Non-uniform stent

Abstract

Disclosed are example embodiments of a stent including a body formed of a nitinol wire material woven into a tapered shape. The body includes flared ends at both distal and proximal ends, with flare angles between 15 degrees and 30 degrees relative to a longitudinal axis of the stent. The body further includes a first portion having a first number of braid loops per unit length and a second portion having a second, lower number of braid loops per unit length, such that the first portion forms a tighter braid than the second portion. In the second portion, a wire segment of a braid loop is arranged at a shallower angle relative to the longitudinal axis compared to a wire segment of a braid loop in the first portion.

Description

Docket No. TERUM.0003.WONON-UNTFORM STENTTECHNICAL FIELD

[0001] The disclosure relates generally to the field of stents, and specifically and not by way of limitation, some embodiments are related to a non-uniformed stent that may have a taper and a variable braid density.BACKGROUND

[0002] Stents are implantable devices that are designed for insertion into a vein, artery, or other biological lumen, which provide structural support to keep the biological lumen open, thereby ensuring normal flow of fluids or substances within the biological lumen. Although stent insertion is generally a procedure performed to alleviate blockages and improve flow, the procedure may, in some cases, lead to complications, including thrombotic symptoms. Patients with vascular diseases that require a stenting treatment are known to have high risk for thrombosis. Therefore, without effectively capturing the thromboses or reducing the migration of thrombotic symptoms during a stenting treatment, blood clots may travel through the vascular system resulting in severe consequences, such as stroke, heart attack, organ damage, and other chronic health conditions.SUMMARY

[0003] In various embodiments, stents are disclosed that provide non-uniform structural configurations along a longitudinal axis to enhance performance in biological lumens. The stents may exhibit one or more variations along their length, including but not limited to: differences in braid density, wire angles, cross-sectional dimensions, taper profiles, radial forces, anchoring geometries, and flexibility characteristics. Such variations may be formed through adjustments to wire material, wire diameter, winding pitch, braid angle, or combinations thereof, and may serve to optimize luminal support, minimize migration, improve deployment characteristics, and accommodate complex anatomical pathways.

[0004] Disclosed are example embodiments of a stent including a body formed of a nitinol wire material woven into a tapered shape. The body includes flared ends at both distal and proximal ends, with flare angles between 15 degrees and 30 degrees relative to a longitudinal axis of the stent. The body further includes a first portion having a first number of braid loops per unit lengthDocket No. TERUM.0003.WO and a second portion having a second, lower number of braid loops per unit length, such that the first portion forms a tighter braid than the second portion. In the second portion, a wire segment of a braid loop is arranged at a shallower angle relative to the longitudinal axis compared to a wire segment of a braid loop in the first portion.

[0005] Disclosed are example embodiments of a stent including a body formed of a braided nitinol wire material woven to define a lumen having a longitudinal axis. The body includes a proximal section with a first braid density configured to exert a first radial force against a vessel wall and a distal section with a second, lower braid density configured to exert a second, lower radial force. A transition zone between the proximal and distal sections is configured to gradually change the braid density to reduce stress concentrations within the vessel, and flared ends at both proximal and distal ends of the body are angled outwardly relative to the longitudinal axis to inhibit migration after deployment.

[0006] Disclosed are example embodiments of a stent including support means formed of braided wire material for maintaining patency of a lumen in a vessel. The stent includes means for exerting a first radial force on a proximal portion of the vessel and means for exerting a second, lower radial force on a distal portion of the vessel. The stent further includes means for gradually transitioning between the first and second radial forces to reduce localized vessel wall stress and means for anchoring the stent within the vessel lumen to inhibit migration after deployment, wherein the anchoring means comprise outwardly flared end portions of the support means.

[0007] The features and advantages described in the specification are not all-inclusive. In particular, many additional features and advantages will be apparent to one of ordinary skill in the art in view of the drawings, specification, and claims. Moreover, it should be noted that the language used in the specification has been principally selected for readability and instructional purposes and may not have been selected to delineate or circumscribe the disclosed subject matter.BRIEF DESCRIPTION OF THE DRAWINGS

[0008] The foregoing summary, as well as the following detailed description, is better understood when read in conjunction with the accompanying drawings. The accompanying drawings, which are incorporated herein and form part of the specification, illustrate a plurality of embodiments and, together with the description, further serve to explain the principles involved and to enable a person skilled in the relevant art(s) to make and use the disclosed technologies.Docket No. TERUM.0003.WO

[0009] FIG. 1 illustrates a side view of a stent with different pitch sections, according to embodiments of the present disclosure.

[0010] FIG. 2 illustrates a side view of a stent with different wire diameters, according to embodiments of the present disclosure.

[0011] FIGS. 3A-3D illustrate side views of a stent with different pitch sections and wire diameters, according to embodiments of the present disclosure.

[0012] FIG. 4 illustrates a side view of a stent with internal meshes created by a particular weaving / coiling method, according to embodiments of the present disclosure.

[0013] FIGS. 5A-5C illustrate facing views of a stent with an example internal mesh, according to embodiments of the present disclosure.

[0014] FIG. 6 illustrates a side view of a stent having a tapered body with variable braid density, according to embodiments of the present disclosure.

[0015] FIG. 7 illustrates angled views of the stent of FIG. 6 from different orientations to show the variation in braid angles, according to embodiments of the present disclosure.

[0016] FIG. 8 illustrates a detailed partial view of the stent of FIG. 6 highlighting nitinol wire material and an optional radiopaque drawn fdled tube wire, according to embodiments of the present disclosure.

[0017] The figures and the following description describe certain embodiments by way of illustration only. One skilled in the art will readily recognize from the following description that alternative embodiments of the structures and methods illustrated herein may be employed without departing from the principles described herein. Reference will now be made in detail to several embodiments, examples of which are illustrated in the accompanying figures. It is noted that wherever practicable similar or like reference numbers may be used in the figures to indicate similar or like functionality.DETAILED DESCRIPTION

[0018] The present disclosure provides for non-uniform stent designs in which a stent is constructed using one or more structural wires of different diameters woven into a mesh having one or more sections with different winding pitches — where “pitch” refers to the number of windings (e.g., crossings or loops of a wire around the lumen) per unit longitudinal length of the stent. The non-uniform stent designs may create an internal mesh inside the stent when one orDocket No. TERUM.0003.WO more structural wires loop inward as a result of particular weaving methods, differences in wire diameters, or variations in winding pitch. The internal mesh may allow blood to flow normally while also capturing thrombotic material, thereby reducing risk of clot migration and reducing complications such as stroke, heart attack, organ damage, and other severe conditions during or after stent treatment.

[0019] FIG. 1 illustrates a side view 100 of a stent 110 with different pitch sections, according to embodiments of the present disclosure. As illustrated, the stent 110 includes a structural wire 120 woven into a mesh that defines a lumen of a given lumen diameter 152 along a longitudinal axis of the stent 110 providing a support means to a biological lumen. The structural wire 120 is made from materials including, but not limited to: stainless steel, nitinol, and cobalt-chromium alloy.

[0020] In the first section 130 (e.g., a proximal section) of the stent 110, the mesh has a first pitch 120a of the structural wire 120, where “pitch” refers to the number of windings of the structural wire 120 per unit longitudinal length of the stent (e.g., windings per millimeter or per centimeter). In the second section 140 (e.g., a distal section), the mesh has a second pitch 120b, different from the first pitch 120a. For example, in stents having a length between 50 millimeters (mm) and 170 mm and a diameter of approximately 10-20 mm, the pitch may range from about 0.03 windings per mm (i.e., one winding per ~35 mm) to about 0.2 windings per mm (i.e., one winding per ~5 mm), with higher pitch corresponding to a denser braid and greater radial force.

[0021] As illustrated in FIG. 1, the first pitch 120a is higher than the second pitch 120b, meaning that the first section 130 includes more windings of the structural wire 120 per unit longitudinal length than the second section 140. This higher pitch produces a tighter braid pattern and generally increases radial force and stiffness in the first section 130. Conversely, the lower pitch of the second section 140 yields fewer windings per unit length, resulting in a more open braid geometry that enhances flexibility and compliance.

[0022] In some embodiments, the stent is oriented such that the first end 150a of the lumen 150 is placed upstream (e.g., closer to the heart in an artery, further from the heart in a vein) of the second end 150b of the lumen in the targeted treatment area within the biological lumen to keep the biological lumen wide open to support normal blood flow. In some embodiments, the first end 150a is placed downstream (e.g., further from the heart in an artery, closer to the heart in a vein) of the second end 150b. The orientation may be based on one or more of the relative crush resistances of the first section 130 and the second section 140, the presence (or absence) of internalDocket No. TERUM.0003.WO meshes defined by the structural wires 120 in one or both of the first section 130 and the second section 140, the presence (or absence) of a preexisting stent or obstruction in the biological lumen, whether the biological lumen narrows or expands at the target location, a thickness of the biological lumen (and whether any tears or fissures are currently present therein) at the target location, and other factors that a skilled practitioner may evaluate for seating the stent 110 during a stenting procedure.

[0023] As illustrated, the stent 110 may terminate with flared ends 11 la-111b (generally or collectively, flared end 111) on one or both ends. In various embodiments, these flared ends project for a variable amount from the diameter for the lumen 150 defined by the stent 110 (e.g., one to two times the nominal diameter of the stent 110 at between 15 and 65 degrees from the longitudinal axis of the stent 110), which allow the stent 110 to be secured in a target location (e.g., a blood vessel) via spring-pressure pushing into the biological lumen or catching at a joint between a biological lumen and another anatomical feature (e.g., another blood vessel, sphincter or valve for an organ), etc. In one example, each of the flared ends l l la-b form an angle relative to a longitudinal axis of the main body of the stent 110 within an inclusive range of about 10 degrees to about 65 degrees, such as 10, 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65 or angles in between. The flared ends are made from the wires used in constructing the stent 110, and allow the wires to be woven back into the main body, and to define a given length for the assembly. In some embodiments, the flared ends 111 are included, but the first flared end 11 la is formed at a different angle relative to the longitudinal axis of the stent 110 than the second flared end 11 lb.

[0024] Both of the flared ends 111 may be omitted in some embodiments, resulting in a venous straight rod style stent. In some embodiments, one of first flared end I l la and the second flared end 11 lb is omitted.

[0025] In some embodiments, as illustrated, the flared ends 111 may terminate with a plurality of loops 112. The loops 112 may be formed from the structural wires 120 or other wires having a diameter that is larger or smaller, different than the diameter of structural wires 120. In some embodiments, the size of the plurality of loops 112 may be the same or vary.

[0026] In various embodiments, the stent 110 may be made from various materials including, but not limited to, steel, nitinol, tungsten, various biocompatible polymers, and combinations thereof (e.g., full or partial area coatings on otherwise bare metal, different materials used in different wires). Additionally, because the structural wires 120 may permit the stent 110 to bend, collapse,Docket No. TERUM.0003.WO and re- expand to deploy (or remove) the stent interior to a biological lumen or to flex as the biological subject moves, the materials used for the structural wires 120 are selected to exert a radially outward springing force, and to resist elastic deformation (e.g., the material of the structural wires 120 is not elastically deformable).

[0027] As described herein, the stent 110 is made by braiding, winding, or weaving various strands or wires among one another to produce an overall shape for a flexible stent 110. A structural wire is not bonded to itself to form the winding (e.g., via welds between wires) or constructed as a monolithic lattice, but instead variably overlaps itself so that the overall shape of the stent 110 may deform under compression and seek to return to an expanded resting state when the compressive force is removed; thereby allowing the stent 110 to be compressed to a smaller diameter (but longer length) for installation in a biological lumen, at which time the stent 110 expands outward and may be held in place via spring forces in the stent 110 against the walls of the biological lumen. Similarly, as the biological subject in which the stent 110 is deployed moves, the stent 110 may deform to account for stresses applied to the biological lumen, and return to a nominal shape when the stresses are removed. These braided / wound wires provide the structure of the stent 110 (e.g., as structural wires 120), in contrast to deployment wires or signaling wires that may be included in the stent 110 to aid in positioning and state transitions of the stent 110 or relaying a condition in the biological lumen at or near the stent 110 to an exterior observer.

[0028] FIG. 2 illustrates a side view 200 of a stent 110 with multiple wires having different wire diameters, according to embodiments of the present disclosure. As illustrated, the stent 110 includes a first structural wire 210 and a second structural wire 220, both woven separately from one another into a mesh defining a lumen 150 of a given lumen diameter 152 along a longitudinal axis of the stent 110 providing a support means to a biological lumen. Each of the structural wires 210, 220 are illustrated in FIG. 2 with the same pitch. In various embodiments, the illustrated stent 110 in FIG. 2 may represent a different stent from that illustrated in the other Figures of the present disclosure, or a different section of a unified stent having different properties in a given section from the properties illustrated in a different section shown in a different Figure.

[0029] The first structural wire 210 and the second structural wire 220 occupy an overlapping section 230. The first structural wire 210 has a first wire diameter 212 and the second structural wire 220 has a second wire diameter 222, which is different than the first wire diameter 212. AsDocket No. TERUM.0003.WO illustrated in FIG. 2, the first wire diameter 212 of the first structural wire 210 is greater than the second wire diameter 222 of the second structural wire 220.

[0030] Although discussed as separate wires, the first structural wire 210 and the second structural wire 220 may be specific lengths of a single structural wire 120 braided amongst itself to define a stent 110, in which the single structural wire 120 has a first length displaying a first diameter (e.g., as the first structural wire 210) and a second length displaying a second diameter (e.g., as the second structural wire 220). As structural elements of the stent 110, both the first structural wire 210 and the second structural wire 220 exhibit a radially outward spring force when compressed, thereby allowing the stent 110 to be secured in a biological lumen by pressing against the walls thereof, and seeking to return to a nominal shape and diameter for the stent 110, while permitting the stent 110 to flex and compress as the biological subject in which the stent 110 is implanted moves.

[0031] As illustrated in FIG. 2, the first structural wire 210 and the second structural wire 220 may be connected via a plurality of weld joints 240. These weld joints maintain the relative positions of the two wires when the mesh is compressed longitudinally, preventing uneven stacking or bunching during catheter loading. Accordingly, although the wires may share a common pitch in some regions, they may also exhibit different pitches — where “pitch” refers to the number of windings of the respective wire per unit longitudinal length — within the same overlapping section 230 (for example, where the second structural wire 220 has fewer windings per unit length than the first structural wire 210).

[0032] In some embodiments, sections in which both the first structural wire 210 and the second structural wire 220 are disposed may have both wires woven among one another such that both are compressed or expand together as forces are applied or released from the stent 110. Accordingly, the two structural wires may provide greater rigidity and a stronger outward springing force in sections where both are located relative to sections where only one is located. The differences in outward springing forces may be affected by the number of windings of a given structural wire in a section (e.g., with a higher pitch, corresponding to a greater number of windings per unit longitudinal length, corresponding to a higher force), the diameters of the structural wire in a given section (e.g., a wire with a greater diameter offering a higher force), a material of the structural wire used (e.g., affected by the structural properties of the metal used in the wires), and combinations thereofDocket No. TERUM.0003.WO

[0033] As illustrated, the stent 110 may terminate with flared ends 11 la-11 1b (generally of collectively, flared end 111) on one or both ends. In various embodiments, these flared ends project for a variable amount from the diameter for the lumen 150 defined by the stent 110 (e.g., one to two times the nominal diameter of the stent 110 at between 15 and 65 degrees from the longitudinal axis of the stent 110), which allow the stent 110 to be secured in a target location (e.g., a blood vessel) via spring-pressure pushing into the biological lumen or catching at a joint between a biological lumen and another anatomical feature (e.g., another blood vessel, sphincter or valve for an organ), etc. In one example, each of the flared ends l l la-b form an angle relative to a longitudinal axis of the main body of the stent 110 within an inclusive range of about 10 degrees to about 65 degrees, such as 10,15, 20, 25, 30, 35, 40, 45, 50, 55, 60, 65 or angles in between. The flared ends are made from the wires used in constructing the stent 110, and allow the wires to be woven back into the main body, and to define a given length for the assembly. In some embodiments, the flared ends 111 are included, but the first flared end 11 la is formed at a different angle relative to the longitudinal axis of the stent 110 than the second flared end 11 lb.

[0034] Both of the flared ends 111 may be omitted in some embodiments, resulting in a venous straight rod style stent. In some embodiments, one of first flared end I l la and the second flared end 11 lb is omitted. In some embodiments, the flared end(s) 111 may be formed by one or both of the first structural wire 210 and the second structural wire 220 (e.g., the first flared end 11 la by the first structural wire 210 and the second flared end 11 lb by the second structural wire 220; the first flared end I l la by the first structural wire 210 and the second flared end 111b by the first structural wire 210; the first flared end I l la by the second structural wire 220 and the second flared end 11 lb by the second structural wire 220; etc.).

[0035] In some embodiments, as illustrated, the flared ends 111 may terminate with a plurality of loops 112. The loops 112 may be formed from the first / second structural wires 210 / 220 or other wires having a diameter that is larger or smaller, different than the diameter of first / second structural wires 210 / 220. In some embodiments, the size of the plurality of loops 112 may be the same or vary.

[0036] In various embodiments, the stent 110 may be made from various materials including, but not limited to, steel, nitinol, tungsten, various biocompatible polymers, and combinations thereof (e.g., full or partial area coatings on otherwise bare metal, different materials used in different wires).Docket No. TERUM.0003.WO

[0037] FIGS. 3A-3D illustrate side views of a stent 110 with different pitch sections and wire diameters, according to embodiments of the present disclosure. FIGS. 3A-3D provide examples of the non-uniform stent designs incorporating both pitch variations and wire diameter variations. In various embodiments, the illustrated stents 110 in FIGS. 3A-3D may represent different stents from those illustrated in the other Figures of the present disclosure, or a different section of a unified stent having different properties in a given section from the properties illustrated in a different section shown in a different Figure.

[0038] As shown in FIGS. 3A-3D, the present disclosure contemplates that the pitch of the first structural wire 210 and the pitch of the second structural wire 220 — each defined as the number of windings per unit longitudinal length — may be varied independently or together along the longitudinal axis of the stent 110. These variations may occur in one or more sections of the stent to tune radial force, flexibility, or internal mesh formation.

[0039] FIG. 3A illustrates a side view 300A of stent 110 including first structural wire 210 and second structural wire 220 in overlapping section 230 where only the first structural wire 210 changes pitch (number of windings per unit length) between first section 130 and second section 140.

[0040] As illustrated, the first structural wire 210 has a first pitch 310a (a first number of windings per unit longitudinal length) in the first section 130 and a second pitch 310b (a different number of windings per unit longitudinal length) in the second section 140. The second structural wire 220 maintains a constant pitch 320a, 320b in both sections. Thus, only the first structural wire 210 varies in winding density.

[0041] FIG. 3B illustrates a side view 300B of stent 110 in which only the second structural wire 220 changes pitch between first section 130 and second section 140, whereas the first structural wire 210 maintains a constant pitch.

[0042] As illustrated, the first structural wire 210 exhibits the same pitch 310a, 310b in both the first section 130 and second section 140, while the second structural wire 220 changes from a first pitch 320a to a second pitch 320b, corresponding to a change in the number of windings per unit longitudinal length.

[0043] FIG. 3C illustrates a side view 300C in which both the first structural wire 210 and the second structural wire 220 change pitch between sections 130 and 140, but the two wires share theDocket No. TERUM.0003.WO same pitch within a given section (for example, both wires having pitch 310a, 320a in section 130 and pitch 310b, 320b in section 140).

[0044] As illustrated, the first structural wire 210 and the second structural wire 220 each change the number of windings per unit length between the first section 130 and the second section 140, while maintaining equality of pitch between the wires within each section.

[0045] FIG. 3D illustrates a side view 300D in which both the first structural wire 210 and the second structural wire 220 change pitch between sections, but each wire exhibits a different pitch from the other within the same section. For example, in section 130, the first wire 210 may have a higher pitch (more windings per unit length) than the second wire 220, whereas in section 140 the relative pitch ordering may reverse.

[0046] As illustrated in FIG. 3D, the differing pitches of the first structural wire 210 and the second structural wire 220 within each section create different winding densities that may alter the mechanical behavior of the stent, including radial force, flexibility, and the geometry of internal loop formation.

[0047] As illustrated in FIG. 3D, both the first structural wire 210 and the second structural wire 220 change pitch, but have different pitches in the same section. These differences in pitches may result in a ratio between the pitches swapping (e.g., an A:B ratio becoming a B: A ratio), or changing a frequency at which the coils of the structural wire 210, 220 intersect one another in the different sections 130, 140.

[0048] Although illustrated in FIGS. 3A-3D that the overlapping section 230 includes two sections 130, 140, the present disclosure contemplates that the overlapping section 230 may include more than two sections. In addition, although illustrated in FIGS. 3C-3D that the first structural wire 210 and the second structural wire 220 change pitch synchronously with each other, the present disclosure contemplates that the first structural wire 210 and the second structural wire 220 can change pitch asynchronously with each other.

[0049] FIG. 4 illustrates a side view 400 of a stent 110 with internal meshes created by a particular weaving / coiling method, according to embodiments of the present disclosure. As illustrated in FIG. 4, one or more internal meshes 410 are created by a particular weaving / coiling method to define a plurality of loops in which each loop of a plurality of loops at least partially overlaps one other loop of the plurality of loops to restrict a flowpath from a first end 150a of the lumen 150 to a second end 150b of the lumen 150 to be less than the given lumen diameter 152.Docket No. TERUM.0003.WO

[0050] The particular weaving / coiling method may either be a hand-made method or a machine- made method, which creates the internal meshes 410 with any desired patterns in two or three dimensions, such as a screen or a basket, and places the internal meshes 410 at any desired locations along the longitudinal axis of the stent 110. The internal meshes 410 created by the particular weaving / coiling method may be further combined with other non-uniform stent designs including variable wire diameters and variable wiring pitches to create more complicated designs.

[0051] In some embodiments, the difference in wire diameters generates a higher radial force looping the first structural wire 210 more inwardly than the second structural wire 220 in the overlapping section 230 to encourage the formation of loops for the internal meshes 410. Additionally or alternatively, changes in pitch of one or more of the structural wires 120, 210, 220 can generate variable radial forces that affect the coiling or weaving of the individual wires to direct the formation or maintain the construction the internal loops of the internal meshes. Accordingly, in various embodiments, the internal meshes 410 may preferable be formed at the boundary between two sections of the stent 110 having different pitches for a given wire.

[0052] The internal mesh 410 may be woven by one of the first structural wire 210 or the second structural wire 220 or by a third wire 420, having a third diameter 422 different than the first diameter 212 of the first structural wire 210 and the second diameter 222 of the second structural wire 220. The third diameter 422 may preferably be smaller than either the first diameter 212 and the second diameter 222 or larger that either the first diameter 212 and the second diameter 222.

[0053] FIGS. 5A-5C illustrate facing views of a stent 110 with an example internal meshes 410, according to embodiment of the present disclosure. Each of the facing views may be understood to be taken at different cross-sections of a single stent 110 with various differently defined internal meshes 410 or from different stents 110 that are constructed with internally-uniform internal meshes 410 of different designs from the other stents 110.

[0054] FIG. 5A illustrates a facing view 500A of an internal mesh defined by the first structural wire 210 with the first wire diameter 212. FIG. 5B illustrate a facing view 500B of an internal mesh defined by the second structural wire 220 with the second wire diameter 222. FIG. 5C illustrate a facing view 500C of an internal mesh defined by both the first structural wire 210 with the first wire diameter 212 and the second structural wire 220 with the second wire diameter 222.

[0055] As illustrated in FIG. 5 A, the first structural wire 210 creates a plurality of loops internal to the lumen 150 of the stent 110. Each loop of the plurality of loops at least partially overlaps oneDocket No. TERUM.0003.WO other loop of the plurality of loops to define an internal mesh which restricts a flowpath from a first end 150a of the lumen 150 to a second end 150b of the lumen 150 to be less than the given lumen diameter 152. For example, because the loops project inward to the lumen 150, the lumen 150 may have a nominal internal diameter that allows objects up to X mm wide to pass through the stent 110, but the loops may define one or more regions that block such objects from traversing the stent 110 while still allowing smaller objects (e.g., having a width less than Y mm, where Y < X) and fluids to pass through the stent 110.

[0056] The internal mesh in FIG. 5A may be created by weaving or coiling the first structural wire 120 / 210 using different pitches — i.e., different numbers of windings per unit longitudinal length — in different sections of the stent 110 as illustrated in FIG. 1. The internal mesh may be disposed within one or both of first section 130 and second section 140.

[0057] As illustrated in FIG. 5B, the second structural wire 220 creates a plurality of loops internal to the lumen 150 of the stent 110, while the first structural wire 210 (not illustrated) remains defining the exterior of the stent 110 and does not project inward to the lumen 150. Each loop of the plurality of loops at least partially overlaps one other loop of the plurality of loops to define an internal mesh 410 which restricts a flowpath from a first end 150a of the lumen 150 to a second end 150b of the lumen 150 to be less than the given lumen diameter 152. For example, because the loops project inward to the lumen 150, the lumen 150 may have a nominal internal diameter that allows objects up to X mm wide to pass through the stent 110, but the loops may define one or more regions that block such objects from traversing the stent 110 while still allowing smaller objects (e.g., having a width less than Y mm, where Y < X) and fluids to pass through the stent 110.

[0058] As in FIG. 5A, the internal mesh in FIG. 5B may be formed by weaving or coiling the second structural wire 220 with different pitches (different winding densities along the longitudinal axis) in different sections of the stent 110.

[0059] As illustrated in FIG. 5C, both the first structural wire 210 and the second structural wire 220 create a plurality of loops internal to the lumen 150 of the stent 110 to define a given internal mesh 410. Each loop of the plurality of loops at least partially overlaps one other loop of the plurality of loops to restrict a flowpath from a first end 150a of the lumen 150 to a second end 150b of the lumen 150 to be less than the given lumen diameter 152.Docket No. TERUM.0003.WO

[0060] The internal mesh in FTG. 5C may be created by differences in pitch — i.e., differing numbers of windings per unit length — between the first structural wire 210 and the second structural wire 220, or by intentionally varying pitch along the longitudinal axis as illustrated in FIGS. 3A-3D.

[0061] In some example embodiments, the addition to permitting the stent 110 to capture obstructions passing through the lumen 150, and thereby easing aspiration operations at a later time, the internal meshes 410 may increase the crush resistance and strength of the stent 110, while still permitting normal flow of bodily fluids (e.g., blood) for proper operation of the stent 110.

[0062] FIG. 6 illustrates a side view of stent 600, according to additional embodiments of the present disclosure. As shown, stent 600 includes body 602 formed of wire 604. Wire 604 may be a nitinol or other superelastic alloy suitable for endovascular deployment. Body 602 may be braided into tapered shape 606, which decreases in diameter along longitudinal axis 614. Tapered profde 606 may improve deployment accuracy, enhance vessel wall apposition, or facilitate pressure gradient control across a stenotic segment.

[0063] Body 602 includes flared ends 608 located at distal end 610 and proximal end 612. Each flared end 608 extends outwardly at an angle relative to longitudinal axis 614, with flare angles ranging from approximately 15 degrees to 30 degrees, or approximately 5 degrees to 50 degrees in some embodiments. Flared ends 608 may act as anchoring elements that resist axial displacement and reduce migration risk post-deployment. Flare geometry may also distribute radial and axial forces more evenly along a vessel wall to reduce local trauma.

[0064] Body 602 may include first portion 616 and second portion 618, arranged sequentially along longitudinal axis 614. First portion 616 may have a higher braid density, e.g., a greater number of braid loops per longitudinal unit, compared to second portion 618. This difference in loop density may result in higher radial force and reduced flexibility in first portion 616, and increased compliance and flexibility in second portion 618. In some cases, denser braid zones (e.g., first portion 616) may align with a stenosed region or branching location, while loose zones (e.g., second portion 618) may accommodate vessel motion or curvature.

[0065] In some embodiments, stent 600 may have a body diameter ranging from approximately 10 mm to 20 mm in the expanded state, or approximately 5mm to 40 mm in the expanded state in some embodiments, and an overall length ranging from about 60 mm to 150 mm, or 30 mm to 300 mm in some embodiments. These ranges may correspond to typical dimensions of venous sinusesDocket No. TERUM.0003.WO or large peripheral veins. The combination of tapered profile 606 and variable braid density between first portion 616 and second portion 618 may improve adaptability to a wide range of clinical anatomies and hemodynamic conditions.

[0066] In some embodiments, flared end 608 includes a rounded segment transitioning into an angled segment, the rounded segment having a radius of curvature in the range of about 0.25 mm to 0.6 mm in some embodiments, or about 0.15 mm to 1 mm in other embodiments, the angled segment having an angle relative to the longitudinal axis in the range of about 20° to 40° in some embodiments, and about 15° to 60° in other embodiments. The rounded segment may reduce risk of vessel wall puncture, abrasion, or unintended perivascular flow. In cases involving covered stents or adjunctive sealing materials, the rounded geometry may also help reduce risk of endoleak — a condition in which blood leaks into or around an excluded vascular region, such as an aneurysm sac, despite placement of an intraluminal implant. The angled segment may promote positional stability by increasing surface contact area for engagement with a vessel wall, improving anchoring performance. Rounded-to-angled transitions may be formed during braid programming or fixed via thermal post-processing of the wire structure.

[0067] In some example embodiments, functional coatings may be applied to body 602. For example, an anti-thrombogenic agent may be applied locally to flared end 608 or to selected struts of the braid pattern to reduce thrombus formation during or after deployment. Additionally, portions of body 602 may be coated with a biocompatible polymer to improve endothelialization — that is, the natural process by which the inner lining of a blood vessel (the endothelium) grows over the surface of the implant. Promoting endothelialization may help integrate the stent with surrounding tissue and reduce long-term complications. Coatings may include hydrophilic or drugeluting polymers applied using techniques such as dip coating, spray deposition, or plasma- enhanced chemical vapor deposition.

[0068] Coating coverage may be full-length, segmental, or selectively targeted depending on clinical indication, deployment zone, or vessel pathology. In one embodiment, only flared ends 608 are coated to minimize thrombogenicity while maintaining bare-metal interaction along central body 602 for improved endothelial integration. In another embodiment, both ends and a portion of second portion 618 may be coated to provide a dual-function balance between visibility and biologic response.Docket No. TERUM.0003.WO

[0069] FIG. 7 illustrates a pair of angled views of stent 600 of FIG. 6, according to embodiments of the present disclosure. The upper view depicts stent 600 from a first perspective that shows taper, longitudinal axis, and distribution of braid density between first portion 616 and second portion 618. The lower view highlights angular orientation of individual braid loops. Wire segment 720 of a braid loop in second portion 618 is shown at shallower angle 722 relative to longitudinal axis 614 than wire segment 724 of a braid loop in first portion 616, while wire segment 724 of a braid loop in first portion 616 is shown at a steeper angle 726 relative to the same axis. This difference between steeper angle 726 and shallower angle 722 illustrates the programmed variation in braid geometry that contributes to different radial force and flexibility characteristics between the two portions of the stent.

[0070] Difference in braid angles is a function of loop spacing and may correlate with mechanical properties of stent 600. Shallower angle 722 in the second portion 618 of the stent 600 may enhance longitudinal flexibility and reduce radial force, supporting deployment in tortuous or compressible anatomy. A steeper angle of wire segment 724 in first portion 616 may provide higher radial strength and outward force, useful for stabilizing segments adjacent to vessel narrowing or thrombus. Variation in braid pattern may be programmed during manufacturing and fixed by thermal setting to retain shape memory.

[0071] FIG. 8 illustrates a view of stent 600, according to embodiments of the present disclosure. Wire 604 is illustrated along with drawn filled tube (DFT) wire 826. DFT wire 826 may be woven into the braid structure to improve radiopacity without compromising flexibility or strength. Core materials of DFT wire may include platinum, gold, or tantalum, encased within an outer shell of nitinol or stainless steel.

[0072] In some embodiments, one or more DFT wires 826 may be included circumferentially, helically, or longitudinally within body 602. Distribution of DFT wires may be symmetric or asymmetric to enhance visualization under fluoroscopy or computed tomography (CT). Radiopaque wires may serve as orientation markers during deployment and follow-up, and may be spaced to delineate first portion 616 and second portion 618 or to indicate correct positioning relative to vascular landmarks. Number, position, and type of DFT wires may be tailored based on imaging modality and target anatomy.

[0073] In some embodiments, the stent may incorporate radiopaque marker functionality through the use of one or more drawn filled tube (DFT) wires integrated into the braid construction of theDocket No. TERUM.0003.WO stent body. The DFT wire may include a nitinol exterior surrounding a radiopaque core, such as platinum or platinum-iridium. The DFT wire enables the stent to be radiographically visible during deployment and post-implantation follow-up without the need for separate radiopaque markers.

[0074] The foregoing description of DFT wire integration is intended to encompass both continuously integrated and locally spliced configurations. In some embodiments, one or more DFT filaments extend substantially along the full length of the stent braid to provide a generally uniform radiopaque profile. In other embodiments, DFT segments are introduced only in selected regions (for example, near the proximal and / or distal ends, or adjacent to a transition zone) to create localized radiopaque markers while preserving predominantly nitinol construction elsewhere. In each case, the DFT filaments function as structural braid elements that follow the same winding pattern as the surrounding nitinol wires, thereby maintaining overall braid geometry and mechanical performance while imparting enhanced imaging visibility.

[0075] In certain embodiments, the DFT wire may be spliced into the stent braid pattern, such that the DFT wire forms one or more continuous braid filaments that are interwoven directly into the stent body structure along with conventional nitinol filaments. In such configurations, a majority of the braid filaments may consist of nitinol wires without radiopaque cores, while only a minority (e.g., one or two braid filaments) consist of the spliced-in DFT wire.

[0076] The incorporation of DFT wire in this manner may eliminate the need for conventional tantalum marker wires, which have traditionally been affixed to stent structures through bonding, welding, or crimping operations after braid formation. As such, the DFT integration may simplify manufacturing by eliminating additional post-braid attachment steps and may further improve production yield by eliminating potential failure points associated with separate marker bonding. Use of DFT wires also reduces dependency on tantalum raw material supply chains.

[0077] In some embodiments, the stent may incorporate one or more drawn filled tube (DFT) wires integrated into the braid structure to provide radiopacity for imaging visualization. The DFT wire may comprise an outer layer of nitinol and a core of radiopaque material, such as platinum or platinum-iridium, to enhance visibility under fluoroscopic or radiographic imaging.

[0078] The DFT wire may be introduced into the stent braid in multiple ways. In certain embodiments, the DFT wire may be continuously integrated into one or more filaments of the braid throughout the body of the stent. In alternate embodiments, the DFT wire may be spliced into the braid at one or more terminal winding positions near the proximal and / or distal ends ofDocket No. TERUM.0003.WO the braid structure. In such configurations, the DFT wire may follow the established winding pattern both forward and backward during the braiding process, thereby creating localized regions of radiopacity at selected locations without altering the overall mechanical integrity of the braid. This splice-in approach enables selective positioning of radiopaque segments without requiring modifications to mandrel geometry or braid machine programming.

[0079] In some embodiments, only a subset of the total braid filaments may be formed from DFT wires, while the remaining filaments are conventional solid nitinol wires. The relative proportion of DFT wires to nitinol wires may be selected based on the desired radiopacity profile, clinical indication, or fluoroscopic visualization requirements.

[0080] The integration of DFT wires directly into the braid structure may eliminate the need for separate radiopaque marker bands or tantalum coils affixed post-braiding. As such, manufacturing may be simplified by removing secondary bonding, welding, or crimping operations. This approach may also improve manufacturing yields by reducing potential failure modes associated with post-braid marker attachment steps. Additionally, integration of DFT wires may reduce or eliminate dependency on tantalum supply chains, providing greater flexibility in material sourcing.

[0081] The DFT integration techniques described herein may be applied across a variety of stent types and clinical applications. In various embodiments, these include but are not limited to: venous stents, deep vein thrombosis (DVT) stents, arterial stents, neurovascular flow diverters, carotid artery stents (e.g., Casper®-type designs), embolic protection devices (EPD), and other endovascular implant devices. The techniques may serve as a drop-in manufacturing upgrade for existing stent platforms, allowing radiopacity enhancements without substantial reengineering of braid patterns, mandrel sizes, or machine setups.

[0082] In certain embodiments, the DFT-enhanced stent designs may be implemented in various stent types including, but not limited to: venous stents, deep vein thrombosis (DVT) stents, neurovascular flow diverters, endovascular protection devices (EPD), and arterial stents. In some embodiments, the DFT wire integration approach may serve as a drop-in manufacturing improvement for existing stent platforms, allowing for direct substitution of conventional marker designs without requiring changes to braid machine settings, braid patterns, or mandrel geometries.

[0083] In one embodiment, the DFT wire used in the stent braid may have an outer nitinol layer with a nominal wire diameter substantially equivalent to the remaining nitinol braid wires to maintain uniformity in braid geometry and mechanical properties. The DFT wire core may includeDocket No. TERUM.0003.WO a platinum, platinum -iridium, or other radiopaque material selected to achieve desired radi opacity on fluoroscopy or x-ray imaging systems. In some embodiments, multiple DFT braid filaments may be incorporated into the braid pattern to achieve enhanced visualization from multiple fluoroscopic angles.

[0084] The integration of DFT wires into the stent braid may provide a radiopaque stent structure without compromising mechanical flexibility, radial strength, or fatigue resistance. In some embodiments, the stent may include a tapered configuration with varying braid densities as otherwise described herein, with the DFT braid filaments following the same pitch variations as the surrounding nitinol wires.

[0085] The present disclosure may also be understood with reference to the following numbered clauses.

[0086] Clause 1 : A stent, comprising a body formed of a nitinol wire material, the body being woven into a tapered shape; the body having a first portion with a first number of braid loops per unit length and a second portion with a second number of braid loops per unit length, the second number being smaller than the first; and a wire segment of a braid loop of the second portion being arranged at a shallower angle relative to a longitudinal axis of the stent compared to a wire segment of a braid loop of the first portion.

[0087] Clause 2: The stent of Clause 1, further comprising a radiopaque drawn-filled-tube wire.

[0088] Clause 3 : The stent of Clause 1 or 2, wherein the body has a size ranging between about 10 mm and 20 mm in diameter.

[0089] Clause 4: The stent of any of Clauses 1-3, wherein the body has a length ranging between about 60 mm and 150 mm.

[0090] Clause 5: The stent of any of Clauses 1-4, wherein the tapered shape provides increased radial force in the first portion compared to the second portion.

[0091] Clause 6: The stent of any of Clauses 1—5, wherein flared ends of the body are coated with an anti-thrombogenic agent.

[0092] Clause 7: The stent of any of Clauses 1-6, wherein the body includes a biocompatible polymer coating.

[0093] Clause 8: The stent of any of Clauses 1-7, wherein the tapered shape is configured to reduce migration within a vessel.Docket No. TERUM.0003.WO

[0094] Clause 9: The stent of any of Clauses 1-8, wherein flared ends are configured to engage vessel walls to prevent displacement.

[0095] Clause 10: The stent of any of Clauses 1-9, wherein wire segments are arranged in a helical pattern along the longitudinal axis.

[0096] Clause 11 : The stent of any of Clauses 1-10, wherein flared ends include a rounded portion and an angled portion, the rounded portion reducing puncture risk by distributing contact pressure.

[0097] Clause 12: The stent of any of Clauses 1-11, wherein an angle of the taper is between about 10° and 20°.

[0098] Clause 13: The stent of any of Clauses 1-12, wherein a flared angle of a distal end is between about 15° and 30° relative to the longitudinal axis.

[0099] Clause 14: The stent of any of Clauses 1-12, wherein a flared angle of a proximal end is between about 15° and 30° relative to the longitudinal axis.

[0100] Clause 15: The stent of any of Clauses 1-12, wherein the body includes flared ends at both distal and proximal ends, each having a flare angle between 15° and 30° relative to the longitudinal axis.

[0101] Clause 16: The stent of any of Clauses 1-15, wherein the first portion comprises a tighter braid than the second portion.

[0102] Clause 17: A stent comprising a body formed of braided nitinol wire material woven to define a lumen, the body including a proximal section having a first braid density configured to exert a first radial force, a distal section having a second, lower braid density to exert a second, lower radial force, a transition zone that gradually changes the braid density to reduce stress concentrations, and flared ends at both proximal and distal ends.

[0103] Clause 18: The stent of Clause 17, wherein the transition zone comprises a continuously varying braid pitch changing from a first pitch in the proximal section to a second, larger pitch in the distal section, smoothing the radial force gradient.

[0104] Clause 19: The stent of Clause 17 or 18, wherein the proximal section has a higher wire angle relative to the longitudinal axis than the distal section, increasing radial stiffness in the proximal section.

[0105] Clause 20: A stent comprising support means formed of braided wire material, means for exerting a first radial force on a proximal portion of a vessel, means for exerting a second,Docket No. TERUM.0003.WO lower radial force on a distal portion, means for gradually transitioning between the forces, and means for anchoring the stent via outwardly flared end portions.

[0106] Clause 21 : A stent comprising a first structural wire woven into a mesh defining a lumen of a given diameter, the mesh having a first pitch in a first section and a second pitch, different from the first, in a second section.

[0107] Clause 22: The stent of Clause 21, further comprising a second structural wire of a different wire diameter.

[0108] Clause 23: The stent of Clause 22, wherein the second structural wire is included in both the first and second sections, having a third pitch in the first and a fourth pitch in the second.

[0109] Clause 24: The stent of any of Clauses 22-23, wherein at least one structural wire defines internal loops forming an internal mesh restricting a flowpath to less than the lumen diameter.

[0110] Clause 25: The stent of any of Clauses 22-24, wherein the first and second structural wires are connected via weld joints maintaining relative position during compression.

[0111] Clause 26: The stent of Clause 21, wherein the first structural wire alone defines internal loops forming an internal flow-restricting mesh.

[0112] Clause 27: A stent comprising first and second structural wires of different diameters woven into a mesh defining a lumen.

[0113] Clause 28: The stent of Clause 27, wherein each wire has first / second and third / fourth pitches in the first and second sections, respectively.

[0114] Clause 29: The stent of Clause 27 or 28, wherein at least one wire defines internal overlapping loops forming a flow-restricting internal mesh.

[0115] Clause 30: The stent of any of Clauses 27-29, wherein the wires are held in position by weld joints during compression.

[0116] Clause 31 : A stent comprising a first structural wire woven into a mesh, the wire defining internal overlapping loops that restrict a flowpath.

[0117] Clause 32: The stent of Clause 31, further comprising a second structural wire of different diameter.

[0118] Clause 33: The stent of Clauses 31-32, wherein the second wire also defines internal loops forming the internal mesh.

[0119] Clause 34: The stent of any of Clauses 31-33, wherein weld joints hold the wires in relative position when compressed.Docket No. TERUM.0003.WO

[0120] Clause 35: The stent of any of Clauses 31-34, wherein both wires have differing pitches in first and second sections as described in Clauses 21-23.

[0121] Clause 36: The stent of Clause 31, wherein the first structural wire has differing first and second pitches in first and second sections.

[0122] Clause 37: A stent comprising support means woven to define a lumen, the support means defining at least one of: (i) a first and second section having different pitches; (ii) an overlapping section in which first and second structural wires of different diameters are separately woven; and (iii) an internal mesh formed by internal loops restricting a flowpath.

[0123] Clause 38: The stent of Clause 37, wherein the overlapping section corresponds to at least one of the first and second sections.

[0124] Clause 39: The stent of Clause 37 or 38, wherein the internal mesh is disposed in at least one section.

[0125] Clause 40: The stent of any of Clauses 37-39, wherein the structural wires are joined by weld joints that maintain position during compression.

[0126] Clause 41 : The stent of Clause 37, wherein the support means defines at least two of (i)- (iii).

[0127] Clause 42: The stent of Clause 37, wherein the support means defines all three of (i)- (iii).

[0128] Clause 43: Any other embodiment discussed herein.

[0129] One or more elements or aspects or steps, or any portion(s) thereof, from one or more of any of the systems and methods described herein may be combined with one or more elements or aspects or steps, or any portion(s) thereof, from one or more of any of the other systems and methods described herein and combinations thereof, to form one or more additional implementations and / or claims of the present disclosure.

[0130] One or more of the components, steps, features, and / or functions illustrated in the figures may be rearranged and / or combined into a single component, block, feature or function or embodied in several components, steps, or functions. Additional elements, components, steps, and / or functions may also be added without departing from the disclosure. The apparatus, devices, and / or components illustrated in the Figures may be configured to perform one or more of the methods, features, or steps described in the Figures. The algorithms described herein may also be efficiently implemented in software and / or embedded in hardware.Docket No. TERUM.0003.WO

[0131] Reference in the specification to “one embodiment” or “an embodiment” means that a particular feature, structure, or characteristic described in connection with the embodiment is included in at least one embodiment of the invention. The appearances of the phrase “in one embodiment” in various places in the specification are not necessarily all referring to the same embodiment.

[0132] The foregoing description of the embodiments of the present invention has been presented for the purposes of illustration and description. It is not intended to be exhaustive or to limit the present invention to the precise form disclosed. Many modifications and variations are possible in light of the above teaching. It is intended that the scope of the present invention be limited not by this detailed description, but rather by the claims of this application. As will be understood by those familiar with the art, the present invention may be embodied in other specific forms without departing from the spirit or essential characteristics thereof. Likewise, the particular naming and division of the modules, routines, features, attributes, methodologies and other aspects are not mandatory or significant, and the mechanisms that implement the present invention or its features may have different names, divisions and / or formats.

[0133] The previous description is provided to enable any person skilled in the art to practice the various aspects described herein. Various modifications to these aspects will be readily apparent to those skilled in the art, and the generic principles defined herein may be applied to other aspects. Thus, the claims are not intended to be limited to the aspects shown herein, but is to be accorded the full scope consistent with the language claims, wherein reference to an element in the singular is not intended to mean “one and only one” unless specifically so stated, but rather “one or more.” The word “exemplary” is used herein to mean “serving as an example, instance, or illustration.” Any aspect described herein as “exemplary” is not necessarily to be construed as preferred or advantageous over other aspects. Unless specifically stated otherwise, the term “some” refers to one or more. Combinations such as “at least one of A, B, or C,” “one or more ofA, B, or C,” “at least one of A, B, and C,” “one or more of A, B, and C,” and “A, B, C, or any combination thereof’ include any combination of A, B, and / or C, and may include multiples of A, multiples of B, or multiples of C. Specifically, combinations such as “at least one of A, B, or C,” “one or more of A, B, or C,” “at least one of A, B, and C,” “one or more of A, B, and C,” and “A,B, C, or any combination thereof’ may be A only, B only, C only, A and B, A and C, B and C, or A and B and C, where any such combinations may contain one or more member or members of A,Docket No. TERUM.0003.WOB, or C. All structural and functional equivalents to the elements of the various aspects described throughout this disclosure that are known or later come to be known to those of ordinary skill in the art are expressly incorporated herein by reference and are intended to be encompassed by the claims. Moreover, nothing disclosed herein is intended to be dedicated to the public regardless of whether such disclosure is explicitly recited in the claims. The words “module,” “mechanism,” “element,” “device,” and the like may not be a substitute for the word “means.” As such, no claim element is to be construed as a means plus function unless the element is expressly recited using the phrase “means for.”

Claims

Docket No. TERUM.0003.WOCLAIMSWHAT IS CLAIMED IS:

1. A stent, comprising: a body formed of a nitinol wire material, the body being woven into a tapered shape; the body having a first portion with a first number of braid loops per unit length and a second portion with a second number of braid loops per unit length, the second number of braid loops per unit length being smaller than the first number of braid loops per unit length; and a wire segment of a braid loop of the second portion being arranged at a shallower angle relative to the longitudinal axis of the stent compared to a wire segment of a braid loop of the first portion.

2. The stent of claim 1, further comprising a radiopaque drawn filled tube wire.

3. The stent of claim 1, the body having a size ranging between about 10mm and 20mm in diameter.

4. The stent of claim 1, the body having a length ranging between about 60mm and 150mm.

5. The stent of claim 1, wherein the tapered shape is configured to provide increased radial force in the first portion compared to the second portion.

6. The stent of claim 1, wherein the flared ends are coated with an anti-thrombogenic agent.

7. The stent of claim 1, wherein the body includes a biocompatible polymer coating.

8. The stent of claim 1, wherein the tapered shape is designed to reduce migration within a vessel.Docket No. TERUM.0003.WO9. The stent of claim 1, wherein the flared ends are designed to engage with vessel walls to prevent displacement.

10. The stent of claim 1, wherein the wire segments are arranged in a helical pattern along the longitudinal axis of the stent.

11. The stent of claim 1, wherein the flared ends include a rounded portion and an angled portion, the rounded portion configured to reduce the risk of puncturing vessel walls by distributing contact pressure more evenly.

12. The stent of claim 1, wherein the angle of the taper is between about 10 degrees and 20 degrees.

13. The stent of claim 1, wherein the flared angle of the distal end is between about 15 degrees and about 30 degrees relative a longitudinal axis of the stent.

14. The stent of claim 1, wherein the flared angle of the proximal end is between about 15 degrees and about 30 degrees relative a longitudinal axis of the stent.

15. The stent of claim 1, wherein the body has flared ends at a distal end and proximal end of the body with flare angles between 15 degrees and 30 degrees relative a longitudinal axis of the stent.

16. The stent of claim 1, wherein the first portion is a tighter braid than the second portion.

17. A stent, comprising: a body formed of a braided nitinol wire material woven to define a lumen having a longitudinal axis, wherein the body comprises: a proximal section having a first braid density configured to exert a first radial force against a vessel wall,Docket No. TERUM.0003.WO a distal section having a second braid density, lower than the first braid density, configured to exert a second, lower radial force against the vessel wall, a transition zone between the proximal section and the distal section configured to gradually change the braid density to reduce stress concentrations within the vessel, and flared ends at both proximal and distal ends of the body angled outwardly relative to the longitudinal axis to inhibit migration after deployment.

18. The stent of claim 17, wherein the transition zone comprises a continuously varying braid pitch that changes from a first pitch in the proximal section to a second, larger pitch in the distal section to smooth the radial force gradient along the longitudinal axis.

19. The stent of claim 17, wherein the proximal section has a higher wire angle relative to the longitudinal axis than the distal section, the higher wire angle being configured to increase radial stiffness and enhance vessel scaffolding in the proximal section.

20. A stent, comprising: support means formed of braided wire material for maintaining patency of a lumen in a vessel, means for exerting a first radial force on a proximal portion of the vessel, means for exerting a second, lower radial force on a distal portion of the vessel, means for gradually transitioning between the first radial force and the second radial force to reduce localized vessel wall stress, and means for anchoring the stent within the vessel lumen to inhibit migration after deployment, the anchoring means comprising outwardly flared end portions of the support means.

21. A stent, comprising: a first structural wire woven into a mesh defining a lumen of a given diameter along a longitudinal axis thereof, the mesh having a first pitch between windings of the first structural wire in a first section along the longitudinal axis and a second pitch between the windings of the first structural wire, different than the first pitch, in a second section along the longitudinal axis.Docket No. TERUM.0003.WO22. The stent of claim 21, further comprising: a second structural wire included in the mesh, the second structural wire having a different wire diameter than the first structural wire.

23. The stent of claim 22, wherein the second structural wire is included in the first section and the second section, and has a third pitch in the first section and a fourth pitch in the second section.

24. The stent of claim 22, wherein at least one of the first structural wire and the second structural wire defines a plurality of loops internal to the lumen of the mesh that form an internal mesh in which each loop of the plurality of loops at least partially overlaps one other loop of the plurality of loops to restrict a flowpath from a first end of the lumen to a second end of the lumen to be less than the given diameter.

25. The stent of claim 22 wherein the first structural wire and the second structural wire are connected via a plurality of weld joints that maintain a relative position of the first structural wire to the second structural wire when the mesh is compressed along the longitudinal axis.

26. The stent of claim 21, wherein the first structural wire defines a plurality of loops internal to the lumen of the mesh that form an internal mesh in which each loop of the plurality of loops at least partially overlaps one other loop of the plurality of loops to restrict a flowpath from a first end of the lumen to a second end of the lumen to be less than the given diameter.

27. A stent, comprising: a first structural wire of a first wire diameter; and a second structural wire of a second wire diameter, different than the first wire diameter, wherein the first structural wire and the second structural wire are woven into a mesh defining a lumen of a given diameter along a longitudinal axis thereof.

28. The stent of claim 27, wherein the mesh has a first pitch between first windings of the first structural wire in a first section along the longitudinal axis and a second pitch between theDocket No. TERUM.0003.WO first windings of the first structural wire in a second section along the longitudinal axis, a third pitch between second windings of the second structural wire in the first section and a fourth pitch between the second windings of the second structural wire in the second section along the longitudinal axis, wherein at least one of the first pitch and the second pitch are different from one another; or the third pitch and the fourth pitch are different from one another.

29. The stent of claim 27, wherein at least one of first structural wire and the second structural wire defines a plurality of loops internal to the lumen of the mesh that forms an internal mesh by each at least partially overlapping one other loop of the plurality of loops to restrict a flowpath from a first end of the lumen to a second end of the lumen to be less than the given diameter.

30. The stent of claim 27, wherein the first structural wire and the second structural wire are connected via a plurality of weld joints that maintain a relative position of the first structural wire to the second structural wire when the mesh is compressed along the longitudinal axis.

31. A stent, comprising: a first structural wire woven into a mesh defining a lumen of a given diameter along a longitudinal axis thereof, wherein the first structural wire defines a plurality of loops internal to the lumen that form an internal mesh by each at least partially overlapping one other loop of the plurality of loops to restrict a flowpath from a first end of the lumen to a second end of the lumen to be less than the given diameter.

32. The stent of claim 31, further comprising: a second structural wire included in the mesh, the second structural wire having a different wire diameter than the first structural wire.

33. The stent of claim 32, wherein the second structural wire defines a plurality of loops internal to the lumen of the mesh that form the internal mesh in which each loop of the pluralityDocket No. TERUM.0003.WO of loops at least partially overlaps one other loop of the plurality of loops to restrict a flowpath from the first end of the lumen to the second end of the lumen to be less than the given diameter.

34. The stent of claim 32, wherein the first structural wire and the second structural wire are connected via a plurality of weld joints that maintain a relative position of the first structural wire to the second structural wire when the mesh is compressed along the longitudinal axis.

35. The stent of claim 32, wherein the mesh has a first pitch between first windings of the first structural wire in a first section along the longitudinal axis and a second pitch between the first windings of the first structural wire in a second section along the longitudinal axis, a third pitch between second windings of the second structural wire in the first section and a fourth pitch between the second windings of the second structural wire in the second section along the longitudinal axis, wherein at least one of: the first pitch and the second pitch are different from one another; or the third pitch and the fourth pitch are different from one another.

36. The stent of claim 31, wherein the mesh having a first pitch between windings of the first structural wire in a first section along the longitudinal axis and a second pitch between the windings of the first structural wire, different than the first pitch, in a second section along the longitudinal axis.

37. A stent, comprising: a support means woven to define a lumen of a given diameter along a longitudinal axis thereof, the support means defining at least one of:(i) a first section and a second section along the longitudinal axis of a mesh in which the support means is woven with differing pitches between windings thereof;(ii) an overlapping section in which a first structural wire of a first wire diameter and a second structural wire of a second wire diameter, different than the first wire diameter, are woven separately from one another to occupy the overlapping section of the lumen along the longitudinal axis thereof; andDocket No. TERUM.0003.WO(iii) an internal mesh formed via a plurality of internal loops of the support means that are defined internally to the lumen, wherein each loop of the plurality of loops at least partially overlaps at least one other loop of the plurality of loops to restrict a flowpath from a first end of the lumen to a second end of the lumen to be less than the given diameter.

38. The stent of claim 37, wherein the overlapping section corresponds to at least one of the first section and the second section.

39. The stent of claim 37, wherein the internal mesh is disposed at least within one of the first section and the second section.

40. The stent of claim 37, wherein the first structural wire and the second structural wire are connected via a plurality of weld joints that maintain a relative position of the first structural wire to the second structural wire when the mesh is compressed along the longitudinal axis.

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