first annular element by a process different from preparing the second annular element; finishing the first annular element by a first process and separately finishing the second annular element by a second process prior to coupling the first annular element with the second annular element; coating the entire endoprosthesis with a substantially uniform coating; loading the endoprosthesis with a substantially uniform drug distribution. In another aspect, the method can include the following: coating the first integrating members a first coating; coating the second integrating members with a second coating; and attaching the first coatings and the second coatings so as to form the plurality of couplings. In another aspect, the first coatings and second coatings can include a polymer and each coupling can be an adhesive. In another aspect, the first coatings and second coatings can include the same polymer and form the couplings as sleeves. In another aspect, the first coatings and second coatings can include a metal or a metallic coating. In yet another aspect the metal or metallic coatings can include a radiopaque metal such as gold, tantalum, platinum, rhenium, palladium, or another radiopaque metal or combination of metals.
In one embodiment, the present invention includes a method of manufacturing another embodiment of a segmented endoprosthesis. Such a method can include the following: providing a primary annular element as described herein; providing a first end annular element as described herein; providing a second end annular element as described herein; coupling the primary annular element with the first end annular element by forming a first plurality of first couplings disposed between and coupling a plurality of primary integrating members of the primary annular element on a first longitudinal side with a plurality of first integrating members of a first end annular element; and coupling the primary annular element with the second end annular element by forming a second plurality of second couplings disposed between and coupling a plurality of primary integrating members of the primary annular element on a second longitudinal side with a plurality of second integrating members of a second end annular element such that the primary annular element is formed into a segmented endoprosthesis with the first end annular element and second end annular element.
In one aspect, the method can include at least one of the following: brazing the primary integrating members to at least one of the first integrating members or the second integrating members in order to form at least the first plurality of first couplings or the second plurality of second couplings; metallurgically bonding the primary integrating members to at least one of the first integrating members or the second integrating members in order to form at least the first plurality of first couplings or the second plurality of second couplings; welding the primary integrating members to at least one of the first integrating members or the second integrating members in order to form at least the first plurality of first couplings or the second plurality of second couplings as welds; mechanically bonding (e.g., swaging and/or crimping) the primary integrating members to at least one of the first integrating members or the second integrating members in order to form at least the first plurality of first couplings or the second plurality of second couplings; adhering the primary integrating members to at least one of the first integrating members or the second integrating members with an adhesive in order to form at least the first plurality of first couplings or the second plurality of second couplings; preparing the primary annular element by a process different from preparing at least one of the first annular end element or the second annular end element; finishing the primary annular element by a first process and separately finishing at least one of the first annular end element the second annular end element by a second process prior to coupling the primary annular element to at least one of the first annular end element or the second annular end element; coating the entire endoprosthesis with a substantially uniform coating; or loading the endoprosthesis with a substantially uniform drug distribution. In another aspect, the method can include the following: coating the primary integrating members with a primary coating; coating the first integrating members with a first coating; coating the second integrating members with a second coating; and attaching the primary coating to both the first coatings and the second coatings so as to form the first plurality of first couplings and second plurality of second couplings. In another aspect, the first coatings and second coatings can include a polymer and each coupling can be an adhesive. In another aspect, the first coatings and second coatings can include the same polymer and form the couplings as sleeves. In another aspect, the first coatings and second coatings can include a metal or a metallic coating. In yet another aspect the metal or metallic coatings can include a radiopaque metal such as gold, tantalum, platinum, rhenium, palladium, or another radiopaque metal or combination of metals.
In one embodiment, the present invention includes a method for manufacturing a custom segmented endoprosthesis. The method includes steps of (1) designing a custom segmented endoprosthesis based on at least one medical condition and/or at least one anatomical characteristic of the site of placement, wherein the designing includes steps of (a) selecting design criteria from the group consisting of material composition, length, diameter, wall thickness, flexibility, shape, structure, drug loading, drug type, shape memory, austenite finish temperature, radial force, or strut elements, and combinations thereof, and (b) selecting a plurality of segments based on the selected design criteria for assembly into the custom segmented endoprosthesis, the segments including annular elements having a plurality of first integrating members on a first longitudinal end and a plurality of second integrating members on a second longitudinal end, (2) adjacently disposing the plurality of first integrating members with the plurality of second integrating members; and (3) coupling the plurality of annular elements by bonding the plurality of first integrating members to the plurality of second integrating members so as to form the custom segmented endoprosthesis.
Examples of suitable medical conditions upon which the design criteria may be selected include, but are not limited to, coronary angioplasty, arterial stenosis, venous stenosis, arterial aneurysm, venous aneurysm, coronary artery disease, peripheral artery disease, peripheral venous disease, chronic limb ischemia, blockage or occlusion of the bile duct, esophageal disease or blockage, defects or disease of the colon, tracheal disease or defect, blockage of the large bronchi, blockage or occlusion of the ureter, or blockage or occlusion of the urethra. Suitable examples of anatomical characteristics of the site of placement include, but are not limited to, a tortuous luminal pathway, longitudinal movement at the site, bending, torsional movement, and tensional and radial cyclical loading.
In one aspect, the first and second integrating members include at least one of the following blunt joinery elements, overlay joinery elements, complementary male and female joinery elements, or complementary finger joinery elements. In another aspect, the bonding includes least one of a brazing, metallurgical bonding, welding, sleeve, mechanical bonding (e.g., swaging and/or crimping) or an adhesive, and combinations thereof. In one aspect, bonding between adjacent joinery elements having a variety of bonding means can be formed by applying localized heat to abutting joinery elements (e.g., indirectly via laser or hot air or directly via contacting heating elements). Such heating can be used, for example, to promote softening, melt flow, and/or cross-linking of polymers and/or metal coatings.
These and other embodiments and features of the present invention will become more fully apparent from the following description, drawings, and/or appended claims, or may be learned by the practice of the invention as set forth hereinafter.
To further clarify the above and other advantages and features of the present invention, a more particular description of the invention will be rendered by reference to specific embodiments thereof which are illustrated in the appended drawings. It is appreciated that these drawings depict only typical embodiments of the invention and are therefore not to be considered limiting of its scope. The invention will be described and explained with additional specificity and detail through the use of the accompanying drawings, in which:
The present invention includes various embodiments of endoprostheses for delivery into a lumen of a body. The endoprostheses can be configured to have improved functionality by being segmented so that adjacent annular elements may have different configurations. As such, the segmented endoprosthesis can have improved functionality and even be multifunctional depending on the configuration of the different annular elements. For example, the different annular elements can be configured to improve delivery and placement of the segmented endoprosthesis within a tortuous luminal pathway.
The use of a segmented endoprosthesis that is sectioned into multiple annular elements or multiple sub-endoprosthesis can enable delivery around tight corners. For example, one annular element or sub-endoprosthesis can be pushed through a tight corner in such a manner that a flexible interconnection allows each annular element or sub-endoprosthesis to move independently. Alternatively, selected annular elements of the segmented endoprosthesis can be more or less flexible so also enhance deployment through tight corners in a body lumen.
In another example, a detachable interconnection can allow the adjacent annular elements to separate from each other in order to avoid generating undue stress at a corner, and then rejoin at a straight section. In still another example, the interconnection can be prepared in such a manner that the different annular elements or sub-endoprosthesis are selectively held together by contact. As such, the interconnection is not unduly stressed and is less susceptible to cracking. Thus, the segmented endoprostheses having multiple annular elements or sub-endoprosthesis can increase the ability for easy deployment and retain substantial structural integrity of the endoprosthesis after deployment.
In another example, fabricating endoprostheses using a plurality of annular rings is more efficient and cost effective. The current trend in medicine is to use longer and longer endoprostheses for applications such as treating chronic limb ischemia below the knee. Typically, endoprostheses of all lengths have been fabricated as unitary structures using techniques such as laser cutting to cut an endoprosthesis out of a single piece of material. Nevertheless, as manufacturers have attempted to fabricate longer endoprostheses using typical methods the scrap rate or the rate at which endoprostheses have to be disposed of because manufacturing defects or mistakes has increased disproportionately. This is undesirable because of the high cost of the alloys typically used to fabricate endoprostheses and because of the cost associated with manufacturing and testing endoprostheses.
In contrast, segmented endoprostheses fabricated from multiple annular elements have a markedly lower scrap rate. That is, when a defect is detected in a singe ring only that ring has to be disposed of as opposed to disposing of the whole endoprosthesis. Moreover, multiple annular elements can be used to efficiently and cost effectively manufacture endoprostheses having almost any length that is practically necessary for treating a patients in need endoprosthetic treatment.
In another example, a custom endoprosthesis designed for a particular medical condition or an anatomical placement can be designed and fabricated using a plurality of annular rings. For example, endoprostheses can be designed having regions with different flexibility. This can be useful for installing an endoprosthesis in a body lumen with particularly tortuous anatomy. Endoprostheses can also be designed and fabricated where different regions that expand to different diameters. This can be useful for endoprosthetic treatment in a region where the body lumen has an inconsistent diameter.
In accordance with the present invention, a segmented endoprosthesis can be provided for improved delivery within a body lumen of a human or other animal. Examples of segmented endoprostheses can include stents, filters, grafts, valves, occlusive devices, trocars, aneurysm treatment devices, or the like. Additionally, a segmented endoprosthesis can be configured for a variety of intralumenal applications, including vascular, coronary, biliary, esophageal, urological, gastrointestinal, or the like. The segmented endoprostheses can be prepared from multiple annular elements or sub-endoprosthesis that are interconnected by interconnectors that are flexible, degradable, bumpers, decouplable, detachable, brazings, metallurgical bonds, mechanical bonds, welds, sleeves, adhesives, or the like. As such, the interconnectors can inhibit stresses or strains from being transmitted between adjacent annular elements or sub-endoprosthesis. Also, the interconnectors inhibit excessive or destructive stresses or strains from being generated at the junctions between the adjacent annular elements or sub-endoprosthesis. Additionally, the interconnectors can be couplings that interconnect different types of annular elements together to form the endoprosthesis. Thus, adjacent annular elements or sub-endoprosthesis can be separated by interconnectors or couplings that inhibit crack formation and failure of the endoprosthesis, and also allow for different types of annular elements or sub-endoprostheses to be joined into a segmented endoprosthesis.
Generally, an endoprosthesis of the present invention can include at least a first set of interconnected strut elements that cooperatively define an annular element or sub-endoprosthesis. A strut element can be more generally described as an endoprosthetic element, wherein all well-known endoprosthetic elements can be referred to here as a “strut element” for simplicity. Usually, each strut element can be defined by a cross-sectional profile as having a width and a thickness, and including a first end and a second end bounding a length. The stent element can be substantially linear, arced, rounded, squared, combinations thereof, or other configurations. The strut element can include a bumper, crossbar, connector, interconnector, intersection, elbow, foot, ankle, toe, heel, medial segment, lateral segment, coupling, sleeve, combinations thereof, or the like, as described in more detail below. The strut element can have improved structural integrity by including crack-inhibiting features, which are described in detail in the incorporated references.
Usually, the annular elements or sub-endoprosthesis can include a plurality of circumferentially-adjacent crossbars that are interconnected end-to-end by an elbow connection, intersection, or a foot extension. As such, at least one annular element or sub-endoprosthesis can include an elbow, intersection, or a foot extension (“foot”) extending between at least one pair of circumferentially-adjacent crossbars. The elbow or foot can thus define an apex between the pair of circumferentially-adjacent crossbars of the annular element or sub-endoprosthesis. Also, an intersection can have a shape similar to a crossbar or interlinked crossbars so as to provide a junction between two coupled pairs of circumferentially-adjacent crossbars.
The elbow can be configured in any shape that connects adjacent ends of circumferentially-adjacent crossbars, and can be described as having a U-shape, V-shape, L-shape, X-shape, Y-shape, H-shape, K-shape, or the like. The elbow and/or intersection can be configured in any shape that connects longitudinal and circumferentially adjacent crossbars, and can be described as having a cross shape, X-shape, Y-shape, H-shape, K-shape, or the like. The foot can have a foot shape having a first foot portion extending circumferentially from an end of one of the adjacent strut members and a second foot portion extending circumferentially from a corresponding end of the other of the circumferentially-adjacent strut members. In combination, the first and second foot portions generally define an ankle portion connected to a toe portion through a medial segment and the toe portion connected to a heel portion through a lateral segment.
As described herein, an endoprosthesis, in one configuration, can include two or more interconnected annular elements or sub-endoprosthesis. Each annular element or sub-endoprosthesis can generally define a ring-like structure extending circumferentially about a longitudinal or central axis. The cross-sectional profile of each annular element or sub-endoprosthesis can be at least arcuate, circular, helical, or spiral, although alternative cross-sectional profiles, such as oval, oblong, rectilinear or the like, can be used. The different annular elements can be defined as having the same characterization or different characterizations.
When the endoprosthesis can include multiple spaced apart annular elements or sub-endoprostheses, a first annular element can be aligned longitudinally adjacent to a second annular element along the longitudinal axis. The first and second annular elements can be interconnected by flexible, degradable, bumper, decouplable, detachable, brazings, metallurgical bonds, mechanical bonds, welds, sleeves, adhesives, and like interconnectors. The interconnectors can be considered as strut elements for the purposes of the invention. For example, the interconnectors can be strut elements that interconnect adjacent annular elements or sub-endoprostheses so as to improve the structural integrity of the endoprosthesis by inhibiting the buildup of stresses or strains at the interconnection or inhibiting propagation of stresses or strains between adjacent annular elements or sub-endoprostheses. In another example, the interconnectors allow for different types of adjacent annular elements or sub-endoprostheses to be interconnected into an endoprosthesis.
The first and second annular elements or sub-endoprostheses generally define a tubular structure. For example, each annular element or sub-endoprosthesis can define a continuous closed ring such that the longitudinally-aligned annular elements or sub-endoprostheses form a closed tubular structure having a central longitudinal axis. Alternatively, each annular element or sub-endoprosthesis can define an open ring shape such that a rolled sheet, open tubular, or “C-shape” type structure is defined by the annular elements. That is, the annular element or sub-endoprosthesis is not required to be closed. Furthermore, each annular element or sub-endoprosthesis can define substantially a 360-degree turn of a helical pattern or spiral, such that the end of one annular element or sub-endoprosthesis can be joined with the corresponding end of a longitudinally-adjacent annular element or sub-endoprosthesis to define a continuous helical pattern along the length of the endoprosthesis.
One configuration of the present invention can include an endoprosthesis configured to flex during deployment and after being set.
For purposes of clarity and not limitation, the endoprosthesis 1a is illustrated in a planar format. As shown, the endoprosthesis 1a can include a plurality of annular elements 10 aligned longitudinally adjacent to each other along a longitudinal axis 15 extending from a first end 16 to a second end 18. Although only two interconnected annular elements need to be provided for the endoprosthesis, it is possible that an endoprosthesis include one or a plurality of annular elements 10. As depicted in
Each annular element 10 can include a set of interconnected strut elements, shown as strut crossbars 20, which are disposed circumferentially about the longitudinal axis 15; the circumferential direction is represented by arrow 17. Each crossbar 20 can have a first end 22a and a second end 22b, referenced generally as end 22. The first end 22a of selected circumferentially-adjacent crossbars 20a-b can be interconnected at elbows 30 that are proximate to a first longitudinal side 12 of each annular element 10, and the second end 22b of selected circumferentially-adjacent crossbars 20b-c can be interconnected to define elbows 30 that are proximate to a second longitudinal side 14 of the annular element.
Each annular element 10 can be expanded to a deployed configuration as shown in
Selected elbows 30 on each side 12, 14 of the annular element 10 can be defined by interconnecting corresponding ends 22 of circumferentially-adjacent crossbars 20a-b directly together to form a zigzag pattern of alternating U-shapes, V-shapes, L-shapes, combinations thereof, or the like when deployed. Alternatively, an elbow 30 can be provided between the corresponding ends of adjacent crossbars to form another contoured shape, such as by using a straight elbow member to form a flat connection configuration.
For purposes of discussion and not limitation,
The adjacent annular elements 10a-10b or 10c-10d can be interconnected with an interconnector 50 as described herein. For example, the interconnector 50 can have a form of a means for reducing force transmission between adjacent annular elements. Stated another way, the interconnector 50, optionally referred to as a shock absorber or shock absorbing connector, can include one or more shock absorbing members that allow limited movement of adjacent annular elements, while reducing the possibility of cracking and fatigue failure due to the movement of adjacent annular elements. As such, the endoprosthesis 1a can include a plurality of interconnectors 50 to connect adjacent annular elements 10a-10b or 10c-10d. Each interconnector 50 can include a first bending member or shock 52 and a second bending member or shock 54, which can bend toward each other to separate the adjacent annular elements 10a-10b or 10c-10d or bend away from each other to being adjacent annular elements closer together. Accordingly, the interconnector 50 can include a first bending point 60 opposite of a second bending point 64. The first bending member or shock 52 can have at least a first arm 66 and a second arm 67. The second bending member or shock 54 can have at least a first arm 68 and a second arm 69. The interconnector 50 can couple with a first crossbar 20 of a first annular element 10c at a first coupling 62a, and couple with a second crossbar of a second annular element 10d at a second coupling 62b.
The endoprosthesis 1a can be easily deployed because of the improved flexibility provided within each annular element 10 or between adjacent annular elements 10a-10b. As such, the resiliently-flexible bending members or shocks 52, 54 can cooperate so as to enable the endoprosthesis 1a to bend around a tight corner by the bending members or shocks on one side of the annular element contracting while bending members or shocks on an opposite side expanding. Also, the combination of elbows 30, foot extensions 40, and/or resiliently flexible interconnectors 50 can allow for radial, longitudinal, torsional, or bending loading to be absorbed without cracking, fracturing or damage occurring to the endoprosthesis 1a. Moreover, the resiliently-flexible interconnectors 50 can allow adjacent annular elements to move independently with respect to each other in radial, longitudinal, and cross directions.
It will be understood that structure 170 can have other configurations while providing flexibility to the endoprosthesis 100. For instance, structure 170 could be replaced with a repeating “V”, a repeating “U”, or other structures such as those shown in U.S. Pat. No. 6,602,285, issued Aug. 5, 2003, and entitled “COMPACT STENT” and U.S. Pat. No. 7,128,756, issued Oct. 31, 2006, and entitled “ENDOPROSTHESIS HAVING FOOT EXTENSIONS”, the entireties of which are incorporated herein by specific reference.
Turning to
In the illustrated configuration, circumferentially-adjacent crossbars 220 can be coupled at an elbow 230 and four or more circumferentially- and longitudinally-adjacent crossbars can be coupled together at an intersection 240. The intersection 240 and elbows 230 that connect four crossbars 220a-d can cooperate so as to form a structure 270 that allows for flexibility as the structure can expand or collapse. As illustrated, the structure 270 has a diamond shape, but it will be understood that other configurations are possible so long as they provide the desired flexibility to the endoprosthesis. For instance, structure 270 could be replaced with a repeating “V”, repeating “U”, “W”, “Z”, wave, or combination thereof, or other structures such as those shown in U.S. Pat. Nos. 6,602,285 and 7,128,756. Thus, each annular element 210 can be a sub-endoprosthesis that can have a series of circumferentially-interconnected flexible structure 270 that can flex radially or circumferentially.
When the endoprosthesis 200a is in the contracted position, the interconnectors 250 enable the sub-endoprostheses 210a-210b to be coupled together and to flex with respect to each other in longitudinal and cross directions. Also, this allows the collapsed orientation to enable the endoprosthesis 200a to flex and bend without causing any of the sub-endoprostheses 210 to expand or open. In part, this is because the interconnectors 250 allow the sub-endoprostheses 210 to move independently with respect to each other, thus bending forces generated during tracking or delivery in one of the segments will not be transmitted to adjacent segments. Thus, each interconnector 250 can move independently during deployment by the surfaces 260 and/or 262 sliding with respect to each other or separating so that the sub-endoprostheses 210a-210b can move independently around tight corners without incurring undue stress.
Another embodiment of the present invention includes an endoprosthesis configured to flex during deployment and separate into individual sub-endoprostheses after being set.
When the endoprosthesis 310a is in the contracted position, the bumpers 350 enable the sub-endoprostheses 310a-310b to be held together by a delivery catheter (not shown) that substantially surrounds the endoprosthesis 300a and to move with respect to each other in longitudinal and cross directions. The sub-endoprostheses 310a-310b can also be held together by an external sleeve, which can be polymeric so as to be biocompatible and optionally biodegradable. Also, this allows the collapsed orientation to enable the endoprosthesis 300a to flex and bend without causing any of the sub-endoprostheses 310 to expand or open. In part, this is because the bumpers 350 allow the sub-endoprostheses 310 to move independently with respect to each other. Thus, each bumper 350 can move independently during deployment by the bumper surfaces 358 sliding with respect to each other or separating so that the sub-endoprostheses 310a-310e can move independently around tight corners without incurring undue stress.
The use of interconnections in accordance with the present invention allow for improved overall structural integrity of an endoprosthesis. The improved interconnections can allow for adjacent annular elements of an endoprosthesis to be delivered together and to separate into distinct sub-endoprostheses during expansion into a deployed orientation. As such, the interconnections can inhibit the endoprosthesis from cracking at high stress areas through reducing the stress upon the high stress areas, thereby improving the performance and reliability of the endoprosthesis. The interconnections can be configured as decouplable interconnectors and/or bumpers, as described above.
The decouplable interconnectors described in
Additionally, the interconnectors illustrated in 5A-5D can be coupled together as described herein. This can include the interconnectors being coupled together by a brazing, metallurgical bond, weld, sleeve, polymer coating, mechanical bond (e.g., swaging and/or crimping), or an adhesive. The couplings may be placed at the points of contact between the adjacent interconnectors. In one aspect, bonding between adjacent joinery elements having a variety of bonding means can be formed by applying heat to abutting joinery elements (e.g., indirectly via laser or hot air or directly via contacting heating elements). Such heating can be used, for example, to promote softening, melt flow, and/or cross-linking of polymers and/or metal coatings. Also, a sleeve, such as a polymeric sleeve, or coating can be applied over the adjacent interconnectors so as to form a sleeve coupling.
The bumpers described in
Additionally, the bumpers illustrated in 6A-6D can be coupled together as described herein. This can include the bumpers being coupled together by a brazing, metallurgical bond, weld, sleeve, polymer coating, mechanical bond (e.g., swaging and/or crimping), or an adhesive. The couplings may be placed at the points of contact between the adjacent bumpers. In one aspect, bonding between adjacent joinery elements having a variety of bonding means can be formed by applying heat to abutting joinery elements (e.g., indirectly via laser or hot air or directly via contacting heating elements). Such heating can be used, for example, to promote softening, melt flow, and/or cross-linking of polymers and/or metal coatings. Also, a sleeve, such as a polymeric sleeve, or coating can be applied over the adjacent bumpers so as to form a sleeve coupling.
Additionally, an endoprosthesis in accordance with the present invention can be configured to have column stiffness during delivery and flexibility after being expanded or deployed. The stiffness can be achieved with compressible interconnectors that allow adjacent annular elements to collapse against each other. Optionally, an overlapping region can allow circumferentially-adjacent compressible interconnectors to overlap while in the delivery orientation so as to create a physical barrier between adjacent annular elements. Also, the overlapping region can release when the endoprosthesis expands so as to create space for the adjacent annular elements to flex or move longitudinally with respect to each other.
A compressible endoprosthesis can have interconnectors that compress or lengthen when bent, stretched, or shortened. The compressible interconnectors can absorb longitudinal or bending stresses to allow the rings to maintain uniformity, which improves their resistance to cracking or failure that may occur due to various loading conditions arising from stresses that occur during longitudinal, bending, and radial cyclical loading. Optionally, the compressible interconnectors can have a member that overlaps another member of a circumferentially adjacent compressible interconnector so as to create a rigid section between adjacent annular elements. The compressible interconnectors featuring the overlapping portions can be included in the described endoprostheses as well as other configurations well known in the art. For example, compressible interconnector can include a compressible arm having a V-shape that has one side connected to one annular element, and a second side that is connected to a second annular element through an extension arm. Additionally, each of the arms of the V-shape and extension arm can be long to increase flexibility. Moreover, the point of the V-shape can be cradled within the opening of an adjacent interconnector so as to form the overlapping configuration.
One configuration of the present invention can include an endoprosthesis configured to be compressed during deployment and be compressible after being expanded and set.
It will be understood that structure 612 can have other configurations while providing flexibility to the endoprosthesis 600. For instance, structure 612 could be replaced with a repeating “V”, “U”, “W”, “Z”, wave, or combination thereof, or other structures such as those shown in U.S. Pat. Nos. 6,602,285 and 7,128,756. Additionally,
Generally, the compression interconnectors 650 can have a V-shape configuration having at least one flexing point 660 and at least two flexible couplings 656, 658, although other configurations of the compression interconnectors 650 can also achieve the desired functionality. The two couplings 656, 658 can couple a collapsing member or shock 652 between adjacent annular elements 610a-610b. The collapsing member or shock 652 can have a first arm 667 coupled to a second arm 668 through the flexing point 660. The flexing point 660 can cooperate with the two couplings 656, 658 to allow the first annular element 610a to flex and/or move with respect to the second annular element 610b. Moreover, the compression interconnectors 650 can cooperate with the annular elements 610 so that the endoprosthesis 100 can bend and flex in any direction. For example, the compression interconnectors 650 can be shaped as diamond-shape, V-shape, U-shape, W-shape, O-shape, N-shape, M-Shape, Z-shape, and the like.
Additionally,
It will be understood that structure 712 can have other configurations while providing flexibility to the endoprosthesis 700. For instance, structure 712 can have a configuration similar to those described herein and in U.S. Pat. Nos. 6,602,285 and 7,128,756.
Additionally,
Generally, the compression interconnectors 750 can have substantially a Z-shape configuration having at least one flexing point 760 and at least two flexible couplings 756, 758 for a first collapsing arm 752a, and at least one flexing point 759 and at least two flexible couplings 764, 765 for a second collapsing arm 752b. Preferably, the first collapsing arm 752a is oriented oppositely from the second collapsing arm 752b so that the flexing points 760, 759 point away from each other. However, other configurations of the compression interconnectors 750 can also achieve the desired functionality. The first collapsing arm 752a can be comprised of a first arm 767 and a second arm 768 that are coupled together through a flexing point 760. The first arm 767 can be coupled to the extension arm 740 through a first coupling 756, and the second arm 768 can be coupled to the second collapsing arm 752b through a second coupling 758. The second collapsing arm 752b can be comprised of a first arm 766 and a second arm 769 that are coupled together through a flexing point 759. The first arm 766 of the second collapsing arm 752b can be coupled to the first collapsing arm 752a through a first coupling 764, and the second arm 769 of the second collapsing arm 752b can be coupled to the elbow 730 of an adjacent annular element 710. More particularly, the second coupling 758 of the first collapsing arm 752a and the first coupling 764 of the second collapsing arm 752b can be coupled together through a flexible transition coupling 762.
Additionally,
The present invention additionally includes hybrid segmented endoprostheses that include at least two annular elements that have different configurations. The two annular elements are coupled together through a coupling so that the segmented endoprosthesis includes the functionality associated with the configuration of the first annular element as well as the functionality associated with the second annular element. Any number of different types of annular elements with unique configurations can be coupled together in order to prepare the hybrid endoprosthesis. For example, a first type of annular element may be more structurally rigid, and the second type can be more flexible so as to allow for flexion during delivery around tight junctions. The couplings can be any of the interconnectors described herein as well as bumpers or the like that are joined together.
The primary annular element 1004 is show to have primary integrating members 1012 at each end. The first end annular element 1002 and second end annular element 1006 are shown to each have integrating members 1010 on an end adjacent to the primary integrating members 1012. The primary integrating members 1010 are shown to be coupled to the integrating members 1012 via couplings 1014.
The first annular element 1102 is shown to have first integrating members 1110 at the end to be coupled to the second annular element 1104. The second annular element 1104 is shown to have second integrating members 1112 on an end adjacent to the first integrating members 1110. The first integrating members 1110 are shown to be coupled to the second integrating members 1112 via couplings 1114.
The first primary annular element 1204 is show to have first integrating members 1212 at each end. The second primary annular element 1202 and third primary annular element 1206 are shown to each have integrating members 1210 on an end adjacent to the first integrating members 1012. The first integrating members 1212 are shown to be coupled to the integrating members 1210 of the second primary annular element 1202 and third primary annular element 1206 via couplings 1214.
The endoprosthesis 1300 is formed by joining a plurality of annular elements 1302. In the example depicted in
The annular elements 1302 are shown to have a plurality of first integrating members 1310 and a plurality of second integrating members 1312. In the depicted embodiment, the endoprosthesis 1300 is formed by overlaying the second integrating members 1312 over the first integrating members 1310 and welding or bonding the first and second integrating members 1310 and 1312 together to form the plurality of couplings 1314.
With respect to
Couplings 1314-1314c, 1316-1316c, and 1318-1318b may be advantageously employed to assemble a modular endoprosthesis. For example, coupling 1316a described in
In one configuration, the hybrid segmented endoprosthesis can include an interconnector that couples first annular element having a first configuration to the second annular element having a second configuration that is different from the first configuration. The interconnector can reduce stress and forces propagating between adjacent positions of the endoprosthesis. The interconnector can flex so that the different annular elements can move relative to one another and facilitate delivery to and placement within a body lumen. Further, the interconnector can enable the endoprosthesis to flex during movement of the body lumen following deployment.
In another configuration, the hybrid segmented endoprosthesis can include a first annular element having a first configuration flexibly-resiliently coupled to a second annular element having a second configuration by first and second flexibly-resilient interconnectors. The first annular element can have a first end that includes both a first strut element and a second strut element, while the second annular element can have a second end that is adjacent to the first end of the first annular element. Adjacent to the third strut element can be the first stent element and the second strut element can be adjacent to the fourth strut element. The first flexibly-resilient interconnector can be coupled to the first strut element and the third strut element, and the second flexibly-resilient interconnector can be coupled to the second strut element and the fourth strut element. Additionally, the first and second interconnectors can be positioned on the endoprosthesis so that when the endoprosthesis bends in a first direction the first interconnector collapses and the second interconnector expands, or vice versa.
In another configuration, a flexible, segmented endoprosthesis can include a first annular element adjacent to a different type of second annular element. A plurality of shock absorbing members or structures each having a first end and a second end can be disposed between the first and second annular elements. The first end can be coupled to the first annular element and the second end can be coupled to the second annular element.
In another configuration, a decouplable segmented endoprosthesis can include a first annular element with a first configuration and having a plurality of first decouplable interconnectors at a first end and a second annular element with a second configuration having a plurality of second decouplable interconnectors at a second end. At least one of the plurality of second decouplable interconnectors can be releasably coupled with at least one of the plurality of first decouplable interconnectors when the segmented endoprosthesis is in a delivery orientation. Additionally, when in the delivery configuration the decouplable interconnectors can be configured to transmit axial loads while preventing one segment to move independent of another.
In another configuration, a decouplable segmented endoprosthesis can include a plurality of sub-endoprostheses having different configurations being releasably coupled together when the segmented endoprosthesis is in a delivery orientation. Each of the plurality of sub-endoprostheses can decouple from adjacent sub-endoprostheses when the endoprosthesis is expanded into a deployed orientation. Accordingly, the endoprosthesis can include a first sub-endoprosthesis that can include at least a first decouplable interconnector and a second sub-endoprosthesis that can include at least a second decouplable interconnector that interlocks with the at least a first decouplable interconnector when the endoprosthesis is in the delivery orientation.
In another configuration, a segmented endoprosthesis can include a series of longitudinally-adjacent sub-endoprostheses that have different configurations. As such, the segmented sub-endoprosthesis can include a first annular element with a first configuration that can have a plurality of first bumpers at a first end and a second annular element with a second configuration that can have a plurality of second bumpers at a second end. At least one of the plurality of second bumpers can abut with at least one of the plurality of first bumpers when the segmented endoprosthesis is in a delivery orientation.
In another configuration, a series of substantially different sub-endoprostheses can each have bumpers that separate each other and form a segmented endoprosthesis. Each sub-endoprosthesis can be in contact with longitudinally-adjacent sub-endoprostheses when the segmented endoprosthesis is in a delivery orientation. Also, each of the plurality of sub-endoprostheses can separate from the longitudinally-adjacent sub-endoprostheses when the endoprosthesis is expanded into a deployed orientation. The segmented endoprosthesis can include a first sub-endoprosthesis that can include at least a first bumper, and a second sub-endoprosthesis that can include at least a second bumper that abuts and contacts the first bumper when the endoprosthesis is in the delivery orientation.
The hybrid segmented endoprostheses of the present invention can be made of a variety of materials, such as, but not limited to, those materials which are well known in the art of endoprosthesis manufacturing. This can include, but not limited to, an endoprosthesis having a primary material for at least one of the annular elements and/or interconnectors. Alternatively, at least two of the annular elements and/or interconnectors can be made of different materials. Generally, the materials for the endoprosthesis can be selected according to the structural performance and biological configurations that are desired.
In one configuration, the interconnectors and/or the annular elements have multiple layers, with at least one layer being applied to a primary material forming the annular elements. As such, at least one annular element can have multiple layers that are different from at least one other annular element. The multiple layers on the interconnectors and/or the annular elements can be resiliently flexible materials or rigid and inflexible materials. For example, materials such as Ti3Al2.5V (also referred to as 3-2.5Ti), Ti6Al4V (also referred to as 6-4Ti), Ti6Al7Nb, Ti6AlV, and platinum may be particularly good choices for adhering to a flexible material, such as, but not limited to, Nitinol and providing good crack arresting properties. The use of resiliently flexible materials can provide shock-absorbing characteristics to the structures, decouplable interconnectors, and/or bumpers, which can also be beneficial for absorbing stress and strains, which may inhibit crack formation at high stress zones. Also, the multiple layers can be useful for applying radiopaque materials to selected annular elements, such as end annular elements to provide different configurations. For example, types of materials that are used to make an endoprosthesis can be selected so that the endoprosthesis is capable of being collapsed during placement and expanded when deployed. Usually, the endoprosthesis can be self-expanding, balloon-expandable, or can use some other well-known configuration for deployment. For purposes of illustration and not limitation, reference is made generally to self-expanding embodiments and balloon-expandable embodiments of the endoprosthesis of the present invention; however, other types of endoprostheses can be configured in accordance with the present invention.
Embodiments of the annular elements or sub-endoprostheses can include a material made from any of a variety of known suitable materials, such as a shaped memory material (“SMM”). For example, the SMM can be shaped in a manner that allows for restriction to induce a substantially tubular, linear orientation while within a delivery shaft, but can automatically retain the memory shape of the endoprosthesis once extended from the delivery shaft. SMMs have a shape memory effect in which they can be made to remember a particular shape. Once a shape has been remembered, the SMM may be bent out of shape or deformed and then returned to its original shape by unloading from strain or heating. Typically, SMMs can be shape memory alloys (“SMA”) comprised of metal alloys, or shape memory plastics (“SMP”) comprised of polymers. The materials can also be referred to as being superelastic.
Usually, an SMA can have any non-characteristic initial shape that can then be configured into a memory shape by heating the SMA and conforming the SMA into the desired memory shape. After the SMA is cooled, the desired memory shape can be retained. This allows for the SMA to be bent, straightened, compacted, and placed into various contortions by the application of requisite forces; however, after the forces are released, the SMA can be capable of returning to the memory shape. The main types of SMAs are as follows: copper-zinc-aluminium; copper-aluminium-nickel; and nickel-titanium (“NiTi”) alloys known as nitinol. Cobalt-chromium-nickel alloys and cobalt-chromium-nickel-molybdenum alloys (known as elgiloy alloys) are similar to SMAs in that they have a high modulus of elasticity and they can be used in many similar applications. However, unlike SMAs, cobalt-chromium-nickel alloys and cobalt-chromium-nickel-molybdenum can be permanently deformed without the application of heat by exceeding the modulus of elasticity. The temperatures at which SMAs and similar alloys change their crystallographic structure are characteristic of the alloy, and can be tuned by varying the elemental ratios or by the conditions of manufacture.
Shape memory materials are characterized by their austenite and martensite states. The transformation between austenite and martensite is reversible but the temperature at which it occurs is different whether the shape memory alloy is being cooled or heated. This difference is referred to as the hysteresis cycle. This cycle is characterized by four different temperatures: As (Austenite Start), Af (Austenite Finish), Ms (Martensite Start), and Mf (Martensite Finish). A martensitic shape memory alloy will begin to transform to austenite when its temperature reaches As and will be fully austenitic when the temperature reaches Af. Upon cooling from a high temperature, martensite will start to appear when the temperature reaches Ms and the transformation will be complete when the temperature drops below Mf. A number of parameters including alloy composition and thermo-mechanical history can affect the transformation temperatures and can be adjusted for specific applications.
Shape memory materials possess unique characteristics that are particularly useful in endoprosthetic applications. If a piece of a shape memory alloy, such as nitinol, is mechanically stretched, compressed, bent, or twisted in its martensitic phase, it will return to its original configuration upon heating. Typically, the shape of the shape memory alloy is set to by deforming an austenitic material at high temperature, cooling the material to a martensitic state. When the material is again heated above the Af temperature, the material will return to the shape it had when it was deformed in the austenitic state.
In one embodiment, at least one annular ring used to fabricate a segmented endoprosthesis is heat set to its final diameter and selectively configured to have a particular Af temperature. Preferably, the Af temperature is a temperature in a range from about 5° C. to about 45° C., more preferably, the Af temperature is a temperature in a range from about 20° C. to about 40° C., most preferably, the Af temperature is a temperature in a range from about 25° C. to about 35° C. An endoprosthesis fabricated from a plurality of annular rings where at least one ring is characterized by having an austenitic finish temperature from about 5° C. to about 45° C. would be capable of self-expanding to a particular diameter when in installed in a body lumen. Additional discussion of the use of austenitic and martensitic shape memory materials can be found in U.S. patent application Ser. No. 11/748,214, filed May 14, 2007, entitled “FATIGUE RESISTANT ENDOPROSTHESES” to Shrivastava et al., the entirety of which is incorporated herein by reference.
For example, the primary material of an endoprosthesis can be of a NiTi alloy that forms superelastic nitinol. In the present case, nitinol materials can be trained to remember a certain shape, straightened in a shaft, catheter, or other tube, and then released from the catheter or tube to return to its trained shape. Also, additional materials can be added to the nitinol depending on the desired configuration.
An SMP is a shape-shifting plastic that can be fashioned into an endoprosthesis in accordance with the present invention. Also, it can be beneficial to include at least one layer of an SMA and at least one layer of an SMP to form a multilayered body; however, any appropriate combination of materials can be used to form a multilayered endoprosthesis. When an SMP encounters a temperature above the lowest melting point of the individual polymers, the blend makes a transition to a rubbery state. The elastic modulus can change more than two orders of magnitude across the transition temperature (“Ttr”). As such, an SMP can formed into a desired shape of an endoprosthesis by heating it above the Ttr, fixing the SMP into the new shape, and cooling the material below Ttr. The SMP can then be arranged into a temporary shape by force, and then resume the memory shape once the force has been applied. Examples of SMPs include, but are not limited to, biodegradable polymers, such as oligo(ε-caprolactone)diol, oligo(ρ-dioxanone)diol, and non-biodegradable polymers such as, polynorborene, polyisoprene, styrene butadiene, polyurethane-based materials, vinyl acetate-polyester-based compounds, and others yet to be determined. As such, any SMP can be used in accordance with the present invention.
An annular element or sub-endoprosthesis having at least one layer made of an SMM or suitable superelastic material and other suitable layers can be compressed or restrained in its delivery configuration within a delivery device using a sheath or similar restraint, and then deployed to its desired configuration at a deployment site by removal of the restraint as is known in the art. An annular element or sub-endoprosthesis made of a thermally-sensitive material can be deployed by exposure of the endoprosthesis to a sufficient temperature to facilitate expansion as is known in the art.
Also, annular elements or sub-endoprostheses can be comprised of a variety of known suitable deformable materials, including stainless steel, silver, platinum, tantalum, palladium, cobalt-chromium alloys or other known biocompatible materials. Such materials can include a suitable biocompatible polymer in addition to or in place of a suitable metal. The polymeric endoprosthesis can include biodegradable or bioabsorbable materials, which can be either plastically deformable or capable of being set in the deployed configuration. If plastically deformable, the material can be selected to allow the endoprosthesis to be expanded in a similar manner using an expandable member so as to have sufficient radial strength and scaffolding and also to minimize recoil once expanded. If the polymer is to be set in the deployed configuration, the expandable member can be provided with a heat source or infusion ports to provide the required catalyst to set or cure the polymer.
For example, one layer can be a coating that is applied over the entire hybrid segmented endoprosthesis, or to select portions. The select portions can include the layer of polymer being applied over the integrating members of adjacent annular elements in order to form a coupling in the form of a sleeve.
Examples of such biocompatible materials can include a suitable hydrogel, hydrophilic polymer, biodegradable polymers, bioabsorbable polymers. Examples of such polymers can include nylons, poly(alpha-hydroxy esters), polylactic acids, polylactides, poly-L-lactide, poly-DL-lactide, poly-L-lactide-co-DL-lactide, polyglycolic acids, polyglycolide, polylactic-co-glycolic acids, polyglycolide-co-lactide, polyglycolide-co-DL-lactide, polyglycolide-co-L-lactide, polyanhydrides, polyanhydride-co-imides, polyesters, polyorthoesters, polycaprolactones, polyesters, polyanydrides, polyphosphazenes, polyester amides, polyester urethanes, polycarbonates, polytrimethylene carbonates, polyglycolide-co-trimethylene carbonates, poly(PBA-carbonates), polyfumarates, polypropylene fumarate, poly(p-dioxanone), polyhydroxyalkanoates, polyamino acids, poly-L-tyrosines, poly(beta-hydroxybutyrate), polyhydroxybutyrate-hydroxyvaleric acids, combinations thereof, or the like.
Furthermore, the endoprosthesis can be formed from a ceramic material. In one aspect, the ceramic can be a biocompatible ceramic which optionally can be porous. Examples of suitable ceramic materials include hydroxylapatite, mullite, crystalline oxides, non-crystalline oxides, carbides, nitrides, silicides, borides, phosphides, sulfides, tellurides, selenides, aluminum oxide, silicon oxide, titanium oxide, zirconium oxide, alumina-zirconia, silicon carbide, titanium carbide, titanium boride, aluminum nitride, silicon nitride, ferrites, iron sulfide, and the like. Optionally, the ceramic can be provided as sinterable particles that are sintered into the shape of an endoprosthesis or layer thereof.
Moreover, the endoprosthesis can include a radiopaque material to increase visibility during placement. Optionally, the radiopaque material can be a layer or coating any portion of the endoprosthesis. The radiopaque materials can be platinum, tungsten, silver, stainless steel, gold, tantalum, bismuth, barium sulfate, or a similar material.
It is further contemplated that the external surface and/or internal surface of the endoprosthesis (e.g., exterior and luminal surfaces) can be coated with another material having a composition different from the primary endoprosthetic material. The use of a different material to coat the surfaces can be beneficial for imparting additional properties to the endoprosthesis, such as providing radiopaque characteristics, drug-reservoirs, and improved biocompatibility.
In one configuration, the external and/or internal surfaces of an endoprosthesis can be coated with a biocompatible material. Such coatings can include hydrogels, hydrophilic and/or hydrophobic compounds, and polypeptides, proteins or amino acids or the like. Specific examples can include polyethylene glycols, polyvinylpyrrolidone (“PVP”), polyvinylalcohol (“PVA”), parylene, heparin, phosphorylcholine, or the like. A preferred coating material can include phosphorylcholine, as disclosed in U.S. Pat. No. 6,015,815, issued Jan. 18, 2000, and entitled “TETRAZOL-CONTAINING RAPAMYCIN ANALOGS WITH SHORTENED HALF-LIVES”, the entirety of which is herein incorporated by reference.
The coatings can also be provided on the endoprosthesis to facilitate the loading or delivery of beneficial agents or drugs, such as therapeutic agents, pharmaceuticals and radiation therapies. As such, the endoprosthetic material and/or holes can be filled and/or coated with a biodegradable material.
Accordingly, the biodegradable material can contain a drug or beneficial agent to improve the use of the endoprosthesis. Such drugs or beneficial agents can include antithrombotics, anticoagulants, antiplatelet agents, thrombolytics, antiproliferatives, anti-inflammatories, agents that inhibit hyperplasia, inhibitors of smooth muscle proliferation, antibiotics, growth factor inhibitors, or cell adhesion inhibitors, as well as antineoplastics, antimitotics, antifibrins, antioxidants, agents that promote endothelial cell recovery, antiallergic substances, radiopaque agents, viral vectors having beneficial genes, genes, siRNA, antisense compounds, oligionucleotides, cell permeation enhancers, and combinations thereof. Another example of a suitable beneficial agent is described in U.S. Pat. No. 6,015,815, issued Jan. 18, 2000, and entitled “TETRAZOLE-CONTAINING RAPAMYCIN ANALOGS WITH SHORTENED HALF-LIVES” and U.S. Pat. No. 6,329,386, issued Dec. 11, 2001, and entitled “TETRAZOLE-CONTAINING RAPAMYCIN ANALOGS WITH SHORTENED HALF-LIVES,” the entireties of which are herein incorporated by reference
In one configuration, the external surfaces of an endoprosthesis can include a coating comprised of polytetrafluorethylene (“PTFE”), expanded PTFE (“ePTFE”), Dacron, woven materials, cut filaments, porous membranes, harvested vessels and/or arteries, or others such materials to form a stent graft prosthesis. Similarly, a medical device, such as a valve, a flow regulator or monitor device, can be used with the endoprosthesis, such that the endoprosthesis functions as an anchor for the medical device within the body lumen.
In one configuration, different external surfaces of an endoprosthesis, such as a low stress zone less susceptible to flexing, can be coated with functional layers of an imaging compound or radiopaque material. The radiopaque material can be applied as a layer at low stress zones of the endoprosthesis. Also, the radiopaque material can be encapsulated within a biocompatible or biodegradable polymer and used as a coating. For example, the suitable radiopaque material can be palladium platinum, tungsten, silver, stainless steel, gold, tantalum, bismuth, barium sulfate, or a similar material. The radiopaque material can be applied as layers on selected surfaces of the endoprosthesis using any of a variety of well-known techniques, including cladding, bonding, adhesion, fusion, deposition or the like.
Also, the biodegradable coating can be applied to the interconnectors and/or integrating members of adjacent annular elements so as to form a coupling in the form of a sleeve.
In one configuration, the interconnectors and/or other stent elements of the endoprosthesis can be degradable. For instance, all or a portion of the interconnector (e.g., coupling between different types of annular elements) can be degraded after deployment by being biodegradable or energy-degradable. More generally, one or more portions of the endoprosthesis can be degraded after development by being biodegradable or energy-degradable. The biodegradable portions can be prepared from any of the biodegradable materials described herein as well as others.
A portion of the endoprosthesis, such as, but not limited to, an interconnector, can be energy degradable by responding to light, RF, vibrational, or ultrasonic energy. As such, application of light, RF, vibrational, or ultrasonic energy to the particular portion of endoprosthesis can cause it to break. Alternatively, the portion of the endoprosthesis can include a material that undergoes a physical transition under light, which can have a specific or range of wavelengths, so that it more easily breaks and degrades under RF, vibrational, or ultrasonic energy. The energy can be applied to the energy degradable material after deployment via a catheter, such as the delivery catheter that delivers the endoprosthesis. In any event, any other type of interconnector between annular elements can be fabricated of such an energy degradable material.
For example, a portion of the endoprosthesis, such as an interconnector, can be fabricated of a material that is flexible during deployment and becomes brittle in response to application of a selected wavelength or range of wavelengths of electromagnetic radiation. As such, the energy can be applied to the endoprosthesis after deployment. Ultrasonic energy, such as that used in ultrasounds, can then be used to degrade the degradable portion of the endoprosthesis. This can be beneficial for removing, for instance, the interconnector after deployment, which may help reduce inflammation and provide increased flexibility to the endoprosthesis. Advantageously, this can be used with an endoprosthesis or endoprosthetic system that includes an embolic filter.
C. Matrix with Crack-Inhibiting Features
In addition to the foregoing compositions that can be used in different annular elements or sub-endoprostheses of the hybrid segmented endoprosthesis, a crack-inhibiting feature can be included within the matrix of the different segments of the endoprosthesis. Exemplary crack-inhibiting features can include holes, fibers, particles, and bodies having multiple layers, such as planar layers or concentric layers. As such, any of the foregoing compositions can be impregnated and/or encapsulated with a suitable fibrous or particulate material. Also, an endoprosthesis can be prepared to include a plurality of holes that extend through the endoprosthetic body. Moreover, the endoprosthetic body can have multiple layers separated by junctions or boundaries that inhibit crack propagation. Additional information regarding fibers being dispersed through a matrix of a layer can be found in U.S. patent application Ser. No. 11/375,380, filed Mar. 13, 2006, and entitled “CRACK/FATIGUE RESISTANT ENDOPROSTHESIS”, and additional information on multilayered endoprosthetic bodies can be found in U.S. patent application Ser. No. 11/375,381, filed Mar. 13, 2006, and entitled “MULTILAYERED ENDOPROSTHESIS, each of which are hereby incorporated by reference in its entirety.
For example, different annular elements or sub-endoprostheses of a hybrid segmented endoprosthesis can have different crack-inhibiting features.
Various different manufacturing techniques are well known and may be used for fabrication of the segmented endoprosthesis of the present invention. Such manufacturing techniques can be employed to make the different annular elements or sub-endoprotheses of the hybrid segmented endoprosthesis. For example, the different annular elements or sub-endoprotheses can be formed from a hollow tube using a known technique, such as laser cutting, EDM, milling, chemical etching, hydro-cutting, and the like. Also, the different annular elements or sub-endoprotheses can be prepared to include multiple layers or coatings deposited through a cladding process such as vapor deposition, electroplating, spraying, or similar processes. Also, various other processes can be used such as those described below and or others known to those skilled in the art in light of the teaching contained herein.
Optionally, the different annular elements or sub-endoprotheses can be fabricated from a sheet of suitable material, where the sheet is rolled or bent about a longitudinal axis into the desired tubular shape. Additionally, either before or after being rolled into a tube, the material can be shaped to include endoprosthetic elements by being shaped with well-known techniques such as laser-cutting, milling, etching or the like. If desired, the lateral edges of the structure can be joined together, such as by welding or bonding, to form a closed tubular structure, or the lateral edges can remain unattached to form a coiled, rolled sheet or open tubular structure. Such fabrication techniques are described in more detail below and known to those skilled in the art.
A method of making different annular elements or sub-endoprotheses in accordance with the present invention can include sintering sinterable particles to provide a sintered article having the shape of the endoprosthesis. The sintering can be conducted in molds that are in the shape of an endoprosthesis.
In one configuration, the sintered body can be obtained from a molded green body prepared by molding a mixture of sinterable particles with or without a binder into the shape of different annular elements or sub-endoprotheses or body intermediate. Sintering a molded green body that has the shape of different annular elements or sub-endoprotheses can provide a sintered body that can function as an endoprosthesis with no or minimal further processing. Alternatively, after the green body has been formed in the mold and sintered into a hardened endoprosthesis, the process can include shaping the sintered body with a stream of energy and/or matter in order to obtain a desired shape. Thus, sintering a green body in a mold can result in an endoprosthesis that is either ready for use, or requires additional processing or finishing.
Additionally, the sintered body can be shaped into an endoprosthesis as described herein. Also, the endoprosthesis can be further processed after sintering and/or shaping such as by grinding, sanding, or the like to provide enhanced surface characteristics.
In one configuration, a multilayered annular elements or sub-endoprotheses in accordance with the present invention can be prepared by a drawing process that draws two or more distinct concentric tubes into a single tube having two or more layers. Additionally, such a drawing process can combine multiple concentric tubes into a single multilayered tube. The drawing process can be configured to produce junctions separating adjacent layers or bonds that bond adjacent layers. As such, the sequentially-adjacent concentric tubes can be drawn together and progressively reduced in a cross-sectional profile until the desired size and residual clamping stress is attained.
Accordingly, a metallurgical bond can be prepared with elements of each sequentially-concentric tube diffusing together and bonding so as to form a strong metallurgical bond. Such a metallurgical bond can be achieved by applying significant pressure and heat to the tubes. As such, a metallurgical bond can form a diffusion layer at the interface between sequentially-adjacent concentric tubes (i.e., layers). The characteristics of these diffusion layers can be controlled by the proper heat treatment cycle. In part, this is because the heat treatment, temperature, and time of processing can control the rates of transfer of the diffusing elements that produce the diffusion layers. Also, the pressure at the interface between layers can be developed so as to result in the residual radial clamping stress in the tube after drawing. A similar process can be used in order to couple the adjacent different annular elements or sub-endoprotheses together to form the hybrid segmented endoprosthesis.
In one example of this process, an outer tube of nitinol, a middle tube of tantalum, and an inner tube of Nitinol can be arranged to form the composite structure. The multilayered material can be produced to result in bonding between the layers to achieve a residual clamping stress of at least about 50 p.s.i. Accordingly, the annealing process can be performed within a limited range of time and temperatures. For example, the lower limit can be at least about 1550° F. for at least six minutes, and the upper limit can be less than about 1850° F. for less than 15 minutes. A similar process can be used in order to couple the adjacent different annular elements or sub-endoprotheses together to form the hybrid segmented endoprosthesis.
In another configuration, a metallic interleaf layer can be placed between separate tubes so as to bond the tubes together and form a multilayered material. The multiple tubes separated by the metallic interleaf layer can be drawn together and progressively reduced until the desired cross-sectional profile and residual clamping stress is attained, as described above. The drawn tubes can be heat-treated to form a diffusion bond between the separate layers. As such, the metallic interleaf layer can enhance the diffusion rate or type of diffusing atoms that are transported across a diffusion region between one layer and the interleaf layer. A similar process can be used in order to couple the adjacent different annular elements or sub-endoprotheses together to form the hybrid segmented endoprosthesis.
In one configuration, a multilayered sheet can be prepared to have separate layers of different materials or the same material. For example, the multilayered sheet can have a top layer of nitinol, a middle layer of tantalum, and a bottom layer of Nitinol. The sheet can be prepared by metallurgically bonding the layers prior to a deep drawing process, which is well known in the art. During the deep drawing process, the sheet can be placed over a die and forced into the die, such as by a punch or the like. A tube having a closed end and a defined wall thickness can be formed in the die. This process can be repeated using a series of dies that have progressively decreasing diameters until a multilayered tube is formed having the desired diameter and wall thickness. For certain material combinations, intermediate heat treatments can be performed between the progressive drawing operations to form a multilayered material that is resistant to delaminating. Once a multilayered tube of desired thickness and dimensions has been formed, the closed end and the curved edges can be cut off. Then, the tube can be heat treated, as described above, until proper inter-metallic bonds are formed between the layers.
Accordingly, an endoprosthetic material can be shaped by various methods as described in more detail below. Such shaping techniques can utilize streams of energy and/or streams of matter in order to impart shapes into the endoprosthetic material. The streams of energy include photons, electromagnetic radiation, atomic, and sub-atomic materials, as described above. On the other hand, the streams of matter are considered to include materials larger than atomic scale particles, and can be microscopic or macroscopic in size. In any event, the shaping can be designed to direct a stream of energy or a stream of matter at the endoprosthetic material to form an endoprosthetic element and/or holes therein.
In one configuration, a stream of energy can cut, shape, and/or form a tube into an endoprostheses by generating heat at the site where the stream intersects the material, as is well known in the art. The thermal interaction can elevate the local temperature to a point, which can cut, melt, shape, and/or vaporize portions of the endoprosthetic material from the rest of the material.
Accordingly, one configuration of the stream-cutting apparatus can operate and shape the endoprosthetic material by thermal interactions. As such, any of the thermal processes described herein can be used for thermal-cutting. For example, such thermal interactions can arise from laser beam treatment, laser beam machining, electron beam machining, electrical discharge machining, ion beam machining, and plasma beam machining.
In one configuration, by knowing the thermal properties of the endoprosthetic material, precise energy requirements can be calculated so that the thermal beam provides the appropriate or minimum energy for melting and/or vaporizing the material without significantly melting undesirable portions of the material. For example, laser beams are a common form of a stream of energy that can be used to shape the endoprosthetic material. Additionally, there are instances where a laser is preferred over all other cutting techniques because of the nature of the resulting endoprosthesis as well as the characteristics of the endoprosthetic material.
In one configuration, an endoprosthesis may be manufactured as described herein using a femtosecond laser. A femtosecond laser may be desirable in producing an endoprosthesis in accordance with the multilayered composite structure of the present invention because it produces a smaller heat influence zone (“HIZ”) or heat affected zone (HAZ) compared to other lasers, or it can substantially eliminate the HIZ or HAZ. In comparison, cutting an endoprosthesis using known methods can result in the tubular material being melted away, and thereby forming the pattern in the tubular member. Such melting can result in embrittlement of some materials due to oxygen uptake into the HIZ.
In one configuration, electrical discharge machining is used to shape endoprosthetic material and/or form holes in the endoprosthetic material as desired. As such, electrical discharge machining be capable of cutting all types of conductive materials such as exotic metal including titanium, hastaloy, kovar, inconel, hard tool steels, carbides, and the like. In electrical discharge, the main interaction between the stream of energy and the endoprosthetic material is thermal, where heat is generated by producing electrical discharges. This can lead to the endoprosthetic material being removed by melting and evaporation. Some examples of electrical discharge machining include wire electron discharge machining, CNC-controlled electrical discharge machining, sinker electrical discharge machining, small hole discharge machining, and the like.
In another configuration, a charged particle beam can be used for shaping the endoprosthetic material, wherein electron beams and ion beams exemplify charged particle beams. A charged particle beam is a group of electrically-charged particles that have approximately the same kinetic energy and move in approximately the same direction. Usually, the kinetic energies are much higher than the thermal energies of similar particles at ordinary temperatures. The high kinetic energy and the directionality of these charged beams can be useful for cutting and shaping of the green bodies, as described herein. Additionally, there are some instances where electron beams or ion beams are preferred over other cutting techniques.
In one configuration, a stream of chemical matter can be used in order to shape or form holes in the endoprosthetic material. Chemical-jet milling, for example, provides selective and controlled material removal by jet and chemical action. As such, the process is similar to water-jet cutting, which is described in more detail below. In any event, chemical-jet milling can be useful for shaping various types of endoprosthetic materials, which provides intricate shaping capabilities.
In another configuration, electrochemical shaping can be based on a controlled electrochemical dissolution process similar to chemical-jet milling an endoprosthetic material. As such, the endoprosthetic material can be attached to an electrical source in order to allow an electrical current to assist in the shaping.
In one configuration, hydro-cutting or water-jet cutting can be used to shape an endoprosthetic material. Hydro-cutting is essentially a water-jet technology that uses the high force and high pressure of a stream of water directed at the endoprosthetic material in order to cut and shape the material as desired. Hydro-cutting can be preferred over some of the other stream-cutting technologies because it can be free of heat, flame, and chemical reactions, and can provide a precise cold shaping technique. Also, heated water with or without being doped with reactive chemicals can also be used. Hydro-cutting is particularly suitable for polymeric endoprostheses, but can be used for metal materials when combined with abrasive particles, as described below.
Additionally, hydro-cutting can be enhanced by the introduction of particulate materials into the water feed line. As such, some hydro-cutting techniques utilize garnet or other rigid and strong materials in order to apply an abrasive cutting force along with the force applied by the water itself. Also, the hydro-cutting process in the present invention can be used with or without inclusion of such abrasives.
Additionally, one of the benefits of hydro-cutting is the ability to reutilize and recycle the spent water-jet material. As such, the endoprosthetic material can be easily separated from the spent water, thereby enabling the recycling and reuse of the water during the hydro-cutting process.
In one configuration, sandblasting, which fits into the regime of stream of matter cutting, can be used to shape an endoprosthetic material by projecting a high energy stream of sand particles at the material. Sandblasting cuts materials in a manner similar to hydro-cutting, especially when the water-jet is doped with abrasive particulates. Additionally, various other particulate streams other than sand can be used in the stream-cutting techniques and machinery.
An additional step of passivation can be performed during the manufacturing stage of the hybrid segmented endoprosthesis in order to form a homogeneous oxide layer for corrosion-resistance. The passivation process may be performed prior to installation of the markers in accordance with the present invention or it may be performed after installation of the radiopaque markers. It can also be done before or after the different annular elements or sub-endoprotheses are coupled together. Alternatively, multiple passivation processes may be performed, once prior to application of the markers, and again after insertion of the markers.
As originally shaped and/or fabricated, the annular elements or sub-endoprotheses can correspond to its delivery configuration, to a deployed configuration, or to a configuration therebetween. The annular elements or sub-endoprotheses can be fabricated with a configuration at least slightly larger than the delivery configuration. In this manner, the endoprosthesis can be crimped or otherwise compressed into its delivery configuration in a corresponding delivery device.
In another configuration, the annular elements or sub-endoprotheses can be originally fabricated from a tube having a diameter corresponding to the deployed configuration. In this manner, the longitudinally-free portions of the annular elements (e.g., elbow or foot not at a connection location) and circumferentially-free portions (e.g., the toe and/or heel portion of the foot extensions) can be maintained within the general cylindrical shape (e.g., diameter) of the endoprosthesis when deployed, so as to avoid such portions from extending radially inward when in the deployed configuration. The endoprosthesis can be designed to match the target vessel in which the endoprosthesis is to be deployed. For example, a stent can be provided with an outer diameter in the deployed configuration ranging from about 1 mm for neurological vessels to about 25 mm for the aorta. Similarly, a stent can be provided with a length ranging from about 5 mm to about 200 mm. Variations of these dimensions will be understood in the art based upon the intended application or indication for the endoprosthesis.
Also, the geometry of each component of the endoprosthesis or endoprosthetic element, such as the width, thickness, length and shape of the strut elements, interconnectors, crossbars, connectors, elbows, foot portions, ankle portions, toe portions, heel portions and the like can be selected to obtain predetermined expansion, flexibility, foreshortening, coverage scaffolding, and cross-sectional profile configurations. For example, longer crossbars and/or connectors can promote greater radial expansion or scaffolding coverage. The phase difference or circumferential alignment between adjacent annular elements likewise can be altered to control coverage and flexibility. Similarly, the number and placement of connection locations and, if present, the connectors, between longitudinally-adjacent annular elements can be selected to obtained the desired flexibility of the endoprosthesis. The number of elbows and/or foot extensions between connection locations also can be varied to achieve desired performance configuration.
After the different annular elements or sub-endoprotheses, which can be formed by the same or different processes, are prepared, they are coupled together into a hybrid segmented endoprosthesis. The different annular elements or sub-endoprotheses can be coupled together by any possible method, including methods of coupling different medical devices as is known in the art. For example, the different annular Aelements or sub-endoprotheses can be coupled together into a hybrid segmented endoprosthesis by brazing, forming a metallurgical bond, welding, forming a sleeve, forming a mechanical bond (e.g., forming a crimp to join two or more pieces of metal), or affixation with an adhesive. Other methods are also possible.
Generally, the hybrid segmented endoprosthesis of the present invention can be delivered into a body of a subject by any method known or developed. For example, the method of using catheters to deploy self-expandable or balloon-expandable stents can be employed.
In one embodiment, the hybrid segmented endoprosthesis of the present invention are configured for use in a body lumen. As such, the present invention includes a method of delivering a hybrid segmented endoprosthesis into a body lumen of a subject. Such a method includes: providing a hybrid segmented endoprosthesis as described herein; orienting the hybrid segmented endoprosthesis into a delivery orientation with a cross section that is smaller than the body lumen; inserting the hybrid segmented endoprosthesis in the delivery orientation into a delivery device, such as a deliver catheter that can be configured substantially as a catheter for delivering a stent; delivering the hybrid segmented endoprosthesis to a desired deployment site within the body lumen of the subject; removing the hybrid segmented endoprosthesis from the delivery device; and expanding the hybrid segmented endoprosthesis so as to have an enlarged dimension that applies radial forces to an inner wall of the body lumen.
The delivery system 1500 delivers the endoprosthesis 1200a with a catheter 1502 similarly to the method of delivering other endoprostheses into a body lumen. As such, an insertion site (not shown) is formed through the skin (not shown) that traverses into a body lumen 1540. A guidewire (not shown) is then inserted through the insertion site, through the body lumen 1540, to the delivery site 1544. A catheter (not shown) is then inserted into the body lumen 1540 to the delivery site 1544 over the guidewire, and the guidewire is optionally extracted. The delivery catheter 1502 is then inserted through the catheter (not shown) until reaching the delivery site 1544 and the catheter is withdrawn.
Optionally, the catheter is the delivery catheter 1502, and in this instance, the delivery catheter 1502 is retained at the delivery site 1544 and the endoprosthesis 1200a is delivered to the delivery site 1544 through the lumen 1507 of the delivery catheter 1502. A pusher 1510 can be used to push the endoprosthesis 1200a within the lumen 1507 of the delivery catheter 1502 to the delivery site 1544.
Accordingly, the delivery system 1500 is inserted through percutaneous insertion site (not shown) that traverses from the skin (not shown) into the body lumen 1540 until reaching the delivery site 1544. The pusher 1510 includes a distal end 1512 that pushes the endoprosthesis 1200a from the distal end 1508 of the delivery member 1504. Alternatively, the endoprosthesis 1200a can be disposed at the distal end 1508 of the delivery member 1504, and the pusher 1510 holds the endoprosthesis 1200a at the delivery site 1544 and the delivery member 1504 is retracted over the endoprosthesis 1200a and pusher 1510. Thus, the pusher 510 can push the endoprosthesis 1200a from the delivery catheter 1502 or the delivery member 1504 can be withdrawn over the endoprosthesis 1200a and pusher 1510 in order to deploy the endoprosthesis 1200a.
In one embodiment, the present invention can include a method of extracting the endoprosthesis from the body lumen, which can include: inserting an endoprosthesis-extracting medical device into the body lumen so as to come into contact with the endoprosthesis; engaging the endoprosthesis-extracting medical device with the endoprosthesis; radially compressing the endoprosthesis so as to have a reduced dimension with a cross section that is smaller than the body lumen; and retrieving the endoprosthesis from the desired deployment site within the body lumen of the subject. Optionally, the endoprosthesis can be received into the endoprosthesis-extracting medical device, which can be substantially similar to a catheter.
In one embodiment, at least one of delivering or retrieving the endoprosthesis is performed with a catheter. Catheters configured for delivering and/or retrieving endoprostheses from a body lumen can be adapted for delivering and/or retrieving the endoprosthesis of the present invention.
The present invention may be configured in other specific forms without departing from its spirit or essential characteristics. The described embodiments are to be considered in all respects only as illustrative and not restrictive. The scope of the invention is, therefore, indicated by the appended claims rather than by the foregoing description. All changes which come within the meaning and range of equivalency of the claims are to be embraced within their scope. All references recited herein are incorporated herein by specific reference.
This United States patent application is a continuation-in-part of U.S. patent application Ser. No. 11/374,923, filed Mar. 13, 2006, and entitled “SEGMENTED ENDOPROSTHESIS”, which is incorporated herein by specific reference in its entirety.
Number | Date | Country | |
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Parent | 11374923 | Mar 2006 | US |
Child | 12548268 | US |