Single layer flow diverter stent with add-on loops

Abstract

A stent includes a mesh having a proximal end and a distal end. The stent also includes a set of proximal end loops forming a single layer with the mesh. Each proximal end loop is separate from the mesh. Each proximal end loop has a proximal-end-loop coupling portion coupled to the mesh and a proximal-end-loop loop portion extending proximally beyond the proximal end of the mesh. In a first configuration, the mesh has an axial length and each proximal-end-loop coupling portion extends along the mesh for less than the axial length of the mesh. In a second configuration, the stent is a single-layer stent, and each proximal-end-loop coupling portion extends along an entire length of the mesh.

Description

SINGLE LAYER FLOW DIVERTER STENT WITH ADD-ON LOOPSCROSS REFERENCE TO RELATED APPLICATION

[0001] This application claims the benefit of U.S. Provisional Application Serial No. 63 / 566,766, entitled “STENT WITH MULTIPLE TUBULAR PORTIONS” and filed March 18, 2024, which is expressly incorporated by reference herein in its entirety.TECHNICAL FIELD

[0002] The present disclosure relates generally to vascular devices and, more particularly, to neurovascular stents with connecting wires.BACKGROUND OF THE INVENTION

[0003] Vascular devices such as stents and stent-grafts are used for various purposes in the vasculature. A non-exhaustive list includes maintaining vessel patency by propping open diseased or occluded vessels to restore blood flow, diverting blood away from vulnerable areas such as aneurysms, and retaining embolic material at a treatment site to promote localized occlusion. Aneurysm embolization, in particular, involves deploying embolic materials, such as detachable coils, within the aneurysm sac to induce thrombosis and prevent rupture.

[0004] Flow-diverting stents, a specialized subclass of vascular stents, are designed to treat aneurysms by reducing blood flow into the aneurysm sac while preserving normal circulation in adjacent vessels. These stents are placed across the neck of the aneurysm, facilitating endothelial growth over time, which ultimately leads to aneurysm occlusion and the restoration of normal hemodynamics.

[0005] In addition to flow diversion, an intraluminal support stent, another specialized subclass of vascular stents, can serve as a structural scaffold for aneurysm embolization procedures. For example, the stent can be deployed within the vessel to help retain embolic material, such as detachable coils, within the aneurysm sac. By providing structural support, the stent ensures proper coil retention while maintaining vessel patency, thereby reducing the risk of aneurysm rupture.BRIEF SUMMARY

[0006] The following presents a simplified summary of one or more aspects in order to provide a basic understanding of such aspects. This summary is not an extensive overview of all contemplated aspects. This summary neither identifies key or critical elements of all aspects nor delineates the scope of any or all aspects. Its sole purpose is to present some concepts of one or more aspects in a simplified form as a prelude to the more detailed description that is presented later.

[0007] In an aspect of the disclosure, a stent is provided. The stent may include a mesh having a proximal end and a distal end. The stent may also include a set of proximal end loops forming a single layer with the mesh, each proximal end loop being separate from the mesh, each proximal end loop having a proximal-end-loop coupling portion coupled to the mesh and a proximal-end-loop loop portion extending proximally beyond the proximal end of the mesh.

[0008] In an aspect of the disclosure, a method of manufacturing a stent is provided. The method may include forming a mesh having a proximal end and a distal end. The method may also include coupling a set of proximal end loops to the mesh, the set of proximal end loops forming a single layer with the mesh, each proximal end loop being separate from the mesh, each proximal end loop having a proximal-end-loop coupling portion coupled to the mesh and a proximal-end-loop loop portion extending proximally beyond the proximal end of the mesh.

[0009] In some aspects, the techniques described herein relate to a stent, including: a first portion including a first plurality of wires and including a first end and a second end; a second portion including a second plurality of wires; wherein the second portion partially overlaps with the first portion along a first overlapping region and wherein at least a middle region of the first portion includes a non-overlapping region; and, a first attachment mechanism between the first portion and the second portion.

[0010] In some aspects, the techniques described herein relate to a stent, wherein the first portion is tubular, and the second portion is tubular.

[0011] In some aspects, the techniques described herein relate to a stent, wherein the first plurality of wires is braided, and the second plurality of wires is braided.

[0012] In some aspects, the techniques described herein relate to a stent, wherein a first free end of the second portion radially increases in diameter away from a longitudinal axis of the first portion when the stent is in an expanded configuration.

[0013] In some aspects, the techniques described herein relate to a stent, wherein the first overlapping region is within an inclusive range of about 5% to about 30% of an axial length of the first portion.

[0014] In some aspects, the techniques described herein relate to a stent, wherein the first overlapping region is within an inclusive range of about 0.5 cm to about 5 cm from the first end.

[0015] In some aspects, the techniques described herein relate to a stent, wherein the second plurality of wires has a diameter within an inclusive range of about 0.0001 inch to 0.001 inch; and wherein the first plurality of wires is within an inclusive range of about 0.0005 inch to about 0.1 inch.

[0016] In some aspects, the techniques described herein relate to a stent, wherein the first attachment mechanism includes; (i) a weld; (ii) a wire coil that wraps around one of the first plurality of braided wires and one of the second plurality of braided wires; (iii) an adhesive; or (iv) interleaving wire between at least some of the first plurality of braided wires and at least some of the second plurality of braided wires.

[0017] In some aspects, the techniques described herein relate to a stent, wherein the second portion is partially positioned around an exterior side of the first portion.

[0018] In some aspects, the techniques described herein relate to a stent, wherein the second portion is partially positioned within an interior lumen the first portion.

[0019] In some aspects, the techniques described herein relate to a stent, wherein the first plurality of braided wires of the first portion have a smaller diameter relative to the second plurality of braided wires of the second portion.

[0020] In some aspects, the techniques described herein relate to a stent, wherein the first portion has a porosity within an inclusive range of about 0.001 inch to 0.010 inch and wherein the second portion has a porosity of about 0.1 inch or higher.

[0021] In some aspects, the techniques described herein relate to a stent, wherein the first plurality of braided wires include drawn filled tubing wires, nitinol wires, or a combination of both drawing filled tubing wires and nitinol wires.

[0022] In some aspects, the techniques described herein relate to a stent, wherein the second portion is flared at an angle relative to a longitudinal axis of the second portion of about 15 and 60 degrees relative to the longitudinal axis of the first portion when the stent is in an expanded configuration.

[0023] In some aspects, the techniques described herein relate to a stent, further including a third portion including a third plurality of braided wires; and a second attachment mechanism connecting the first portion and the third portion along a second overlapping region at the second end; wherein the third portion radially increases in diameter away from a longitudinal axis of the first portion when the stent is in an expanded configuration.

[0024] In some aspects, the techniques described herein relate to a stent, wherein the second overlapping region is within an inclusive range of about 0.5 cm to about 5 cm from the second tubular end.

[0025] In some aspects, the techniques described herein relate to a stent, wherein the third portion is partially positioned around an outside of the first portion or is partially positioned within the first portion.

[0026] In some aspects, the techniques described herein relate to a stent, wherein the second portion is partially positioned around an outside of the first portion or is partially positioned within the first portion.

[0027] In some aspects, the techniques described herein relate to a stent, wherein the first plurality of braided wires have a smaller diameter relative to the second plurality of braided wires and relative to the third plurality of braided wires.

[0028] In some aspects, the techniques described herein relate to a stent, including: a first plurality of wires braided into a first tubular portion; a second plurality of wires braided into a second tubular portion; wherein the second tubular portion partially overlaps a first end region of the first tubular portion without overlapping a middle region of the first tubular portion; a third plurality of wires braided into a third tubular portion; wherein the third tubular portion partially overlaps a second end region of the first tubular portion without overlapping the middle region of the first tubular portion; and, a first attachment mechanism connecting the first tubular portion and the second tubular portion, and the first tubular portion and the third tubular portion; wherein the second plurality of wires and the third plurality of wires include wires having a larger wire diameter than a smaller wire diameter of the wires of the first plurality of wires, and wherein the second tubular portion and the third tubular portion have a higher porosity than the first tubular portion.

[0029] In some aspects, the techniques described herein relate to a stent, wherein the first tubular portion has a porosity within an inclusive range of about 0.001 inch to 0.010 inch and wherein the second tubular portion has a porosity of about 0.1 inch or higher.

[0030] In some aspects, the techniques described herein relate to a stent, wherein the larger wire diameter of the second plurality of wires and the third plurality of wires is within an inclusive range of about 0.0001 inch to 0.001 inch; and wherein smaller wire diameter of the first plurality of wires is within an inclusive range of about 0.0005 inch to about 0.1 inch.

[0031] In some aspects, the techniques described herein relate to a stent, wherein the second tubular portion is partially positioned around an outside of the first tubular portion or is partially positioned within the first tubular portion; and wherein the third tubular portion is partially positioned around an outside of the first tubular portion or is partially positioned within the first tubular portion.

[0032] In some aspects, the techniques described herein relate to a stent, including: a first tubular portion means for diverting blood flow; a second tubular portion means for anchoring the first tubular portion means; wherein the second tubular portion means partially overlaps a first end region of the first tubular portion means; and, a third tubular portion means for anchoring the first tubular portion means; wherein the third tubular portion means partially overlaps a second end region of the first tubular portion means.

[0033] In some aspects, the techniques described herein relate to a method for creating a stent, including: braiding a first plurality of wires into a first tubular portion; braiding a second plurality of wires braided into a second tubular portion; braiding a third plurality of wires braided into a third tubular portion; and, attaching the second tubular portion so that it partially overlaps a first end region of the first tubular portion without overlapping a middle region of the first tubular portion; and, attaching the third tubular portion so that it partially overlaps a second end region of the first tubular portion without overlapping the middle region of the first tubular portion.

[0034] To the accomplishment of the foregoing and related ends, the one or more aspects may include the features hereinafter fully described and particularly pointed out in the claims. The following description and the drawings set forth in detail certain illustrative features of the one or more aspects. These features are indicative, however,of but a few of the various ways in which the principles of various aspects may be employed.BRIEF DESCRIPTION OF THE DRAWINGS

[0035] FIG. 1 is a diagram illustrating a side view of a stent positioned across an example target site, in accordance with various aspects of the present disclosure.

[0036] FIG. 2 is a diagram illustrating an example of a delivery device for delivering a stent, in accordance with various aspects of the present disclosure.

[0037] FIG. 3 is a diagram illustrating an example of a stent partially deployed from a delivery device, in accordance with various aspects of the present disclosure.

[0038] FIG. 4A is a diagram illustrating a side view of an example stent showing one or more proximal end-loops coupled to the mesh portion of the stent in an expanded or benchtop configuration, in accordance with various aspects of the present disclosure.

[0039] FIG. 4B is a diagram illustrating a side view of an example stent showing one or more proximal end loops and one or more distal end loops coupled to the mesh portion of the stent in an expanded or benchtop configuration, in accordance with various aspects of the present disclosure.

[0040] FIG. 4C illustrates a proximal-side view of the example stent, in accordance with various aspects of the present disclosure.

[0041] FIG. 5 is a diagram illustrating a side view of an example stent showing the proximal end loop coupled to the mesh portion of the stent in an expanded or benchtop configuration, in accordance with various aspects of the present disclosure.

[0042] FIG. 6 is a diagram illustrating an example offset of fixed points on different proximal end loops, in accordance with various aspects of the present disclosure.

[0043] FIG. 7 is a diagram illustrating an example stent within a delivery device in a compressed configuration, in accordance with various aspects of the present disclosure.

[0044] FIG. 8 is a diagram illustrating an example stent partially deployed from the delivery device, in accordance with various aspects of the present disclosure.

[0045] FIG. 9 is a diagram illustrating an example stent with one or more end loop wires extending along the full axial length of the mesh, in accordance with various aspects of the present disclosure.

[0046] FIG. 10 is a diagram illustrating an example of the stent partially deployed from the delivery device, in accordance with various aspects of the present disclosure.

[0047] FIG. 11 is a flow diagram illustrating an example of a method for manufacturing the stent, in accordance with various aspects of the present disclosure.

[0048] FIG. 12 illustrates a side view of an example stent, in accordance with various aspects of the present disclosure.

[0049] FIG. 13 illustrates a cross-sectional side view of the stent of FIG. 12, in accordance with various aspects of the present disclosure.

[0050] FIG. 14 illustrates a cross-sectional side view of a stent with attachment mechanisms, in accordance with various aspects of the present disclosure

[0051] FIG. 15 illustrates a cross-sectional side view of a stent with another example attachment mechanisms, in accordance with various aspects of the present disclosure.

[0052] FIG. 16 illustrates a cross-sectional side view of a stent with another attachment mechanisms, in accordance with various aspects of the present disclosure.

[0053] FIG. 17 illustrates an enlarged perspective view of an end of a stent with radiopaque markers, in accordance with various aspects of the present disclosure.

[0054] FIG. 18 illustrates an enlarged perspective view of an end of a stent with radiopaque markers, in accordance with various aspects of the present disclosure.

[0055] FIG. 19 illustrates a side view of another example stent, in accordance with various aspects of the present disclosure.

[0056] FIG. 20 illustrates a cross-sectional side view of the stent of FIG. 19, in accordance with various aspects of the present disclosure.

[0057] FIG. 21 illustrates a cross-section side view of an example stent, in accordance with various aspects of the present disclosure.

[0058] FIG. 22 illustrates a cross-section side view of an example stent according to one example, in accordance with various aspects of the present disclosure.DETAILED DESCRIPTION

[0059] Various aspects of the present disclosure relate generally to stent design, and more specifically to systems and methods for enhancing stent deliverability, stability, and flow diversion performance through the integration of add-on loops (also referred as “attachment wires,” or “end loops” or “flared ends”)) in a single-layer flow diverter stent. In some aspects, the stent may include one or more proximal end loops, whichmay be symmetrically or asymmetrically positioned around a circumference of the stent body (e.g., a wire mesh) and may be coupled to the mesh by a weave through or fixed to the mesh. The incorporation of the proximal end loops provides a more controlled and predictable deployment process, allowing end users to employ existing delivery techniques similar to those used with conventional flow diverters. The high- density machine-braided mesh (PPI > 100) increases the metal surface area, thereby improving blood flow diversion and promoting aneurysm occlusion. Additionally, by allowing the add-on loops to be pre-shaped or wound into the braid body of the stent (e.g., the mesh portion of the stent), the stent maintains a flexible, single-layer structure within the middle portion, while ensuring secure anchoring within the vessel. The loop wires of the add-on loops and braid wires of the stent body may be configured parallel to each other, optimizing alignment and integration within the mesh. Furthermore, offset weld or joint locations for securing the loop legs of the addon loops prevent stress concentration, thereby reducing mechanical weaknesses and enhancing stent durability. The use of hybrid material configurations for the mesh, such as drawn-filled tube (DFT), Nitinol, or a combination of materials, provides customizable mechanical properties to further improve deployment characteristics and performance.

[0060] Additionally, compared with multi-layer stents with end loops, the single-layer stent with add-on loops may have a thinner middle portion, as it avoids the additional material bulk from multiple overlapping layers. This may result in improved deliverability, reduced friction in the compressed state within the delivery catheter, and easier navigation through tortuous anatomy. By optimizing the loop attachment and stent structure, the disclosed design enhances stent navigability, stability, and flow diversion efficiency, improving treatment outcomes in neurovascular interventions.

[0061] Particular aspects of the subject matter described in this disclosure can be implemented to achieve one or more of the following advantages. For example, by incorporating add-on loops at the proximal (and distal ends in some examples) of a flow diverter stent, the described techniques enhance stent deliverability and deployment control, allowing for a more predictable and stable positioning within the vessel.

[0062] While the embodiments described in this specification may be generally referred to as stents, the teachings herein are applicable to a wide range of different vascular devices such as grafts, valves, anchoring mechanism, or any other vascular medical device that may include at least one braided portion. Hence, the term stent should be understood to be inclusive of all of these devices.

[0063] The present specification also describes several different features of stents, such as different wire materials of different layers, different layer arrangements, different layer lengths, different connections between layers, different add-on loops coupling portion lengths, and other features. Any of these aspects can be used and interchanged with each other. Hence, while every permutation of feature is not specifically described, such combinations are specifically contemplated as being part of the present invention and supported by the specification.

[0064] The terms distal or distally generally refer to a direction or area towards an end of a device within a patient (e.g., away from a physician / clinician), while the terms proximal or proximally refer to a direction or area toward an end of a device that remains outside of a patient (e.g., toward or closer to a physician / clinician or handle / hub of a device).

[0065] The terminology used in this disclosure should be interpreted in a permissive manner and is not intended to be limiting. In the drawings, like numbers refer to like elements. Unless otherwise noted, all of the accompanying drawings are not to scale. Unless otherwise noted, the term “about” is defined to mean plus-or-minus 5% of a stated value.

[0066] The present disclosure uses the terms portion, layer, segment, or region of a stent interchangeably. These terms may generally refer to a discrete braided component of a stent that may be in the form of a tubular shape and may be attached to another discrete braided component of a stent.

[0067] Numerical ranges discussed in this specification should be interpreted as both inclusive numerical ranges and as covering / disclosing a plurality of numbers within the ranges. Specifically, a range should be considered to recite numbers that increment by two decimal places (hundredths) for the purposes of support in the claims (e.g., 0.01, 0.02, 0.03, etc.). Any of these incremented numbers from a range should be understood to have significance and importance in the context of the present specification.

[0068] Aspects of example stents are generally disclosed below and are intended to be described in an inclusive, holistic manner such that any of these aspects are interchangeable or may be used together in any combination or permutation. The figures describe specific example combinations of some of these aspects but should not be interpreted to limit the present disclosure to only those combinations.

[0069] Generally, the present disclosure includes stents that may have multiple layers that are fixed to each other and that only partially overlap with each other (e.g., tubular layers). At least two of these layers may have different physical properties than the other layer, which may allow the stent to demonstrate improved performance that may not otherwise be easily achieved with a single layer stent alone. Note that the terms stent “layers” and “portions” are generally used synonymously in this specification.

[0070] The example stents may have a radially compressed configuration and a radially expanded configuration. In their radially expanded configuration, they may have a generally tubular shape with a lumen extending therethrough.

[0071] The detailed description set forth below in connection with the drawings describes various configurations and does not represent the only configurations in which the concepts described herein may be practiced. The detailed description includes specific details for the purpose of providing a thorough understanding of various concepts. However, these concepts may be practiced without these specific details. In some instances, well known structures and components are shown in block diagram form in order to avoid obscuring such concepts.

[0072] FIG. 1 is a diagram 100 illustrating a side view of a stent 110 in an expanded configuration, positioned across an example target site 105, in accordance with various aspects of the present disclosure. As shown in FIG. 1, an example target site (also referred as “treatment site”) 105 may include an aneurysm 102 along a sidewall of a vessel 104. In some aspects, an example stent 110 may be a flow diverting stent used for treating aneurysms which can reduce blood flow into the aneurysm sac while preserving normal circulation in adjacent vessels. For example, the stent 110 may be placed across the neck of the aneurysm 102, facilitating endothelial growth over time, which ultimately leads to aneurysm occlusion and the restoration of normal hemodynamics. In some examples, a flow-diverting stent may have a higher porosity compared to an intraluminal support stent, allowing for greater reduction in blood flow into the aneurysm sac.

[0073] Additionally or alternatively, a stent 110 may be an intraluminal support stent to serve as structural scaffolds for aneurysm embolization procedures for treating the aneurysms 102. For example, in stent-assisted coiling, when an intraluminal support stent is delivered to the target site 105 (e.g., aneurysm neck), embolic materials such as small coils (also referred as “microcoils” or “embolic coil”) may be delivered to the aneurysm 102 via a catheter. In some aspects, the catheter navigates to the aneurysm through the strut of a stent 110 and is positioned within the aneurysm for coil delivery. Compared with flow diverting stents, intraluminal support stents may be composed of relatively thicker wires to help anchor their position in the vessel and therefore also tend to be relatively porous (e.g., larger pore openings) in their construction.

[0074] It is contemplated that the stent 110 depicted in the figures is for illustrative purposes only. A variety of stent embodiments with different porosity levels and / or number of layers may be utilized depending on the desired therapeutic effects.

[0075] FIG. 2 is a diagram 200 illustrating an example delivery device 210 for deploying a stent 110 in a compressed configuration, in accordance with various aspects of the present disclosure. In some aspects, when deploying the stent 110, a guidewire (not shown) may be advanced along vessel of a patient so that the distal end of the guidewire is positioned at or near a target site (e.g., target site 105 shown in FIG. 1). A guide catheter (not shown) configured for delivering a delivery device 210 may be advanced over the guidewire so that the distal end of the guide catheter is positioned at or near the target site. The guidewire may then be removed. The stent 110 may be delivered to the target site via the delivery device 210 in the compressed configuration. In some aspects, the stent is deployed by retracting the delivery catheter 250 while the pusher (e.g., stent delivery wire) is held in place. This allows the stent to gradually expand against the vessel wall while it exits the distal end of a delivery catheter 250.

[0076] For example, the delivery device 210 may be advanced through the guide catheter to deliver the stent 110 to the target site. In some aspects, the delivery device 210 may include a delivery catheter (also referred as “microcatheter”) 250 having an inner lumen 255 (e.g., an elongated lumen, passage, or channel) between its proximal end 250p and distal end 250d. The delivery device 210 may also include a pusher 252 that is longitudinally movable within the inner lumen 255 of the delivery catheter 250. Insome aspects, the pusher 252 may include a mechanism on or near its distal end that can engage the stent 110 and allow the stent 110 to be navigated in the delivery catheter 250 (e.g., pushed or retracted back) by the pusher 252.

[0077] For example, the pusher 252 may include a pair of raised protrusions 270a and 270b configured to engage the stent 110 to distally push and / or retract back into the delivery catheter 250. In some aspects, the raised protrusion 270a and 270b may be made of a radiopaque material such as platinum, palladium, or tantalum, in a form of radiopaque cylinders, star shapes, marker band, or other similar shapes, to aid in visualization of the connection junction.

[0078] As will be discussed and shown in detail below, the stent 110 may include a plurality of end loops 226 at the proximal end and / or distal end of the stent 110, for instance 2- 10 end loops (e.g., 2-10 proximal end loops 226a and / or 2-10 distal end loops 226b). The end loops 226 may help stabilize the stent 110 in the vessel (e.g., the vessel 104 in FIG. 1) and, as will be explained later, can provide a mechanism to connect the stent 110 to a pusher element (e.g., pusher 252) of the delivery device 210, which may facilitate navigation and delivery of the stent 110. For example, the end loops 226 may include radiopaque elements (e.g., marker bands 228) coupled to (e.g., wrapped around) portions of the end loops 226. The marker bands 228 may help visualize the ends of the stent 110 during the stent delivery process and, as will be explained later, can further enable connection to the pusher 252. In some examples, the marker bands 228 may be a helical wrap, a marker wire coil, a sleeve, a tube, or a similar structure formed from a radiopaque material, such as DFT or tantalum.

[0079] For example, the proximal end loops 226a of the stent 110 (e.g., end loops at the proximal end of the stent 110) may include marker bands (also referred as “marker coils”) 228. The proximal end loops 226a may be placed within a marker band region 275 of the pusher 252, defined by the raised protrusions 270a and 270b (e.g., between the raised protrusions 270a and 270b), where the marker bands 228 of the stent 110 may help constrain the proximal end loops 226a of the stent 110 within the marker band region 275, e.g., the marker bands 228 may be constrained between the raised protrusions 270a and 270b of the pusher 252. In some aspects, the distal raised protrusion 270b may be sized to fit within openings of the stent 110, such as the proximal end loops 226a, while the proximal raised protrusion 270a may be sized andpositioned to about a proximal end of the stent 110. Accordingly, the pusher 252 may be mechanically connected to the stent 110.

[0080] In some aspects, all or only some of the proximal end loops 226a of the stent 110 are gripped by the pusher 252. For example, all of the plurality of proximal end loops 226a may be gripped between the raised protrusions 270a and 270b of the pusher 252. Additionally or alternatively, only one or some of the plurality of proximal end loops 226a may be gripped between the raised protrusions 270a and 270b of the pusher 252.

[0081] In some aspects, the proximal end loops 226a may not all have the same length. For example, some proximal end loops 226a may be larger, while others are smaller, forming an alternating pattern around the periphery of the stent’s 110 proximal end (e.g., one long loop adjacent to one short loop). In such configurations, only the larger / longer proximal end loops may be gripped between the raised protrusions 270a and 270b of the pusher 252.

[0082] It is understood that the engagement mechanism between the stent 110 and the pusher 252 described herein is provided for illustrative purposes. Various alternative pushers and stent engagement mechanisms may also be used.

[0083] FIG. 3 is a diagram 300 illustrating an example of the delivery device 210 for delivering a stent 110, in accordance with various aspects of the present disclosure. The delivery device 210 configured to deliver the stent 110 to a target site (e.g., the target site 105 in FIG. 1) as discussed above with respect to FIG. 2. In some aspects, the stent 110 may be advanced through the inner lumen 255 of the delivery catheter 250 to a target site (e.g., the target site 105 in FIG. 1), e.g., at a location distally beyond or at the distal end of the target site. For example, the pusher 252 may be held in place while the delivery catheter 250 is proximally withdrawn to expose a distal end 1 lOd of the stent 110, which may radially expand to engage and anchor to the vessel (e.g., the vessel 104 in FIG. 1). For example, the pusher 252 may be advanced distally by a physician (e.g., the operator of the delivery device 210) and the delivery catheter 250 may be retracted proximally to cause the stent 110 to exit from the distal end of the delivery catheter 250.

[0084] In some examples, a core wire 253, as shown in FIG. 3, may be used to facilitate the advancement and positioning of the delivery catheter 250 within the vasculature. The core wire 253 may be part of the pusher 252. The core wire 253 may be composed of a flexible core material, such as nitinol or stainless steel, and may include ahydrophilic or polytetrafluoroethylene (PTFE) coating to improve trackability and reduce friction during navigation through tortuous vessels. For example, when deploying the stent 110, the core wire 253 may be inserted first and advanced through a guide catheter (not shown) to establish a stable pathway for the delivery catheter 250 and / or the stent 110. In some examples, once the distal end of the core wire253 reaches the target site, the delivery catheter 250 and / or the stent 110 may be advanced over the core wire253, ensuring precise positioning of the stent 110 before deployment.

[0085] Various aspects of the present disclosure relate generally to stent design, and more specifically to systems and methods for improving stent deliverability, deployment control, and flow diversion efficiency by integrating add-on loops into a single-layer flow diverter stent. In some aspects, the disclosed stent may incorporate proximal and / or distal end loops, which are woven into and / or fixed to the wire mesh to facilitate precise positioning and anchoring within the vessel. Compared to conventional multi-layer stents that include end loop configurations, the disclosed single-layer flow diverter reduces overall stent thickness, particularly in the middle portion, thereby minimizing bulk and enhancing flexibility. The reduced diameter of the middle portion allows for a higher-density mesh (e.g., a high-density machine- braided mesh with PPI > 100), which increases the metal surface area, thereby improving blood flow diversion for aneurysm occlusion while maintaining a thinner, more conformable structure. Additionally, the incorporation of offset weld or joint locations for securing the loop legs prevents stress concentration, reducing mechanical weaknesses and improving stent durability.

[0086] The optimized loop configuration also ensures less friction during delivery, as the single-layer structure avoids the excessive material buildup commonly seen in multilayered stents, thereby reducing contact resistance within the delivery catheter (e.g., delivery catheter 250 in FIGs. 2 and / or 3). Furthermore, the parallel alignment of loop wires with braid wires enhances structural integrity and deployment accuracy while maintaining compatibility with existing delivery systems. By improving stent flexibility, deliverability, and anchoring, the disclosed design may enable smoother navigation through tortuous vascular pathways while maintaining effective flow diversion capabilities, ultimately leading to improved treatment outcomes.

[0087] FIG. 4A is a diagram 400 illustrating a side view of a stent 410 in an expanded or benchtop configuration, in accordance with various aspects of the present disclosure. The stent 410 may correspond to stent 110 in FIGs. 1-3. In some aspects, the stent 410 may include a mesh 401 having a proximal end 401p and a distal end 401d, forming a cylindrical or tubular-shaped body of the stent 410, and one or more proximal end loops 420 at the proximal end 401p. The mesh 401 and the one or more proximal end loops 420 may form a single-layer structure within the stent 410. The proximal end loops 420 may function similarly to the end loops 226 in FIGs. 2 and 3.

[0088] In some aspects, each proximal end loop 420 is separate and extends from the mesh 401. For example, each proximal end loop 420 may include a proximal-end-loop coupling portion 422, which is attached to the mesh 401, and a proximal-end-loop loop portion 423, which extends proximally beyond the proximal end 401p.

[0089] As discussed above, to reduce the diameter of the middle portion of the stent 410, each proximal-end-loop coupling portion 422 may extend less than the entire axial length of the mesh 401, measured along the longitudinal axis 402. For example, the proximal-end-loop coupling portion 422 may extend less than half, one-third, or one- fourth of the axial length of the mesh 401, depending on the desired performance. By maintaining a single-layer structure with add-on loops (e.g., the proximal end loop 420), the stent 410 minimizes bulk in the middle portion, enhancing flexibility and deliverability compared to multi-layer stents with integrated end loops.

[0090] In some aspects, the proximal end loops 420 may be interwoven through (e.g., coupled to by a weave) the mesh 401 and / or fixed to the mesh 401 via a weld, glue, coupling, helical wrap, or another securing method. In a first configuration, the proximal end loops 420 are coupled to the mesh through a weave. In a second configuration, the proximal end loops 420 are coupled to the mesh through one or more of a weld, glue, coupling, helical wrap, or other securing method. In a third configuration, the proximal end loops 420 are coupled to the mesh through both a weave and one or more of a weld, glue, coupling, helical wrap, or other securing method. In relation to the weave, as shown in FIG. 5 (diagram 500), the proximal-end-loop coupling portion 422 may be interwoven through the mesh 401 using an interweaving pattern, such as: 1. 1 : 1 - The proximal-end-loop coupling portion 422 passes under one wire 401a and then over one wire 401b,2. 1:2 - The proximal-end-loop coupling portion 422 passes under one wire and then passes over two adjacent wires 401b,3. 1 :3 - The proximal-end-loop coupling portion 422 passes under one wire and then over three adjacent wires 401b, and so on.

[0091] It is understood that the interweaving pattern may be defined as p x q, where p represents the number of wires over which the proximal-end-loop coupling portion 422 extends, and q represents the number of wires under which the proximal-end-loop coupling portion 422 extends, with the constraints 1 < p < 5 and 1 < q < 5. The interweaving configuration ensures secure attachment of the proximal end loops 420 to the mesh 401 while maintaining flexibility and structural integrity.

[0092] Referring back to FIG. 4A, in some aspects, each proximal end loop 420 may be formed from a single proximal loop wire 421, creating a continuous loop structure. In some embodiments, the proximal loop wire 421 may be composed of drawn-filled tube (DFT) or another suitable material. The proximal end loop 420 may include two wire legs 421a and 421b, which may have different configurations depending on performance requirements. For example, when fixed to the mesh 401, the two wire legs 421a and 421b may overlap with each other, be spaced apart with a gap, or align in contact without overlapping. The variations of the wire legs 421a and 421b allow for customized anchoring and flexibility in deployment.

[0093] As shown in FIG. 4 A, in some aspects, the DFT wires 10 may have an inner core 12 composed of a radiopaque material (e.g., tantalum) and an outer jacket 14 composed of a shape memory alloy (e.g., nitinol).

[0094] Additionally or alternatively, in some aspects, the proximal end loop 420 may be fixed (e.g., through a weld, glue, coupling, helical wrap) to the mesh 401 at multiple fixed points. To improve structural stability while avoiding stress concentration, the fixed points on different proximal end loops 420 may be offset in a radial direction. For example, FIG. 6 is a diagram 600 illustrating an example of radial offsets of the fixed points 425 on different proximal end loops 420, in accordance with various aspects of the present disclosure.

[0095] Specifically, each loop leg 421a or 421b may be secured to the mesh 401 via one or more welded attachment points (e.g., fixed points 425). The offset 426 (e.g., longitudinal and / or radial) between different proximal end loops 420 may be uniform or varied based on the desired structural and mechanical performance. In someaspects, by offsetting the welded attachment points, the mass caused by the weld joints are distributed along the mesh 401 rather than it being concentrated in a certain region which can affect the stent’s radial profile and its performance. It is understood that the offset 426 can be adjusted to any suitable value depending on the desired stability, anchoring, and deployment characteristics.

[0096] Referring back to FIG. 4A, in some aspects, one or more proximal end loops 420 may include a radiopaque element 428, which is coupled to at least one proximal end loop 420. In one example, the radiopaque element 428 may be a helical wrap, a marker wire coil, a sleeve, a tube, or a similar structure formed from a radiopaque material, such as DFT or tantalum. The radiopaque element 428 functions similarly to the marker bands 228 in FIGs. 2 and 3, enhancing fluoroscopic visibility during deployment and facilitating precise stent delivery and positioning.

[0097] In some aspects, the mesh 401 may be composed of one or more machine-braided interwoven wires, ensuring a consistent, high-density structure. In some aspects, the mesh 401 may have a density of at least 100 PPI, enhancing flow diversion efficiency. For example, in some non-limiting implementations, the PPI may be about 110 PPI, 120 PPI, 140 PPI, 150 PPI, or 165 PPI. Additionally, in some examples, the pores 460 of the mesh 401 may be sized within a range of about 0.2 mm to about 0.6 mm when the stent 410 is in its expanded configuration 406. In one example, the wire diameter of the wires forming the mesh 401 may be about 0.00085 inch and may be braided to achieve about 165 PPI.

[0098] In some aspects, the mesh 401 may be braided using multiple wires (e.g., 20, 24, or 36 wires braided together) composed of different materials, such as shape memory alloys like nitinol, to maintain a tubular shape. In some examples, the mesh 401 may be formed from a first wire and a second wire with different material compositions and / or structural configurations, allowing for optimized mechanical properties tailored to flexibility, durability, or deployment characteristics.

[0099] To enhance deliverability and flexibility, the mesh 401 and proximal end loops 420 may be formed from different material types and / or wires of different thicknesses. In some aspects, the proximal end loops 420 may be thicker than the wires forming the mesh 401, providing additional structural reinforcement to improve stent deployment and anchoring, while preserving the flexibility of the middle portion of the stent 410 to facilitate better vessel conformance.

[0100] For improved alignment, a portion of the proximal end loop 420 (e.g., the proximal- end-loop coupling portion 422) may extend approximately parallel to a wire of the mesh 401. For example, in a grid of pores 460 of the mesh 401, the proximal-end- loop coupling portion 422 extends approximately parallel to a strand 451 forming one of the pores 460.

[0101] In some aspects, when in the expanded configuration 406, the proximal end loops 420 may have a deflection angle 440 of about 40° to 70°, e.g., 50°, 55°, 50°, 65°, to name a few, relative to the longitudinal axis 402. The deflection angle 440 helps prevent fish-mouth deformation (e.g., if the angle is too small) and avoids the proximal end loops 420 flipping backward toward the mesh 401 (e.g., if the angle is too large). The deflection angle 440 will decrease when the stent 410 transitions to a compressed configuration 403, as discussed below.

[0102] In some aspects, the proximal end loops 420 may retract axially and expand radially as the stent 410 transitions from a compressed configuration to an expanded (deployed) configuration. For example, FIG. 7 is a diagram 700 illustrating the stent 410 in a compressed configuration, in accordance with various aspects of the present disclosure. When in a compressed configuration 403, the dimensions of the stent 410 can change longitudinally (e.g., length increases) and radially (e.g., diameter decreases). For example, as illustrated, in the compressed configuration 403, the proximal end loop 420 may extend out in a longitudinal direction (along the longitudinal axis 402) from the mesh 401 by a length approximately LPicwhich is defined by a distance from the proximal edge of the mesh 401 (e.g., when the mesh 401 being in the compressed configuration 403) to the end of the proximal end loop 420. In addition, the proximal end loop 420 may extend out in a radial direction from the mesh 401 (relative to the longitudinal axis 402) by a radius approximately Rpic which is defined by a distance from the longitudinal axis 402 to the end of the proximal end loop 420 (e.g., contacting the inner surface of the catheter 450). When the stent 410 is deployed from the catheter 450 and in an expanded configuration 406 (e.g., as shown in FIG. 4A and also shown in dash lines in FIG. 7), the dimensions of the stent 410 may change longitudinally (e.g., length decreases) and radially (e.g., diameter increases). For example, as shown in FIG. 7, when transitioned to the expanded configuration 406, the proximal end loop 420 may extend out in the longitudinal direction (along the longitudinal axis 402) from the mesh 401 by a lengthapproximately LPiewhich is defined by a distance from the proximal edge of the mesh in the expanded configuration (e.g., which may be distal to the proximal edge of the mesh in the compressed configuration) to the end of the proximal end loop 420. In addition, the proximal end loop 420 may extend out in the radial direction from the mesh 401 (relative to the longitudinal axis 402) by a radius approximately RPiewhich is defined by a distance from the longitudinal axis 402 to the end of the proximal loop 420. As such, LPic may be greater than LPieand RPiemay be greater than RPic. As shown in FIG. 7, when in the compressed configuration 403, the mesh 401 has an average radius of Rmc, where RPic = Rmc + A, where A > 0. In some aspects, A is approximately equal to an average spacing between an outer surface 40 lo of the mesh 401 and an inner lumen 455 of a catheter 450 (e.g., corresponding to delivery catheter 250 in FIGs. 2 and 3) compressing the stent 410. Therefore, in some aspects, when delivered through the catheter 450, the proximal end loop 420 becomes the primary contact point with the inner lumen 455, reducing friction (between mesh 401 and inner lumen 455) and minimizing potential damage to the inner surface of the catheter 450.

[0103] In some aspects, the stent 410 may further optionally include one or more distal end loops at the distal end 40 Id that are separate from the one or more proximal end loops 420 at proximal end 401p. For example, as shown in FIG. 4B (diagram 405), the stent 410 may further include one or more distal end loops 470 at the distal end 40 Id. The mesh 401 and the one or more distal end loops 470 may form a single-layer structure within the stent 410.

[0104] In some aspects, each distal end loops 470 is separate and extends from the mesh 401. For example, each distal end loops 470 may include a distal-end-loop coupling portion 472, which is attached to the mesh 401, and a distal-end-loop loop portion 473, which extends distally beyond the distal end 40 Id.

[0105] As discussed above, to reduce the diameter of the middle portion of the stent 410, each distal-end-loop coupling portion 472 may extend less than the entire axial length of the mesh 401, measured along the longitudinal axis 402. For example, the distal- end-loop coupling portion 472 may extend less than half, one-third, or one-fourth of the axial length of the mesh 401, depending on the desired performance.

[0106] In some aspects, the distal end loops 470 may be approximately symmetrically or asymmetrically distributed around the circumference of the distal end 40 Id, similar to the proximal end loops 420, as shown in FIG. 4C (will be discussed in detail below).

[0107] In some aspects, the distal end loops 470 may be interwoven through (e.g., coupled to by a weave) the mesh 401 and / or fixed to the mesh 401 via a weld, glue, coupling, helical wrap, or another securing method similar to the distal end loops 470, as shown in FIG. 5. In a first configuration, the distal end loops 470 are coupled to the mesh through a weave. In a second configuration, the distal end loops 470 are coupled to the mesh through one or more of a weld, glue, coupling, helical wrap, or other securing method. In a third configuration, the distal end loops 470 are coupled to the mesh through both a weave and one or more of a weld, glue, coupling, helical wrap, or other securing method. In relation to the weave, the distal-end-loop coupling portion 472 may be interwoven through the mesh 401 using an interweaving pattern, such as:1. 1 : 1, where the distal-end-loop coupling portion 472 passes under one wire 401a and then over one wire 401b,2. 1 :2, where the distal-end-loop coupling portion 472 passes under one wire and then passes over two wires 401b,3. 1 :3, where the distal-end-loop coupling portion 472 passes under one wire and then over three wires 401b, and so on.

[0108] It is understood that the interweaving pattern may be defined as p x q, where p represents the number of wires over which the distal-end-loop coupling portion 472 extends, and q represents the number of wires under which the distal-end-loop coupling portion 472 extends, with the constraints 1 < p < 5 and 1 < q < 5. The interweaving configuration ensures secure attachment of the distal end loops 470 to the mesh 401 while maintaining flexibility and structural integrity.

[0109] Referring back to FIG. 4B, in some aspects, similar to the proximal end loops 420, each distal end loops 470 may be formed from a single distal loop wire 471, creating a continuous loop structure. In some embodiments, the distal loop wire 471 may be composed of DFT or another suitable material. The distal end loops 470 may include two wire legs 471a and 471b, which may have different configurations depending on performance requirements. For example, when fixed to the mesh 401, the two wire legs 471a and 471b may overlap with each other, be spaced apart with a gap, or align in contact without overlapping. The variations of the wire legs 471a and 471b allow for customized anchoring and flexibility in deployment.

[0110] Additionally or alternatively, similar to the proximal end loops 420, the distal end loops 470 may, in some aspects, be fixed (e.g., through a weld, glue, coupling, helical wrap) to the mesh 401 at multiple fixed points. To enhance structural stability, the fixed points of different distal end loops 470 may be offset in the radial direction, similar to the proximal end loops 420, as shown in FIG. 6.

[0111] Referring back to FIG. 4B, in some aspects, one or more distal end loops 470 may include a radiopaque element 478, which is coupled to at least one distal end loops 470. In one example, the radiopaque element 478 may be a helical wrap formed of tantalum. The radiopaque element 478 functions similarly to the marker bands 228 in FIG. 2, enhancing fluoroscopic visibility during deployment and facilitating precise stent delivery and positioning.

[0112] To enhance deliverability and flexibility, the mesh 401 and the distal end loops 470 may be formed from different material types and / or wires of different thicknesses.

[0113] For improved alignment, a portion of the distal end loops 470 (e.g., the distal-end- loop coupling portion 472) may extend approximately parallel to a wire of the mesh 401, similar to the proximal end loops 420, as discussed with respect to FIG. 4A.

[0114] In some aspects, the distal end loops 470 may retract axially and expand radially as the stent 410 transitions from a compressed configuration to an expanded (deployed) configuration, similar to the proximal end loops 420, as shown in FIG. 7. When in a compressed configuration 403, the dimensions of the stent 410 can change longitudinally (e.g., length increases) and radially (e.g., diameter decreases). For example, in the compressed configuration 403, the distal end loop 470 may extend out in a longitudinal direction (along the longitudinal axis 402) from the mesh 401 by a length approximately Laic which is defined by a distance from the distal edge of the mesh (e.g., when the mesh 401 being in the compressed configuration 403) to the end of the proximal end loop 420. In addition, the distal end loop 470 may extend out in a radial direction from the mesh 401 (relative to the longitudinal axis 402) by a radius approximately Raic which is defined by a distance from the longitudinal axis 402 to the end of the distal end loop 470 (e.g., may or may not contact the inner surface of the catheter 450). When the stent 410 is deployed from the catheter 450 and in an expanded configuration 406 (e.g., as shown in FIG. 4A and also shown in dash lines in FIG. 7), the dimensions of the stent 410 may change longitudinally (e.g., length decreases) and radially (e.g., diameter increases). For example, similar to the proximalend loops 420 as shown in FIG. 7, when transitioned to the expanded configuration 406, the distal end loop 470 may extend out in the longitudinal direction (along the longitudinal axis 402) from the mesh 401 by a length approximately Laie which is defined by a distance from the distal edge of the mesh 401 in the expanded configuration (e.g., which may be distal to the proximal edge of the mesh in the compressed configuration) to the end of the distal end loop 470. In addition, the distal end loop 470 may extend out in the radial direction from the mesh 401 (relative to the longitudinal axis 402) by a radius approximately Raie which is defined by a distance from the longitudinal axis 402 to the end of the distal end loop 470. As such, Laic may be greater than Laie and Raie may be greater than Raic. Similar to the proximal end loops 420, as shown in FIG. 7, when in the compressed configuration 403, the mesh 401 has an average radius of Rmc, where Raic = Rmc + A, where A > 0. In some aspects, A is approximately equal to an average spacing between an outer surface of the mesh 401 and an inner lumen 455 of a catheter compressing the stent 410. Therefore, in some aspects, when delivered through catheter 450 (e.g., corresponding to delivery catheter 250 in FIGs. 2 and 3), the distal end loops 470 may also serve as primary contact points with the inner lumen 455, helping to reduce friction (between mesh 401 and inner lumen 455) and minimize potential damage to the inner surface of catheter 450.

[0115] In some aspects, when in the expanded configuration 406, the distal end loops 470 may have a deflection angle 490 of about 40° to 70°, e.g., 50°, 55°, 50°, 65°, to name a few, relative to the longitudinal axis 402, similar to the deflection angle 440 of the proximal end loop 420, as discussed above.

[0116] In some aspects, the mesh 401 may have a cylindrical or tubular-shaped body, and the proximal end loops 420 and / or the distal end loops 470 may be approximately symmetrically or asymmetrically distributed around the circumference of the proximal end 401p. For example, FIG. 4C is a diagram 407 illustrating a proximal- side view of the stent 410, in accordance with various aspects of the present disclosure. As shown in FIG. 4B, the mesh 401, when viewed from the proximal side, may have a circumference 404, along which the proximal end loops 420 and / or the distal end loops 470 are evenly or nearly evenly distributed. This balanced distribution helps ensure stable deployment and predictable expansion of the stent. In some aspects, each of the proximal end or the distal end of tubular body (e.g., the braidedtubular portion) of the stent 410 may have, for example, 3, 4, 5, 6, 7, 8, 9, 10, 11, 12, or more end loops. In some aspects, the proximal end loops 420 and / or the distal end loops 470 may not all have the same length. For example, the proximal end loops 4201 and / or the distal end loops 4701 may be larger (e.g., having a radius Ri from a center 408 of the circumference 404), while others are smaller (e.g., the proximal end loops 420s and / or the distal end loops 470s e.g., having a radius Rs from the center 408 of the circumference 404, Rs being smaller than Ri). The larger proximal end loops 4201 (or larger distal end loops 4701 at the distal end) and smaller proximal end loops 420s (or small distal end loops 470s at the distal end) may form an alternating pattern, e.g., four larger and four smaller loops are interposed with each other.

[0117] In some aspects, the configurations of proximal end loops 420 and the distal end loops 470, may differ based on functional, structural, and material considerations to optimize stent performance. For example, the proximal end loops 420 may be designed to facilitate stent retrieval, repositioning, and controlled deployment, while the distal end loops 470, if present, may serve functions such as enhancing radi opacity, preventing fraying, and / or stabilizing the distal end of the stent 410.

[0118] Due to these differing roles, at least one proximal end loop 420 may differ from at least one distal end loop 470 in various structural and material properties. For example, the deflection angle of the end loops (e.g., the deflection angle 440 of the proximal end loop 420 and the deflection angle 480 of the distal end loop 470) relative to the longitudinal axis 402 of the mesh 401 in an expanded configuration 406 may vary to optimize engagement with the delivery catheter 450 (shown in FIG. 4B) and ensure proper anchoring. Additionally, differences in number of end loops (e.g., the proximal end loop 420 and the distal end loop 470), end loop length, wire construction, thickness, and material type may be implemented to provide mechanical reinforcement at the proximal end of the stent 410 while ensuring sufficient flexibility at the distal end of the stent 410.

[0119] In some aspects, the number of wires forming the end loops and the interweaving pattern of the coupling portion (e.g., the proximal-end-loop coupling portion 422 and the distal-end-loop coupling portion 472) with the mesh 401 may vary to achieve secure attachment and tailored mechanical responses at each end.

[0120] Furthermore, the coupling mechanism, the distance of the end loops (e.g., the proximal end loop 420 and the distal end loop 470) to the respective proximal anddistal ends of the mesh 401 (401p and 401d), and the axial length of the coupling portions (e.g., the proximal-end-loop coupling portion 422 and the distal -end-loop coupling portion 472) coupled to the mesh 401 may be different and may be customized to ensure optimal deployment characteristics and vessel conformity. The rotational orientation of the end loops (e.g., the proximal end loop 420 and the distal end loop 470) may also be different and may be adjusted to enhance stability, reduce mechanical stress, and improve overall stent performance during delivery and expansion. By implementing these differences, the disclosed stent design achieves enhanced deliverability, secure anchoring, and improved flow diversion efficiency while maintaining flexibility and structural integrity within the vessel.

[0121] FIG. 8 is a diagram 800 illustrating an example of the delivery device 810 for delivering a stent 410, in accordance with various aspects of the present disclosure. The delivery device 810 configured to deliver the stent 410 to a target site (e.g., the target site 105 in FIG. 1) may correspond to the delivery device 210 in FIG. 2. In some aspects, the delivery device 810 may include a delivery catheter 450 (e.g., corresponding to the delivery catheter 250 in FIGs. 2 and 3). In some aspects, the stent 410 may be advanced through the inner lumen 455 of the delivery catheter 450 to a target site (e.g., the target site 105 in FIG. 1), e.g., at a location distally beyond or at the distal end of the target site. For example, the pusher 452 (e.g., corresponding to the pusher 252 in FIGs. 2 and 3) may be held in place while the delivery catheter 450 is proximally withdrawn to expose a distal end 410d of the stent 410, which may radially expand to engage and anchor to the vessel (e.g., the vessel 104 in FIG. 1). For example, the pusher 452 may be advanced distally by a physician (e.g., the operator of the delivery device 810) and the delivery catheter 450 may be retracted proximally to cause the stent 410 to be longitudinally pushed forward.

[0122] In some examples, a core wire 453 (e.g., corresponding to the core wire 253 in FIG. 3), may be used to facilitate the advancement and positioning of the delivery catheter 450 within the vasculature. The core wire 453 may be composed of a flexible core material, such as nitinol or stainless steel, and may include a hydrophilic or polytetrafluoroethylene (PTFE) coating to improve trackability and reduce friction during navigation through tortuous vessels. For example, when deploying the stent 410, the core wire 453 may be inserted first and advanced through a guide catheter (not shown) to establish a stable pathway for the delivery catheter 450 and / or the stent410. In some examples, once the distal end of the core wire 453 reaches the target site, the delivery catheter 450 and / or the stent 410 may be advanced over the core wire 453, ensuring precise positioning of the stent 410 before deployment.

[0123] In some aspects, the stent may be a single-layer stent, and each proximal-end-loop coupling portion or distal-end-loop coupling portion may extend along the entire length of the mesh. For example, FIG. 9 is a diagram 900 illustrating a stent 910 with one or more end loop wires 921 extending along the full axial length of the mesh 901, in accordance with various aspects of the present disclosure. The stent 910 may correspond to stent 110 in FIGs. 1-3 and may have similar characteristics to stent 410, as discussed above. Unlike stent 410, where proximal end loops 420 and distal end loops 470 are formed separately, in the stent 910, one or more proximal end loops 920 and corresponding one or more distal end loops 970 may be formed from one or more continuous end loop wires 921 that extend through the full length of the mesh 901. The configuration allows for different mechanical properties, load distribution, and anchoring performance, providing an alternative structural reinforcement method compared to individually attached or shorter coupling portions as discussed above.

[0124] FIG. 10 is a diagram 1000 illustrating an example of the delivery device 1010 for delivering a stent 910, in accordance with various aspects of the present disclosure. The delivery device 1010 configured to deliver the stent 910 to a target site (e.g., the target site 105 in FIG. 1) may correspond to the delivery device 210 in FIG. 2. In some aspects, the delivery device 1010 may include a delivery catheter 1050 (e.g., corresponding to the delivery catheter 250 in FIGs. 2 and 3). In some aspects, the stent 910 may be advanced through the inner lumen 1055 of the delivery catheter 1050 to a target site (e.g., the target site 105 in FIG. 1), e.g., at a location distally beyond or at the distal end of the target site. For example, the pusher 1052 (e.g., corresponding to the pusher 252 in FIGs. 2 and 3) may be held in place while the delivery catheter 1050 is proximally withdrawn to expose a distal end 910d of the stent 910, which may radially expand to engage and anchor to the vessel (e.g., the vessel 104 in FIG. 1). For example, the pusher 1052 may be advanced distally by a physician (e.g., the operator of the delivery device 1010) and the delivery catheter 1050 may be retracted proximally to cause the stent 910 to be longitudinally pushed forward.

[0125] In some examples, a core wirel053 (e.g., corresponding to the core wire253 in FIG. 3), may be used to facilitate the advancement and positioning of the delivery catheter1050 within the vasculature. The core wirel053 may be composed of a flexible core material, such as nitinol or stainless steel, and may include a hydrophilic or polytetrafluoroethylene (PTFE) coating to improve trackability and reduce friction during navigation through tortuous vessels. For example, when deploying the stent 910, the core wire 1053 may be inserted first and advanced through a guide catheter (not shown) to establish a stable pathway for the delivery catheter 1050 and / or the stent 910. In some examples, once the distal end of the core wire 1053 reaches the target site, the delivery catheter 1050 and / or the stent 910 may be advanced over the core wire 1053, ensuring precise positioning of the stent 910 before deployment.

[0126] FIG. 11 is a flow diagram 1100 illustrating an example of a method for manufacturing the stent, in accordance with various aspects of the present disclosure. The stent may correspond to the stent 410 in FIGs. 4A, 4B, 4C, 5, 6, 7, and 8, and / or the stent 910 in FIGs. 9 and 10.

[0127] 1105 may include forming a mesh (e.g., the mesh 401 in FIGs. 4A, 4B, 4C, 5, 6, 7, and 8 and / or the mesh 901 in FIGs. 9 and 10) having a proximal end (e.g., the proximal end 401p in FIGs. 4A, 4B, 4C, 5, 6, 7, and 8 and / or the proximal end 901p in FIGs. 9 and 10) and a distal end (e.g., the distal end 401d in FIGs. 4C and 8 and / or the distal end 90 Id in FIGs. 9 and 10). In some aspects, the mesh may be composed of one or more machine-braided interwoven wires, ensuring a consistent, high-density structure. In some embodiments, the mesh may have a density of at least 100 PPI, enhancing flow diversion efficiency. For example, in some non-limiting implementations, the PPI may be about 110 PPI, 120 PPI, 140 PPI, 150 PPI, or 165 PPI. Additionally, in some examples, the pores of the mesh 401 may be sized within a range of about 0.2 mm to about 0.6 mm when the stent is in its expanded configuration. In one example, the wire diameter of the wires forming the mesh may be about 0.00085 inch and may be braided to achieve about 165 PPI.

[0128] 1110 may include coupling a set of proximal end loops (e.g., the proximal end loops420 in FIGs. 4A, 4B, 4C, 5, 6, 7, and 8 and / or the proximal end loops 920 in FIGs. 9 and 10) to the mesh. In some aspects, the set of proximal end loops forms a single layer with the mesh. In some aspects, each proximal end loop may be separate from the mesh. In some aspects, each proximal end loop may have a proximal-end-loop coupling portion (e.g., the proximal-end-loop coupling portion 422 in FIGs. 4A, 4B, 4C, 5, 6, 7, and 8 and / or the proximal-end-loop coupling portion 922 in FIGs. 9 and10) coupled to the mesh and a proximal-end-loop loop portion (e.g., the proximal- end-loop loop portion 423 in FIGs. 4A, 4B, 4C, 5, 6, 7, and 8 and / or the proximal- end-loop loop portion 923 in FIGs. 9 and 10) extending proximally beyond the proximal end of the mesh. In some aspects, the proximal-end-loop coupling portion 422 may extend less than the entire axial length of the mesh, measured along the longitudinal axis.

[0129] In some aspects, the method may optionally include 1115 which may include coupling a set of distal end loops to (e.g., the distal end loops 470 in FIGs. 4C and 8 and / or the distal end loops 970 in FIGs. 9 and 10) the mesh. In some aspects, the set of distal end loops forms the single layer with the mesh. In some aspects, each distal end loop may be separate from the mesh. In some aspects, each distal end loop 470 may have a distal-end-loop coupling portion (e.g., the distal -end-loop coupling portion 472 in FIGs. 4C and 8 and / or the distal-end-loop coupling portion 972 in FIGs. 9 and 10) coupled to the mesh and a distal -end-loop loop portion (e.g., the distal -end-loop loop portion 473 in FIGs. 4C and 8 and / or the distal-end-loop loop portion 973 in FIGs. 9 and 10) extending distally beyond the distal end of the mesh. In some aspects, the distal-end-loop coupling portion may extend less than the entire axial length of the mesh, measured along the longitudinal axis.

[0130] In some aspects, the method may optionally include 1120 which may include coupling a radiopaque element (e.g., the radiopaque element 428 in FIGs. 4A, 4B, 4C, 5, 6, 7, and 8) to at least one of the set of proximal end loops.

[0131] In some aspects, each proximal end loop of the set of proximal end loops may be formed by one wire.

[0132] In some aspects, each proximal end loop of the set of proximal end loops may be a continuous loop of wire.

[0133] In some aspects, at least one proximal end loop of the set of proximal end loops may have two ends forming two wire legs.

[0134] In some aspects, the mesh may have an axial length and each proximal-end-loop coupling portion extends along the mesh for less than the axial length of the mesh.

[0135] In some aspects, each proximal-end-loop coupling portion may extend less than half of the axial length of the mesh.

[0136] In some aspects, each proximal-end-loop coupling portion may extend less than one third of the axial length of the mesh.

[0137] In some aspects, in a compressed configuration, at least one proximal end loop of the set of proximal end loops may extend out in a longitudinal direction from the mesh by a length approximately LPicand in a radial direction by a radius approximately RPic, and in an expanded configuration, the at least one proximal end loop of the set of proximal end loops may extend in the longitudinal direction out from the mesh by a length approximately LPieand in the radial direction by a radius approximately RPie, where LPicmay be greater than LPieand Rple may be greater than RPic.

[0138] In some aspects, in the compressed configuration, the mesh may have an average radius of Rmc, where RPic = Rmc + A, where A > 0.

[0139] In some aspects, A may be approximately equal to an average spacing between an outer surface of the mesh and an inner lumen of a catheter compressing the stent.

[0140] In some aspects, the stent may be a single-layer stent, and each proximal-end-loop coupling portion extends along an entire length of the mesh.

[0141] In some aspects, each proximal end loop of the set of proximal end loops may be coupled to the mesh by being woven through or fixed to the mesh.

[0142] In some aspects, each distal end loop of the set of distal end loops may be formed by one wire.

[0143] In some aspects, the mesh may have an axial length and each distal-end-loop coupling portion extends along the mesh for less than the axial length of the mesh.

[0144] In some aspects, each distal-end-loop coupling portion may extend less than half of the axial length of the mesh.

[0145] In some aspects, each distal-end-loop coupling portion may extend less than one third of the axial length of the mesh.

[0146] In some aspects, a proximal end loop of the set of proximal end loops and a distal end loop of the set of distal end loops may be formed by one continuous wire.

[0147] In some aspects, in a compressed configuration, at least one distal end loop of the set of distal end loops may extend in a longitudinal direction from the mesh by a length approximately Laic and in a radial direction by a radius approximately Raic, in an expanded configuration, the at least one distal end loop of the set of distal end loops may extend in the longitudinal direction out from the mesh by a length approximately Laie and in the radial direction by a radius approximately Raie, where Laic is greater than Laie and Raie is greater than Raic.

[0148] In some aspects, in the compressed configuration, the mesh has an average radius of Rmc, where Rdic = Rmc + A, where A > 0.

[0149] In some aspects, A is approximately equal to an average spacing between an outer surface of the mesh and an inner lumen of a catheter compressing the stent.

[0150] In some aspects, at least one proximal end loop of the set of proximal end loops differs from at least one distal end loop of the set of distal end loops in at least one of an end loop deflection angle relative to a longitudinal axis of the mesh in an expanded configuration; an end loop length; a wire construction; a wire thickness; a wire material type; an amount of wires; a coupling portion interweaving pattern; a coupling mechanism; a distance to respective proximal and distal ends of the mesh; an axial length of the respective coupling portions coupled to the mesh; or a rotational orientation of the end loops.

[0151] In some aspects, the mesh may include one or more machine-braided interwoven wires.

[0152] In some aspects, the mesh may have a mesh density of at least 100 pores per inch (PPI)

[0153] In some aspects, the one or more machine-braided interwoven wires may include a first wire having a first wire construction and a second wire having a second wire construction, where the first and second wire constructions are different.

[0154] In some aspects, the mesh and the set of proximal end loops may be formed by a plurality of different material types.

[0155] In some aspects, the set of proximal end loops may be formed of DFT.

[0156] In some aspects, the set of proximal end loops may be formed of wires that are thicker than wires forming the mesh.

[0157] In some aspects, the mesh may have a cylindrical body, and the set of proximal end loops may be approximately symmetrically distributed around a circumference of the proximal end of the cylindrical body of the mesh.

[0158] In some aspects, the mesh may have a grid of pores, and a portion of each proximal end loop of the set of proximal end loops coupled to the mesh may extend approximately parallel to a strand forming a pore of the grid of pores.

[0159] In some aspects, each proximal-end-loop coupling portion may have an interweaving pattern of p x q, where for each interweave p is a number of wires over which theproximal-end-loop coupling portion extends and q is a number of wires under which the proximal-end-loop coupling portion extends, and 1 < p < 5 and 1 < q < 5.

[0160] Referring again to FIGs. 1-11, a stent 410 includes a mesh 401 having a proximal end 401p and a distal end 401d. The stent 410 further includes a set of proximal end loops 420 forming a single layer with the mesh 401. Each proximal end loop 420 is separate from the mesh 401. Each proximal end loop 420 has a proximal-end-loop coupling portion 422 coupled to the mesh 401 and a proximal-end-loop loop portion 423 extending proximally beyond the proximal end of the mesh 401. Each proximal end loop of the set of proximal end loops 420 is formed by one wire, e.g., a proximal loop wire 421. Each proximal end loop of the set of proximal end loops 420 is a continuous loop of wire. At least one proximal end loop of the set of proximal end loops 420 has two ends forming two wire legs 421a and 421b. The two wire legs 421a and 421b are the proximal-end-loop coupling portion 422. The mesh 401 has an axial length and each proximal-end-loop coupling portion 422 extends along the mesh 401 for less than the axial length of the mesh 401. Each proximal-end-loop coupling portion 422 extends less than half of the axial length of the mesh 401. Each proximal-end-loop coupling portion 422 extends less than one third of the axial length of the mesh 401. In a compressed configuration 403 as shown in FIG. 7, at least one proximal end loop of the set of proximal end loops 420 extends out in a longitudinal direction from the mesh 401 by a length approximately LPicand in a radial direction by a radius approximately Rpic, and in an expanded configuration 406 as shown in FIG. 4A and FIG. 4B, the at least one proximal end loop of the set of proximal end loops 420 extends in the longitudinal direction out from the mesh 401 by a length approximately Lpieand in the radial direction by a radius approximately Rpie, where LPicis greater than Lpieand RPieis greater than RPic. In the compressed configuration 403 shown in FIG. 7, the mesh has an average radius of Rmc, where Rpic = Rmc + A, where A > 0. A is approximately equal to an average spacing between an outer surface of the mesh 401 and an inner lumen 455 of a catheter 450 compressing the stent 410. Each proximal end loop of the set of proximal end loops 420 is coupled to the mesh 401 by a weave through or fixed to the mesh 401. The stent 410 further includes a set of distal end loops 470. The set of distal end loops 470 forms the single layer with the mesh 401. Each distal end loop 470 is separate from the mesh 401. Each distal end loop 470 has a distal-end-loop coupling portion 472 coupled to the mesh 401 and a distal-end-loop loop portion 473 extending distally beyond the distal end 401d of the mesh 401. Each distal end loop of the set of distal end loops 470 is formed by one wire 471. The mesh 401 has an axial length and each distal-end-loop coupling portion 472 extends along the mesh 401 for less than the axial length of the mesh 401. Each distal-end- loop coupling portion 472 extends less than half of the axial length of the mesh 401. Each distal -end-loop coupling portion 472 extends less than one third of the axial length of the mesh 401. A proximal end loop of the set of proximal end loops 920 and a distal end loop of the set of distal end loops 970 are formed by one continuous wire. In a compressed configuration 403, at least one distal end loop of the set of distal end loops 470 extends in a longitudinal direction from the mesh 401 by a length approximately Laic and in a radial direction by a radius approximately Raic, in an expanded configuration 406, the at least one distal end loop of the set of distal end loops 470 extends in the longitudinal direction out from the mesh 401 by a length approximately Laie and in the radial direction by a radius approximately Raie, where Laic is greater than Laie and Raie is greater than Raic. In the compressed configuration 403, the mesh 401 has an average radius of Rmc, where Raic = Rmc + A, where A > 0. A is approximately equal to an average spacing between an outer surface of the mesh 401 and an inner lumen 455 of a catheter 450 compressing the stent 410. At least one proximal end loop of the set of proximal end loops 420 differs from at least one distal end loop of the set of distal end loops 470 in at least one of an end loop deflection angle relative to a longitudinal axis of the mesh in an expanded configuration, an end loop length, a wire construction, wire thickness, wire material type, an amount of wires, a coupling portion interweaving pattern, a coupling mechanism, a distance to respective proximal and distal ends of the mesh, an axial length of the respective coupling portions coupled to the mesh, or a rotational orientation of the end loops. The mesh 401 includes one or more machine-braided interwoven wires. The mesh 401 has a mesh density of at least 100 PPI. The one or more machine-braided interwoven wires include a first wire having a first wire construction and a second wire having a second wire construction, wherein the first and second wire constructions are different. The mesh 401 and the set of proximal end loops 420 are formed by a plurality of different material types. The set of proximal end loops 420 is formed of DFT. The set of proximal end loops 420 are formed of wires that are thicker than wires forming the mesh 401. The mesh 401 has a cylindrical body, and the set ofproximal end loops 420 is approximately symmetrically distributed around a circumference 404 of the proximal end of the cylindrical body of the mesh 401. The mesh 401 has a grid of pores 460, and a portion of each proximal end loop of the set of proximal end loops (e.g., the proximal-end-loop coupling portion 422) coupled to the mesh 401 extends approximately parallel to a strand 451 forming a pore of the grid of pores 460. The stent 410 further includes a radiopaque element 428 coupled to at least one of the set of proximal end loops 420. Each proximal-end-loop coupling portion 422 has an interweaving pattern of p x q, where for each interweave p is a number of wires over which the proximal-end-loop coupling portion extends and q is a number of wires under which the proximal-end-loop coupling portion extends, and 1 < p < 5 and 1 < q < 5. The stent 910 is a single-layer stent, and each proximal-end- loop coupling portion 922 extends along an entire length of the mesh 901, as shown in FIG. 9.

[0161] Particular aspects of the subject matter described in this disclosure can be implemented to achieve one or more of the following advantages. For example, by incorporating add-on loops at the proximal (and distal ends in some examples) of a flow diverter stent, the described techniques enhance stent deliverability and deployment control, allowing for a more predictable and stable positioning within the vessel. The integration of symmetrically positioned add-on loops provides secure anchoring, helping to mitigate unintended stent migration while maintaining flexibility in the central stent body. The high-density machine-braided mesh (PPI > 100) increases metal surface area, improving flow diversion performance compared to lower-density hand-braided designs. Additionally, offset loop weld points of the add-on loops prevent mechanical stress concentration, enhancing stent durability and reducing the risk of structural failure. The ability to construct the stent using varied material configurations, such as DFT, Nitinol, or hybrid material combinations, further optimizes mechanical properties for improved deployment characteristics and vessel conformity. Furthermore, by ensuring that loop wires of the add-on loops and braid wires of the body of the stent (e.g., the mesh portion of the stent) remain substantially parallel, the design enhances structural integration, potentially reducing friction during delivery. The disclosed stent configuration allows for seamless compatibility with existing delivery systems, minimizing the need for modificationsto deployment mechanisms while improving treatment efficiency in neurovascular interventions.

[0162] In one example, a stent may include a first tubular portion and a second tubular portion that overlaps a first end of the first tubular portion. The stent may also optionally include a third tubular portion that overlaps a second end of the first tubular portion. The second tubular portion and third tubular portion, if included, only extend a relatively short distance along the length of the first tubular portion, such that neither the second tubular portion nor the third tubular portion overlap a middle region of the first tubular portion. In other words, the second tubular portion and the third tubular portion, if included, only overlap at proximal and distal regions or areas of the first tubular portion.

[0163] In one example, the first tubular portion is configured as a flow diverter in which its porosity is small enough to divert or generally prevent blood flow from passing through its sidewalls. For example, the first tubular portion may have a porosity within an inclusive range of about 0.001 inch to 0.010 inch when in a radially expanded configuration.

[0164] In one example, the second tubular portion and / or third tubular portion are configured as an anchoring portion that assists in anchoring the stent within a vessel of a patient. For example, the second / third tubular portion may exhibit a relatively stronger radial expansion force against a vessel than the first tubular portion, particularly when the first tubular portion is configured as a flow diverter. This relatively stronger radial force of the second / third tubular portion may be achieved by using relatively larger diameter wires, wires of a different material than those of the first tubular portion, and / or secondary shapes that radially flare in a radially expanded configuration relative to the first tubular portion. Since the anchoring portion may have a relatively larger porosity, it may also decrease the frictional force on the components of a delivery device, especially during deployment, such as against an outer catheter sheath that maintains the stent in its radially compressed configuration. Additionally, the anchoring portion, when included on a proximal end of the stent, may provide a stronger and more robust connection point to the delivery device which may allow for more reliable deployment of the stent.

[0165] In one example, the first tubular portion, the second tubular portion, and the third tubular portion may each be composed of one or more braided wires that havedifferent properties and / or that are braided in a different pattern. Several properties are described below and may be used in any combination with each other.

[0166] For example, the wire of the first tubular portion may be relatively smaller in wire diameter than the wire of the second tubular portion and the wire of the third tubular portion. In one example the wire of the first tubular portion may have a diameter within an inclusive range of about 0.0005 inch to about 0.1 inch, and more specifically about 0.0005 inch to 0.0020 inch. In another example, the wire of the second tubular portion and the third tubular portion may have a diameter within an inclusive range of about 0.0001 inch to 0.001 inch, and more specifically 0.0005 inch to about 0.0040 inch.

[0167] In another example, the wire comprising the first tubular portion may be solely drawn filled tube wire (DFT wire), solely shape memory wire (e.g., Nitinol), or a combination of DFT wire and shape memory wire. The wire of the second tubular portion and the third tubular portion may be solely drawn filled tube wire (DFT wire), solely shape memory wire (e.g., Nitinol), or a combination of DFT wire and shape memory wire. In one specific example, the first tubular portion may be composed of DFT wire and Nitinol wire, while the second tubular portion and optional third tubular portion may be braided with only one or more Nitinol wires.

[0168] In another example, the wire of the first tubular portion may have a braiding pattern forming a picks-per-inch (PPI) that is different than the PPI of the second tubular portion and / or the PPI of the optional third tubular portion. Put another way, the first tubular portion may have a braiding pattern forming a porosity that is different than the porosity of the second tubular portion. In one specific example, the first tubular portion may have a PPI that is higher than a PPI of the second tubular portion and the third tubular portion.

[0169] In another example, the first tubular portion may have a braiding pattern forming a porosity or average pore size that is different than the porosity or pore size of the second tubular portion and / or the third tubular portion. In one specific example, the first tubular portion may have a lower porosity than the second tubular portion or third tubular portion. In a further example, the first tubular portion may be configured as a flow diverter and therefore may have a porosity with an average pore size within an inclusive range of about 0.001 inch to 0.010 inch (or generally less than 0.010 inch), while the second tubular portion and the third tubular portion have a porosity with anaverage pore size that is higher than the first tubular portion (e.g., 0.1 inch or higher) depending on a diameter of the stent and its picks-per-inch (PPI). Note that pore size here refers to a diameter of a generally circular shape that fits within the “diamond” of the cell when the first tubular portion and / or the second tubular portion are in a radially expanded configuration.

[0170] In another example, the first tubular portion may have a number of braided wires that are different from the number of braided wires of the second tubular portion and / or the optional third tubular portion. For example, the first tubular portion may have braided wires within an inclusive range of about 12 to 80, and more specifically 36, 46, 48, or 64 wires. In another example, the second tubular portion and / or third tubular portion may have a number of braided wires within an inclusive range of about 6 to 48 wires, and more specifically 12, 16, 20, or 24 wires. The second tubular portion and the third tubular portion may have the same number of braided wires or different numbers of braided wires. Note that the term “wires” in this context may include individually braided wires or wire segments between a proximal and distal end of the first tubular portion (or other stent portions) in the case of a braid created by only a single wire. Hence, the terms “wires” and “wire segments” may be used interchangeably in the context of braid descriptions.

[0171] In another example, the first tubular portion may have a longer axial length than either the second tubular portion or the third tubular portion. For example, the first tubular portion may have a length between its proximal end and its distal end within an inclusive range of about 5 cm to about 100 cm, and the second tubular portion or third tubular portion may have a length within an inclusive range of about 1 cm to about 20 cm. As compared with a stent having two full tubular layers, the inclusion of one or two shorter portions / layers may result in regions of the stent that are relatively thinner, which may allow for smaller diameter delivery catheters and improved delivery performance.

[0172] The DFT wires of this specification may be composed of a variety of different materials with different cross-sectional thicknesses. For example, a DFT wire or segments may comprise an inner core composed of a first material and an outer jacket or tube composed of a second material. In another example, the outer jacket may alternately be composed of multiple layers of different material (e.g., two or more layers over inner core). Either the inner core and the outer jacket may be composedof radiopaque materials (such as platinum, gold, tantalum, palladium, or similar known radiopaque materials). Either the inner core and the outer jacket may be composed of non-radiopaque materials (i.e., materials with a relatively low or no radiopaque properties). Such non-radiopaque materials may include, e.g., stainless steel, cobalt-chromium, or shape memory alloys such as Nitinol. In one example, the inner core may be composed of radiopaque material(s) and the outer jacket may be composed of non-radiopaque materials. In another example, the inner core may be composed of non-radiopaque materials and the outer jacket may be composed of non- radiopaque materials.

[0173] In one example, the inner core may be composed of a radiopaque material and the outer jacket may be composed of a shape memory alloy such as Nitinol. The radiopaque material promotes visualization of the DFT wire, while the outer jacket allows for good pliability and the ability to have a memorized shape (e.g., via being heat-set). In another example, the inner core may be composed of platinum or tantalum, while the outer jacket may be composed of Nitinol-1 or Nitinol-2.

[0174] The inner core may have a cross-sectional shape that is circular, elliptical, or ovular, though a variety of other shapes can be used, such as rectangular, triangular, or the like. The outer jacket may be tubular in shape with an inner diameter that closely matches the outer diameter of the inner core. Put differently, the outer jacket may include an internal lumen through which the inner core extends.

[0175] Additionally, DFT wires may sometimes exhibit a higher degree of bendability and reduced stiffness than a single-metal shape memory wire once heat treatment / heat- setting occurs. This may be generally unexpected since inclusion of a radiopaque material in the inner core (depending on which particular material is used) can generally be stiffer in comparison to the metallic shape memory outer jacket. However, the inclusion of two separate materials in creating a single wire can alter the material characteristics of the combined wire shape. Due to these characteristics, when DFT wires or segments are used in a stent, design aspects of the stent may need to compensate for this increased flexibility, especially to promote proper deployment and proper apposition of the DFT stent at the treatment site to prevent stent migration.

[0176] The outer diameter of the DFT wire or segment may have a wide range of diameters, depending on its use within a stent. For example, the DFT wire or segment may have a diameter within an inclusive range of about 0.001 inch to 0.004 inch, or about 0.0025inch to about 0.003 inch. The inner core and outer jacket of the DFT wire or segment may be composed of different percentages of the cross section of the DFT wire or segment based on cross-sectional width or diameter. For example, the inner core may be within an inclusive range of 5% to 30% of the cross-sectional width or diameter of the DFT wire or segment with the remaining percentage being the outer jacket (i.e., 95% to 70%). In a more specific example, the ration may be 10% inner core cross sectional width or diameter and 90% outer jacket cross sectional width or diameter.

[0177] In some examples, the total cross-sectional width or diameter of the DFT wire or segment is within an inclusive range of about 0.0018 inch to about 0.0022 inch. In some examples, the inner core (e.g., composed of a radiopaque material) has a width or diameter within an inclusive range of about 0.0005 inch to about 0.001 inch, or an inclusive range of about 0.0008 inch to about 0.0009 inch.

[0178] Any of the wires used in a stent of this disclosure may be functionalized, for example with poly (MEA-co-APMA).

[0179] The second tubular portion and the third tubular portion may be attached to the first tubular portion by one or more attachment mechanisms. For example, the wires of the portions may be welded to each other at one or more locations, the wires of the portions may be attached via adhesive at one or more locations, the wires of the portions may be attached via wire coils or tubular members, or the wires of the portions may be attached by interleaving or braiding a connecting wire between the portions. For the example of the welding, adhesive, coils, or tubular members, the attachment locations may be uniformly distributed along the overlapping length of the two portions and at uniform radial position, or may be located only near the inner and / or outer edges of the overlapping portions.

[0180] In some examples, the second tubular portion and the third tubular portion may overlap with the first tubular portion along an outer surface of the first tubular portion or along an inner surface of the first tubular portion. Hence, the second tubular portion may be positioned on the outer surface or the inner surface of the first tubular portion, and the second tubular portion, if included, may be positioned on the outer surface or the inner surface of the first tubular portion.

[0181] Depending on the configuration, any of the free ends of the first tubular portion, the second tubular portion, or the third tubular portion may have a radially expanded shape that radially flares or increases in diameter. For example, if only the secondtubular portion overlaps with the first tubular portion, the opposite free end of the first tubular portion may have a radially flared or diametrically increasing size. In another example, if both the second tubular portion and the third tubular portion are attached and only partially overlap a portion of the first tubular portion, the non-overlapping regions of the second tubular portion and the third tubular portion may be radially flared or diametrically increasing in size towards their free ends. In one example, the radial flare forms an angle relative to a longitudinal axis of the second tubular portion within an inclusive range of about 15 degrees to about 60 degrees, such as 15, 20, 25, 30, 35, 40, 45, 50, 55, 60, or angles in between.

[0182] Any of the free ends of the first tubular portion, the second tubular portion, or the third tubular portion may have a plurality of loops that are larger in size than the regular pore sizes of their respective braid patterns. When any of the portions are in their expanded configurations, the plurality of loops may form a uniform or constant tubular diameter with their respective portions, or may have a radially flared or diametrically increasing size relative to the bodies of the tubular portions. The size of the plurality of loops themselves may all be relatively the same diameter or may have different diameters (e.g., alternating larger and smaller loops).

[0183] In some examples, any of the loops of the first tubular portion, the second tubular portion, or the third tubular portion may further include radiopaque markers. Those radiopaque markers may comprise one or more wire coils formed from a radiopaque wire (e.g., tantalum), a radiopaque sleeve or tube formed from a radiopaque material (e.g., tantalum), or a radiopaque coating.

[0184] The second tubular portion or the third tubular portion may partially overlap with the first tubular portion by only a fractional amount (i.e., less than complete overlap). For example, the second tubular portion or the third tubular portion may partially overlap in axial length a percentage of the length of the first tubular portion within an inclusive range of about 5% to about 30%, or more specifically 5, 6, 7, 8, 9, 10, 11, 12, 13, 14, 15, 16, 17, 18, 19, 20, 21, 22, 23, 24, 25, 26, 27, 28, 29, 30 percent, or percentages in between. In another example, the second tubular portion or the third tubular portion may partially overlap within an inclusive range of about 0.3 cm to about 2 cm starting from either a first tubular end or a second tubular end of the first tubular portion. In another specific example, the second tubular portion or the third tubular portion maypartially overlap within an inclusive range of about 0.5 cm to about .8 cm starting from either a first tubular end or a second tubular end of the first tubular portion.

[0185] While the second tubular portion or the third tubular portion are described in this specification as overlapping the first tubular portion, the edges of each portion may be connected immediately adjacent to each other in a non-overlapping configuration.

[0186] The second tubular portion and the third tubular portion may be positioned to overlap either within an interior lumen of the first tubular portion or on an outer surface of the first tubular lumen. If both the second tubular portion and the third tubular portion are present, both may be located within or on an outer surface of the first tubular member, or one may be located within the lumen of the first tubular member and the other may be located on the outer surface of the first tubular member.

[0187] In one example configuration, the first tubular portion may comprise a blood flow diverter, while the second tubular portion and optional third tubular portion may comprise anchoring portions overlapping ends of the first tubular portion, as previously described. Typically, stents with flow diverter layers have an anchoring layer and a flow diverter layer that extends either the entire length of the anchoring layer or a partial / fractional length of the anchoring layer, since this may allow the entire length of the flow diverter to be anchored at nearly every cross-sectional position. However, by including anchoring layers only overlapping or extending from one or two ends of a flow diverter layer and overlapping only a short distance, the stent may have a thinner profile, may produce less friction during deployment, and may allow for a greater percentage of radiopaque wire materials (e.g., radiopaque DFT wire).

[0188] The first tubular portion, second tubular portion, and third tubular portion of the example stents of this disclosure are typically referred to as “tubular” but may also include similar shapes, such as an open tubular shape with a “C” cross section or two arc-shaped cross-sectional shapes.

[0189] Additional aspects and features of the stent examples described in this specification may be modified or combined with those disclosed in U.S. Pat. No. 9,439,791 which is hereby incorporated by reference.

[0190] In one example, a method is provided for creating a stent with any combination of the features discussed in this specification. A first plurality of wires may be braided into a first tubular portion with any of the features discussed in this specification. A secondplurality of wires may be braided into a second tubular portion with any of the features discussed in this specification. A third plurality of wires may be braided into a third tubular portion with any of the features discussed in this specification. The second tubular portion may be attached so that it partially overlaps a first end region of the first tubular portion without overlapping a middle region of the first tubular portion and the third tubular portion may be attached so that it partially overlaps a second end region of the first tubular portion without overlapping the middle region of the first tubular portion. The attachment mechanisms may be any of those discussed in this specification.

[0191] Specific examples of the previously described stent are further described below in connection with the figures. However, it is the intent of this disclosure to encompass stents with any combination of the aspects disclosed in this specification, and therefore the disclosure should not be strictly limited to the specific combination of the figures.

[0192] FIGs. 12 and 13 illustrate one example of a stent 1200. FIG. 12 illustrates a side view of the stent 1200 and FIG. 13 illustrates a cross-sectional side view of the stent 1200 along line 2-2 of FIG. 12.

[0193] The stent 1200 may have a generally tubular shape with a radially compressed configuration and a radially expanded configuration. In the present example, the stent 1200 may comprise a first tubular portion 1202 and a second tubular portion 1204 that overlap each other along overlapping region 1214 to form a continuous stent lumen therethrough.

[0194] In the present example, the first tubular portion 1202 may be configured as a flow diverter region of the stent 1200 while the second tubular portion 1204 may be configured as an anchoring region of the stent 1200, as described earlier in this specification. However, other uses or functionality of each are also possible.

[0195] The first tubular portion 1202 may be composed of one or a plurality of braided wires 1206 that form a tubular shape having a first tubular end 1202 A and a second tubular end 1202B. In the present example, the plurality of braided wires 1206 may comprise all DFT wires or a combination of DFT wires and shape memory wires (Nitinol wires), however, other combinations disclosed in this specification are also possible.

[0196] The free second tubular end 1202B of the first tubular portion 1202 (i.e., the end not overlapped by the second tubular portion 1204) may terminate with a plurality ofloops 1212. These loops 1212 may be formed from the plurality of braided wires 1206 during the braiding process or may be formed after braiding by welding the free ends of the plurality of braided wires 1206 together.

[0197] The second tubular portion 1204 may be composed of one or a plurality of braided wires 1208 that form a tubular shape. In the present example, the plurality of braided wires 1208 may comprise all shape memory wires (e.g., Nitinol wires), all DFT wires, or a combination of DFT wires and shape memory wires (e.g., Nitinol wires), however, other combinations disclosed in this specification are also possible.

[0198] The free end of the second tubular portion 1204 (i.e., the end not overlapped by the first tubular portion 1202) may terminate with a plurality of loops 1210. These loops 1210 may be formed from the plurality of braided wires 1208 during the braiding process or may be formed after braiding by welding the free ends of the plurality of braided wires 1208 together. The plurality of loops 1210, and optionally part of the non-looped, braided region of the second tubular portion 1204, may be radially flared in the radially expanded configuration of the stent 1200. In other words, the radial size increases towards the free end of the second tubular portion 1204. Alternatively, the second tubular portion 1204 may not be radially flared.

[0199] As previously discussed, the first tubular portion 1202 and the second tubular portion 1204 may have different wire configurations and properties, such as different wire diameter, different wire material, different porosity, different PPI, number of braided wires, axial lengths, and similar features.

[0200] In the present example, the first tubular portion 1202 may have, relative to the second tubular portion 1204, a smaller diameter of plurality of braided wires 1206 relative to plurality of braided wires 1208. In the present example, the first tubular portion 1202 may comprise a plurality of braided wires 1206 comprising DFT wires and Nitinol wires, and the second tubular portion 1204 may comprise a plurality of braided wires 1208 comprising Nitinol wires. In the present example, the first tubular portion 1202 may comprise a lower porosity than the second tubular portion 1204, such as a porosity in an inclusive range of about 0.001 inch to 0.010 inch for the first tubular portion 1202 and about 0.05 inch to about 0.5 inch for the second tubular portion 1204. In the present example, the first tubular portion 1202 may comprise a higher PPI than the second tubular portion 1204, such as a PPI in an inclusive range of about 100 to 300 PPI (e.g., between about 120 to 250 PPI or about 180 to 215 PPI) whenexpanded for the first tubular portion 1202 and about 200 to 500 PPI (e.g., between about 10 to 90 PPI or about 65 to 72 PPI) for the second tubular portion 1204. In the present example, the first tubular portion 1202 may comprise a higher number of the plurality of braided wires 1206 than the plurality of braided wires 1208 of the second tubular portion 1204, such as an inclusive range of about 12 to 80 wires for the first tubular portion 1202 and about 6 to 48 wires for the second tubular portion 1204.

[0201] In the present example, the first tubular portion 1202 may comprise an axial length that is higher than the second tubular portion 1204, such as an axial length in an inclusive range of about 5 cm to about 100 cm for the first tubular portion 1202 and about 1 cm to about 20 cm for the second tubular portion 1204. Again, other differences and variations discussed in this specification for the first tubular portion 1202 and second tubular portion 1204 are also possible. These example differences between the first tubular portion 1202 and second tubular portion 1204 may be beneficial in some cases since the first tubular portion 1202 may be configured as a blood flow diverter which may have relatively reduced radial anchoring force and the second tubular portion 1204 may be configured as an anchoring portion with relatively increased radial anchoring force. In other words, the second tubular portion 1204 may produce a relatively higher radial force to keep the stent 1200 in place within a vessel. Additionally, the first tubular portion 1202 may include a higher number of DFT wires which may increase the radiopaque" qualities and therefore visualization of the stent 1200 during a procedure, possibly at the cost of further reduced anchoring force by the first tubular portion 1202.

[0202] The first tubular portion 1202 and the second tubular portion 1204 may overlap with each other in axial length along an overlapping region 1214 and the first tubular portion 1202 may have a non-overlapping region 1213. Hence, both the first tubular portion 1202 and the second tubular portion 1204 may be considered to have overlapping and non-overlapping areas. In the present example, the first tubular portion 1202 may have a non-overlapping region 1213 that includes its middle region and opposite second tubular end 1202B. In the present example of stent 1200, the first tubular portion 1202 and second tubular portion 1204 only partially overlap with each other (i.e., less than complete overlap) within an inclusive range of about 5% to about 10% of the axial length of the first tubular portion 1202, though any other overlapping percentage discussed in this specification is also possible. In the presentexample of stent 1200, the first tubular portion 1202 and second tubular portion 1204 only partially overlap with each other (i.e., less than complete overlap) within an inclusive range of about 0.5 cm to about 5 cm starting from a first tubular end 1202A.

[0203] In some examples, radiopaque markers may be added along the overlapping region 1214 to help indicate to a physician where the overlapping region 1214 starts and stops as seen during visualization (e.g., fluoroscopy) while performing a procedure. In some examples, radiopaque markers may include wire coils, sleeves, or similar members discussed elsewhere in this specification. In some examples, radiopaque markers may be positioned in a circumferential pattern (e.g., around a circular perimeter), a longitudinal pattern (e.g., linearly), or both circumferential and longitudinal patterns.

[0204] In the present example stent 1200, the second tubular portion 1204 may be positioned within the interior lumen of the first tubular portion 1202, as illustrated in FIG. 13. In some examples, such as those where the first tubular portion 1202 is configured as a blood flow diverter and the second tubular portion 1204 is configured as an anchoring portion, the interior positioning of the second tubular portion 1204 may help radially push or expand the first tubular portion 1202. Alternatively, in some examples, the first tubular portion 1202 may be positioned within the interior lumen of the second tubular portion 1204, as discussed elsewhere in this specification.

[0205] The first tubular portion 1202 and the second tubular portion 1204 may be connected to each other with one or a plurality of different attachment mechanisms, as previously discussed.

[0206] FIG. 14 is a cross-sectional side view of the stent 1200 along line 2-2 of FIG. 12 illustrating an example attachment mechanism. As seen in FIG. 14, the first tubular portion 1202 and the second tubular portion 1204 may be attached via an attachment mechanism comprising a plurality of weld locations 1211 that may be formed by welding the respective braided wires of the tubular portions. These weld locations 1211 may be positioned between at least one of the plurality of braided wires 1206 and at least one of the plurality of braided wires 1208. The plurality of braided wires 1206 and plurality of braided wires 1208 may be braided such that the first tubular portion 1202 and second tubular portion 1204 generally foreshorten at the same rate, thereby preventing or limiting either the first tubular portion 1202 or the second tubular portion 1204 from restricting the foreshortening of the other due to theplurality of weld locations 1211. Alternatively, in some examples, the plurality of weld locations 1211 may instead be adhesive or similar material.

[0207] FIG. 15 is a cross-sectional side view of the stent 1200 along line 2-2 of FIG. 12 illustrating another example attachment mechanism. As seen in FIG. 15, the first tubular portion 1202 and the second tubular portion 1204 may be attached via an attachment mechanism that includes a plurality of attachment coils 1209. These plurality of attachment coils 1209 may be positioned between at least one of the plurality of braided wires 1206 and at least one of the plurality of braided wires 1208. The plurality of braided wires 1206 and plurality of braided wires 1208 may be braided such that the first tubular portion 1202 and second tubular portion 1204 generally foreshorten at the same rate, thereby preventing or limiting either the first tubular portion 1202 or the second tubular portion 1204 from restricting the foreshortening of the other due to the plurality of attachment coils 1209. In some examples, the plurality of attachment coils 1209 may be comprised of coiled wire (e.g., Nitinol or tantalum). Alternatively, the plurality of attachment coils 1209 may be a plurality of tubular sleeves, rings, or similar structures.

[0208] FIG. 16 is a cross-sectional side view of the stent 1200 along line 2-2 of FIG. 12 illustrating another example attachment mechanism. As seen in FIG. 16, the first tubular portion 1202 and the second tubular portion 1204 may be attached via an example attachment mechanism that includes one or more connecting wires 1215 that are interwoven between the first tubular portion 1202 and the second tubular portion 1204. The plurality of braided wires 1206 and plurality of braided wires 1208 may be braided such that the first tubular portion 1202 and second tubular portion 1204 generally foreshorten at the same rate, thereby preventing or limiting either the first tubular portion 1202 or the second tubular portion 1204 from restricting the foreshortening of the other due to the one or more connecting wires 1215. The one or more connecting wires 1215 may extend along the full axial length of the overlapping region 1214, only part of the axial length of the overlapping region 1214, or may extend beyond the overlapping region 1214 (e.g., further along a nonoverlapping portion of the first tubular portion 1202). In some examples, the one or more connecting wires 1215 may comprise a shape memory metal such as Nitinol, a radiopaque material such as tantalum, or a DFT wire.

[0209] In some examples, the first tubular portion 1202 and the second tubular portion 1204 generally foreshorten at the same rate. In such examples, the PPI of the first tubular portion 1202 and the second tubular portion 1204 may also be different. This similar braid angle but different PPI may be achieved, in part, by braiding with a different number of wires for the first tubular portion 1202 as compared with the second tubular portion 1204 (e.g., wires here being defined as the number of cross-sectional wire ends that are created if a tubular portion is cut perpendicularly to its longitudinal axis). In one example, the first tubular portion 1202 may have 48 wires and a PPI of 195 while the second tubular portion 1204 may have 16 wires and a PPI of 65. This may result in about the same braid angle for both tubular portions and therefore about the same rate of foreshortening.

[0210] FIG. 17 illustrates an enlarged perspective view of an end of a stent with radiopaque wires 1222. Any of the end loops of the stents of this specification may further include radiopaque wires 1222. For example, FIG. 17 illustrates a perspective view of an end of stent 1220 which is similar to the previously described stent 1200 but further includes radiopaque wires 1222 on one or more of the plurality of loops 1210 of the second tubular portion 1204. In the present example, the radiopaque wires 1222 may comprise a coil of radiopaque material (e.g., tantalum), however, sleeves, rings, or similar structures comprising radiopaque material may alternatively be used.

[0211] In another example, FIG. 18 illustrates a perspective view of an end of a stent 1230 which may be similar to the previously described stent 1200 but further includes radiopaque wires 1222 (as previously discussed) on one or more of the plurality of loops 1212 or on non-loop portions of the plurality of braided wires 1206. While stent 1220 of FIG. 17 is depicted as a different stent than stent 1230 of FIG. 18, it should be appreciated that both uses of radiopaque wires 1222 may also be used together in the same stent, as well as independently of each other.

[0212] FIGs. 19 and 20 respectively illustrate a side view and a cross-sectional side view of another stent 1240 according to one example. While the stent 1200 discussed previously may include two tubular portions, three tubular stent portions are also possible. For example, the stent 1240 seen in FIGs. 19 and 20 comprises a first tubular portion 1202, a second tubular portion 1204A, and a third tubular portion 1204B. FIG. 19 illustrates a side view of the stent 1240 and FIG. 20 illustrates a cross-sectional side view of the stent 1240 along line 9-9 of FIG. 19.

[0213] The stent 1240 may be similar to the previously described stent 1200 and may have any feature or aspect described elsewhere in this specification. However, the stent 1240 may comprise a second tubular portion 1204A that overlaps with the second tubular end 1202B of the first tubular portion 1202 and a third tubular portion 1204B that overlaps with a first tubular end 1202A of the first tubular portion 1202. In the present example, the first tubular portion 1202 may have a non-overlapping region 1213 that includes a longitudinal length extending across a longitudinal middle of the first tubular portion 1202, while the second tubular portion 1204 A creates overlapping region 1214A and the third tubular portion 1204B creates overlapping region 1214B.

[0214] Generally, the second tubular portion 1204A and third tubular portion 1204B may be similar to the second tubular portion 1204 of stent 1200. Additionally, the second tubular portion 1204A and the third tubular portion 1204B may be identical or alternatively may have one or more different features from each other, such as different wire diameters, wire materials, axial lengths, attachment mechanisms, braid patterns, porosities, PPI, radial flaring, radiopaque markers, or other features discussed in this specification.

[0215] In the present example and as seen best in FIG. 20, the second tubular portion 1204 A and the third tubular portion 1204B may be both partially positioned within the interior lumen of the first tubular portion 1202. Where the second tubular portion 1204 A and the third tubular portion 1204B are configured as anchoring portions, they may exert radial force outwardly against the first tubular portion 1202 and help anchor the stent 1240 against a vessel wall.

[0216] Alternatively, one of the second tubular portion 1204A and the third tubular portion 1204B may be partially positioned within the interior lumen of the first tubular portion 1202 and the other may be partially positioned along the outer surface of the first tubular portion 1202. For example, FIG. 21 illustrates a cross-sectional view of a stent 1260 that is similar to the previously described stent 1240, but the second tubular portion 1204A is partially positioned on an outer surface of the first tubular portion 1202 and the third tubular portion 1204B is partially positioned within the interior lumen of the first tubular portion 1202. The second tubular portion 1204A and the third tubular portion 1204B may also include connecting mechanisms, as previously described in this specification.

[0217] Alternatively, both the second tubular portion 1204A and the third tubular portion 1204B may be partially positioned within the interior lumen of the first tubular portion 1202 or both may be partially positioned along the outer surface of the first tubular portion 1202. For example, FIG. 22 illustrates a cross-sectional view of a stent 1270 that is similar to the previously described stent 1240, but the second tubular portion 1204A is partially positioned on an outer surface of the first tubular portion 1202 and the third tubular portion 1204B is partially positioned on the outer surface of the first tubular portion 1202. The second tubular portion 1204A and the third tubular portion 1204B may also include connecting mechanisms, as previously described in this specification.

[0218] 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 limited to the aspects described herein but are to be accorded with the full scope consistent with the language claims. Reference to an element in the singular does not mean “one and only one” unless specifically so stated, but rather “one or more.” Terms such as “if,” “when,” and “while” do not imply an immediate temporal relationship or reaction. That is, these phrases, e.g., “when,” do not imply an immediate action in response to or during the occurrence of an action but simply imply that if a condition is met then an action will occur, but without requiring a specific or immediate time constraint for the action to occur. 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 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’ 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, orC,” “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, B, or C. Sets should be interpreted as a set ofelements where the elements number one or more. Accordingly, for a set of X, X would include one or more elements. 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 encompassed by the claims. Moreover, nothing disclosed herein is 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.”

[0219] As used herein, the phrase “based on” shall not be construed as a reference to a closed set of information, one or more conditions, one or more factors, or the like. In other words, the phrase “based on A” (where “A” may be information, a condition, a factor, or the like) shall be construed as “based at least on A” unless specifically recited differently.

[0220] The following aspects are illustrative only and may be combined with other aspects or teachings described herein, without limitation.

[0221] Aspect l is a stent including a mesh having a proximal end and a distal end, and a set of proximal end loops forming a single layer with the mesh, each proximal end loop being separate from the mesh, each proximal end loop having a proximal-end-loop coupling portion coupled to the mesh and a proximal-end-loop loop portion extending proximally beyond the proximal end of the mesh.

[0222] Aspect 2 is the stent of aspect 1, each proximal end loop of the set of proximal end loops is formed by one wire.

[0223] Aspect 3 is the stent of aspect 1 or 2, each proximal end loop of the set of proximal end loops is a continuous loop of wire.

[0224] Aspect 4 is the stent of any of aspects 1 to 3, at least one proximal end loop of the set of proximal end loops has two ends forming two wire legs, the two wire legs being the proximal-end-loop coupling portion.

[0225] Aspect 5 is the stent of any of aspects 1 to 4, the mesh has an axial length and each proximal-end-loop coupling portion extends along the mesh for less than the axial length of the mesh.

[0226] Aspect 6 is the stent of any of aspects 1 to 5, each proximal-end-loop coupling portion extends less than half of the axial length of the mesh.

[0227] Aspect 7 is the stent of any of aspects 1 to 6, each proximal-end-loop coupling portion extends less than one third of the axial length of the mesh.

[0228] Aspect 8 is the stent of any of aspects 1 to 7, in a compressed configuration, at least one proximal end loop of the set of proximal end loops extends out in a longitudinal direction from the mesh by a length approximately LPicand in a radial direction by a radius approximately RPic, and in an expanded configuration, the at least one proximal end loop of the set of proximal end loops extends in the longitudinal direction out from the mesh by a length approximately LPieand in the radial direction by a radius approximately RPie, where LPicis greater than LPieand RPieis greater than RPic.

[0229] Aspect 9 is the stent of any of aspects 1 to 8, in the compressed configuration, the mesh has an average radius of Rmc, where RPic = Rmc + A, where A > 0.

[0230] Aspect 10 is the stent of any of aspects 1 to 9, A is approximately equal to an average spacing between an outer surface of the mesh and an inner lumen of a catheter compressing the stent.

[0231] Aspect 11 is the stent of any of aspects 1 to 4 and 8-10, the stent is a single-layer stent, and each proximal-end-loop coupling portion extends along an entire length of the mesh.

[0232] Aspect 12 is the stent of any of aspects 1 to 11, each proximal end loop of the set of proximal end loops is coupled to the mesh by a weave through or fixed to the mesh.

[0233] Aspect 13 is the stent of any of aspects 1 to 12, further including a set of distal end loops forming the single layer with the mesh, each distal end loop being separate from the mesh, each distal end loop having a distal-end-loop coupling portion coupled to the mesh and a distal -end-loop loop portion extending distally beyond the distal end of the mesh.

[0234] Aspect 14 is the stent of any of aspects 1 to 13, each distal end loop of the set of distal end loops is formed by one wire.

[0235] Aspect 15 is the stent of any of aspects 1 to 14, the mesh has an axial length and each distal-end-loop coupling portion extends along the mesh for less than the axial length of the mesh.

[0236] Aspect 16 is the stent of any of aspects 1 to 15, each distal-end-loop coupling portion extends less than half of the axial length of the mesh.

[0237] Aspect 17 is the stent of any of aspects 1 to 16, each distal-end-loop coupling portion extends less than one third of the axial length of the mesh.

[0238] Aspect 18 is the stent of any of aspects 1 to 4 and 8-14, a proximal end loop of the set of proximal end loops and a distal end loop of the set of distal end loops are formed by one continuous wire.

[0239] Aspect 19 is the stent of any of aspects 1 to 18, in a compressed configuration, at least one distal end loop of the set of distal end loops extends in a longitudinal direction from the mesh by a length approximately Laic and in a radial direction by a radius approximately Raic, in an expanded configuration, the at least one distal end loop of the set of distal end loops extends in the longitudinal direction out from the mesh by a length approximately Laie and in the radial direction by a radius approximately Raie, where Laic is greater than Laie and Raie is greater than Raic.

[0240] Aspect 20 is the stent of any of aspects 1 to 19, in the compressed configuration, the mesh has an average radius of Rmc, where Raic = Rmc + A, where A > 0.

[0241] Aspect 21 is the stent of any of aspects 1 to 20, A is approximately equal to an average spacing between an outer surface of the mesh and an inner lumen of a catheter compressing the stent.

[0242] Aspect 22 is the stent of any of aspects 1 to 21, at least one proximal end loop of the set of proximal end loops differs from at least one distal end loop of the set of distal end loops in at least one of: an end loop deflection angle relative to a longitudinal axis of the mesh in an expanded configuration; an end loop length; a wire construction; a wire thickness; a wire material type; an amount of wires; a coupling portion interweaving pattern; a coupling mechanism; a distance to respective proximal and distal ends of the mesh; an axial length of the respective coupling portions coupled to the mesh; or a rotational orientation of the end loops.

[0243] Aspect 23 is the stent of any of aspects 1 to 22, the mesh comprises one or more machine-braided interwoven wires.

[0244] Aspect 24 is the stent of any of aspects 1 to 23, the mesh has a mesh density of at least 100 PPI.

[0245] Aspect 25 is the stent of any of aspects 1 to 24, the one or more machine-braided interwoven wires comprise a first wire having a first wire construction and a second wire having a second wire construction, wherein the first and second wire constructions are different.

[0246] Aspect 26 is the stent of any of aspects 1 to 25, the mesh and the set of proximal end loops are formed by a plurality of different material types.

[0247] Aspect 27 is the stent of any of aspects 1 to 26, the set of proximal end loops is formed of drawn-filled tube (DFT).

[0248] Aspect 28 is the stent of any of aspects 1 to 27, the set of proximal end loops are formed of wires that are thicker than wires forming the mesh.

[0249] Aspect 29 is the stent of any of aspects 1 to 28, the mesh has a cylindrical body, and the set of proximal end loops is approximately symmetrically distributed around a circumference of the proximal end of the cylindrical body of the mesh.

[0250] Aspect 30 is the stent of any of aspects 1 to 29, the mesh has a grid of pores, and a portion of each proximal end loop of the set of proximal end loops coupled to the mesh extends approximately parallel to a strand forming a pore of the grid of pores.

[0251] Aspect 31 is the stent of any of aspects 1 to 30, further including a radiopaque element coupled to at least one of the set of proximal end loops.

[0252] Aspect 32 is the stent of any of aspects 1 to 31, each proximal-end-loop coupling portion has an interweaving pattern of p x q, where for each interweave p is a number of wires over which the proximal-end-loop coupling portion extends and q is a number of wires under which the proximal-end-loop coupling portion extends, and 1 < p < 5 and 1 < q < 5.

[0253] Aspect 33 is a method of manufacturing a stent including forming a mesh having a proximal end and a distal end; and coupling a set of proximal end loops to the mesh, the set of proximal end loops forming a single layer with the mesh, each proximal end loop being separate from the mesh, each proximal end loop having a proximal-end- loop coupling portion coupled to the mesh and a proximal-end-loop loop portion extending proximally beyond the proximal end of the mesh.

[0254] Aspect 34 is the method of aspect 33, each proximal end loop of the set of proximal end loops is formed by one wire.

[0255] Aspect 35 is the method of aspect 33 or 34, each proximal end loop of the set of proximal end loops is a continuous loop of wire.

[0256] Aspect 36 is the method of any of aspects 33 to 35, at least one proximal end loop of the set of proximal end loops has two ends forming two wire legs, the two wire legs being the proximal-end-loop coupling portion.

[0257] Aspect 37 is the method of any of aspects 33 to 36, the mesh has an axial length and each proximal-end-loop coupling portion extends along the mesh for less than the axial length of the mesh.

[0258] Aspect 38 is the method of any of aspects 33 to 37, each proximal-end-loop coupling portion extends less than half of the axial length of the mesh.

[0259] Aspect 39 is the method of any of aspects 33 to 38, each proximal-end-loop coupling portion extends less than one third of the axial length of the mesh.

[0260] Aspect 40 is the method of any of aspects 33 to 39, in a compressed configuration, at least one proximal end loop of the set of proximal end loops extends out in a longitudinal direction from the mesh by a length approximately LPicand in a radial direction by a radius approximately RPic, and in an expanded configuration, the at least one proximal end loop of the set of proximal end loops extends in the longitudinal direction out from the mesh by a length approximately LPieand in the radial direction by a radius approximately RPie, where LPicis greater than LPieand RPieis greater than RPic.

[0261] Aspect 41 is the method of any of aspects 33 to 40, in the compressed configuration, the mesh has an average radius of Rmc, where RPic = Rmc + A, where A > 0.

[0262] Aspect 42 is the method of any of aspects 33 to 41, A is approximately equal to an average spacing between an outer surface of the mesh and an inner lumen of a catheter compressing the stent.

[0263] Aspect 43 is the method of any of aspects 33 to 36 and 40-42, the stent is a singlelayer stent, and each proximal-end-loop coupling portion extends along an entire length of the mesh.

[0264] Aspect 44 is the method of any of aspects 33 to 43, each proximal end loop of the set of proximal end loops is coupled to the mesh by a weave through or fixed to the mesh.

[0265] Aspect 45 is the method of any of aspects 33 to 44, further comprising coupling a set of distal end loops to the mesh, the set of distal end loops forming the single layer with the mesh, each distal end loop being separate from the mesh, each distal end loop having a distal-end-loop coupling portion coupled to the mesh and a distal-end-loop loop portion extending distally beyond the distal end of the mesh.

[0266] Aspect 46 is the method of any of aspects 33 to 45, each distal end loop of the set of distal end loops is formed by one wire.

[0267] Aspect 47 is the method of any of aspects 33 to 46, the mesh has an axial length and each distal-end-loop coupling portion extends along the mesh for less than the axial length of the mesh.

[0268] Aspect 48 is the method of any of aspects 33 to 47, each distal -end-loop coupling portion extends less than half of the axial length of the mesh.

[0269] Aspect 49 is the method of any of aspects 33 to 48, each distal -end-loop coupling portion extends less than one third of the axial length of the mesh.

[0270] Aspect 50 is the method of any of aspects 33 to 36 and 40-45, a proximal end loop of the set of proximal end loops and a distal end loop of the set of distal end loops are formed by one continuous wire.

[0271] Aspect 51 is the method of any of aspects 33 to 50, in a compressed configuration, at least one distal end loop of the set of distal end loops extends in a longitudinal direction from the mesh by a length approximately Laic and in a radial direction by a radius approximately Raic, in an expanded configuration, the at least one distal end loop of the set of distal end loops extends in the longitudinal direction out from the mesh by a length approximately Laie and in the radial direction by a radius approximately Raie, where Laic is greater than Laie and Raie is greater than Raic.

[0272] Aspect 52 is the method of any of aspects 33 to 51, in the compressed configuration, the mesh has an average radius of Rmc, where Raic = Rmc + A, where A > 0.

[0273] Aspect 53 is the method of any of aspects 33 to 52, A is approximately equal to an average spacing between an outer surface of the mesh and an inner lumen of a catheter compressing the stent.

[0274] Aspect 54 is the method of any of aspects 33 to 53, at least one proximal end loop of the set of proximal end loops differs from at least one distal end loop of the set of distal end loops in at least one of: an end loop deflection angle relative to a longitudinal axis of the mesh in an expanded configuration; an end loop length; a wire construction; a wire thickness; a wire material type; an amount of wires; a coupling portion interweaving pattern; a coupling mechanism; a distance to respective proximal and distal ends of the mesh; an axial length of the respective coupling portions coupled to the mesh; or a rotational orientation of the end loops.

[0275] Aspect 55 is the method of any of aspects 33 to 54, the mesh comprises one or more machine-braided interwoven wires.

[0276] Aspect 56 is the method of any of aspects 33 to 55, the mesh has a mesh density of at least 100 PPI.

[0277] Aspect 57 is the method of any of aspects 33 to 56, the one or more machine-braided interwoven wires comprise a first wire having a first wire construction and a second wire having a second wire construction, wherein the first and second wire constructions are different.

[0278] Aspect 58 is the method of any of aspects 33 to 57, the mesh and the set of proximal end loops are formed by a plurality of different material types.

[0279] Aspect 59 is the method of any of aspects 33 to 58, the set of proximal end loops is formed of drawn-filled tube (DFT).

[0280] Aspect 60 is the method of any of aspects 33 to 59, the set of proximal end loops are formed of wires that are thicker than wires forming the mesh.

[0281] Aspect 61 is the method of any of aspects 33 to 60, the mesh has a cylindrical body, and the set of proximal end loops is approximately symmetrically distributed around a circumference of the proximal end of the cylindrical body of the mesh.

[0282] Aspect 62 is the method of any of aspects 33 to 61, the mesh has a grid of pores, and a portion of each proximal end loop of the set of proximal end loops coupled to the mesh extends approximately parallel to a strand forming a pore of the grid of pores.

[0283] Aspect 63 is the method of any of aspects 33 to 62, further comprising coupling a radiopaque element to at least one of the set of proximal end loops.

[0284] Aspect 64 is the method of any of aspects 33 to 63, each proximal-end-loop coupling portion has an interweaving pattern of p x q, where for each interweave p is a number of wires over which the proximal-end-loop coupling portion extends and q is a number of wires under which the proximal-end-loop coupling portion extends, and 1 < p < 5 and 1 < q < 5.

[0285] Aspect 65. A stent, comprising: a first portion comprising a first plurality of wires and comprising a first end and a second end; a second portion comprising a second plurality of wires; wherein the second portion partially overlaps with the first portion along a first overlapping region and wherein at least a middle region of the first portion comprises a non-overlapping region; and, a first attachment mechanism between the first portion and the second portion.

[0286] Aspect 66. The stent of Aspect 65, wherein the first portion is tubular, and the second portion is tubular.

[0287] Aspect 67. The stent of any of aspect 65 or 66, wherein the first plurality of wires is braided, and the second plurality of wires is braided.

[0288] Aspect 68. The stent of any of aspects 65-67, wherein a first free end of the second portion radially increases in diameter away from a longitudinal axis of the first portion when the stent is in an expanded configuration.

[0289] Aspect 69. The stent of any of aspects 65-68, wherein the first overlapping region is within an inclusive range of about 5% to about 30% of an axial length of the first portion.

[0290] Aspect 70. The stent of any of aspects 65-69, wherein the first overlapping region is within an inclusive range of about 0.5 cm to about 5 cm from the first end.

[0291] Aspect 71. The stent of any of aspects 65-70, wherein the second plurality of wires has a diameter within an inclusive range of about 0.0001 inch to 0.001 inch; and wherein the first plurality of wires is within an inclusive range of about 0.0005 inch to about 0.1 inch.

[0292] Aspect 72. The stent of any of aspects 65-71, wherein the first attachment mechanism comprises; (i) a weld; (ii) a wire coil that wraps around one of the first plurality of braided wires and one of: the second plurality of braided wires; (iii) an adhesive; or (iv) interleaving wire between at least some of the first plurality of braided wires and at least some of the second plurality of braided wires.

[0293] Aspect 73. The stent of any of aspects 65-72, wherein the second portion is partially positioned around an exterior side of the first portion.

[0294] Aspect 74. The stent of any of aspects 65-73, wherein the second portion is partially positioned within an interior lumen the first portion.

[0295] Aspect 75. The stent of any of aspects 65-74, wherein the first plurality of braided wires of the first portion have a smaller diameter relative to the second plurality of braided wires of the second portion.

[0296] Aspect 76. The stent of any of aspects 65-75, wherein the first portion has a porosity within an inclusive range of about 0.001 inch to 0.010 inch and wherein the second portion has a porosity of about 0.1 inch or higher.

[0297] Aspect 77. The stent of any of aspects 65-76, wherein the first plurality of braided wires comprise drawn filled tubing wires, nitinol wires, or a combination of both drawing filled tubing wires and nitinol wires.

[0298] Aspect 78. The stent of any of aspects 65-77, wherein the second portion is flared at an angle relative to a longitudinal axis of the second portion of about 15 and 60 degrees relative to the longitudinal axis of the first portion when the stent is in an expanded configuration.

[0299] Aspect 79. The stent of any of aspects 65-78, further comprising a third portion comprising a third plurality of braided wires; and a second attachment mechanism connecting the first portion and the third portion along a second overlapping region at the second end; wherein the third portion radially increases in diameter away from a longitudinal axis of the first portion when the stent is in an expanded configuration.

[0300] Aspect 80. The stent of any of aspects 65-79, wherein the second overlapping region is within an inclusive range of about 0.5 cm to about 5 cm from the second tubular end.

[0301] Aspect 81. The stent of any of aspects 65-80, wherein the third portion is partially positioned around an outside of the first portion or is partially positioned within the first portion.

[0302] Aspect 82. The stent of any of aspects 65-81, wherein the second portion is partially positioned around an outside of the first portion or is partially positioned within the first portion.

[0303] Aspect 83. The stent of any of aspects 65-82, wherein the first plurality of braided wires have a smaller diameter relative to the second plurality of braided wires and relative to the third plurality of braided wires.

[0304] Aspect 84. A stent, comprising: a first plurality of wires braided into a first tubular portion; a second plurality of wires braided into a second tubular portion; wherein the second tubular portion partially overlaps a first end region of the first tubular portion without overlapping a middle region of the first tubular portion; a third plurality of wires braided into a third tubular portion; wherein the third tubular portion partially overlaps a second end region of the first tubular portion without overlapping the middle region of the first tubular portion; and, a first attachment mechanism connecting the first tubular portion and the second tubular portion, and the first tubular portion and the third tubular portion; wherein the second plurality of wires and the third plurality of wires comprise wires having a larger wire diameter than a smaller wire diameter of the wires of the first plurality of wires, and wherein the secondtubular portion and the third tubular portion have a higher porosity than the first tubular portion.

[0305] Aspect 85. The stent of aspect 84, wherein the first tubular portion has a porosity within an inclusive range of about 0.001 inch to 0.010 inch and wherein the second tubular portion has a porosity of about 0.1 inch or higher.

[0306] Aspect 86. The stent of any of aspect 84 or 85, wherein the larger wire diameter of the second plurality of wires and the third plurality of wires is within an inclusive range of about 0.0001 inch to 0.001 inch; and wherein smaller wire diameter of the first plurality of wires is within an inclusive range of about 0.0005 inch to about 0.1 inch.

[0307] Aspect 87. The stent of any of aspects 84-86, wherein the second tubular portion is partially positioned around an outside of the first tubular portion or is partially positioned within the first tubular portion; and wherein the third tubular portion is partially positioned around an outside of the first tubular portion or is partially positioned within the first tubular portion.

[0308] Aspect 88. A stent, comprising: a first tubular portion means for diverting blood flow; a second tubular portion means for anchoring the first tubular portion means; wherein the second tubular portion means partially overlaps a first end region of the first tubular portion means; and, a third tubular portion means for anchoring the first tubular portion means; wherein the third tubular portion means partially overlaps a second end region of the first tubular portion means.

[0309] Aspect 89. A method for creating a stent, comprising: braiding a first plurality of wires into a first tubular portion; braiding a second plurality of wires braided into a second tubular portion; braiding a third plurality of wires braided into a third tubular portion; and, attaching the second tubular portion so that it partially overlaps a first end region of the first tubular portion without overlapping a middle region of the first tubular portion; and, attaching the third tubular portion so that it partially overlaps a second end region of the first tubular portion without overlapping the middle region of the first tubular portion.

Claims

CLAIMSWHAT IS CLAIMED IS:

1. A stent, comprising: a mesh having a proximal end and a distal end; and a set of proximal end loops forming a single layer with the mesh, each proximal end loop being separate from the mesh, each proximal end loop having a proximal-end- loop coupling portion coupled to the mesh and a proximal-end-loop loop portion extending proximally beyond the proximal end of the mesh.

2. The stent of claim 1, wherein each proximal end loop of the set of proximal end loops is formed by one wire.

3. The stent of claim 1, wherein each proximal end loop of the set of proximal end loops is a continuous loop of wire.

4. The stent of claim 1, wherein at least one proximal end loop of the set of proximal end loops has two ends forming two wire legs, the two wire legs being the proximal-end- loop coupling portion.

5. The stent of claim 1, wherein the mesh has an axial length and each proximal-end- loop coupling portion extends along the mesh for less than the axial length of the mesh.

6. The stent of claim 5, wherein each proximal-end-loop coupling portion extends less than half of the axial length of the mesh.

7. The stent of claim 6, wherein each proximal-end-loop coupling portion extends less than one third of the axial length of the mesh.

8. The stent of claim 1, wherein in a compressed configuration, at least one proximal end loop of the set of proximal end loops extends out in a longitudinal direction from the mesh by a length approximately LPicand in a radial direction by a radius approximately Rpic, and in an expanded configuration, the at least one proximal end loop of the set of proximal end loops extends in the longitudinal direction out from the mesh by a lengthapproximately LPieand in the radial direction by a radius approximately RPie, where LPicis greater than LPieand RPieis greater than RPic.

9. The stent of claim 8, wherein in the compressed configuration, the mesh has an average radius of Rmc, where RPic = Rmc + A, where A > 0.

10. The stent of claim 9, wherein A is approximately equal to an average spacing between an outer surface of the mesh and an inner lumen of a catheter compressing the stent.

11. The stent of claim 1, wherein the stent is a single-layer stent, and each proximal- end-loop coupling portion extends along an entire length of the mesh.

12. The stent of claim 1, wherein each proximal end loop of the set of proximal end loops is coupled to the mesh by a weave through or fixed to the mesh.

13. The stent of claim 1 , further comprising a set of distal end loops forming the single layer with the mesh, each distal end loop being separate from the mesh, each distal end loop having a distal-end-loop coupling portion coupled to the mesh and a distal -end-loop loop portion extending distally beyond the distal end of the mesh.

14. The stent of claim 13, wherein each distal end loop of the set of distal end loops is formed by one wire.

15. The stent of claim 14, wherein the mesh has an axial length and each distal-end- loop coupling portion extends along the mesh for less than the axial length of the mesh.

16. The stent of claim 15, wherein each distal-end-loop coupling portion extends less than half of the axial length of the mesh.

17. The stent of claim 16, wherein each distal-end-loop coupling portion extends less than one third of the axial length of the mesh.

18. The stent of claim 13, wherein a proximal end loop of the set of proximal end loops and a distal end loop of the set of distal end loops are formed by one continuous wire.

19. The stent of claim 13, wherein in a compressed configuration, at least one distal end loop of the set of distal end loops extends in a longitudinal direction from the mesh by a length approximately Laic and in a radial direction by a radius approximately Raic, in an expanded configuration, the at least one distal end loop of the set of distal end loops extends in the longitudinal direction out from the mesh by a length approximately Laie and in the radial direction by a radius approximately Raie, where Laic is greater than Laie and Raie is greater than Raic.

20. The stent of claim 19, wherein in the compressed configuration, the mesh has an average radius of Rmc, where Raic = Rmc + A, where A > 0.

21. The stent of claim 20, wherein A is approximately equal to an average spacing between an outer surface of the mesh and an inner lumen of a catheter compressing the stent.

22. The stent of claim 13, wherein at least one proximal end loop of the set of proximal end loops differs from at least one distal end loop of the set of distal end loops in at least one of: an end loop deflection angle relative to a longitudinal axis of the mesh in an expanded configuration; an end loop length; a wire construction; a wire thickness; a wire material type; an amount of wires; a coupling portion interweaving pattern; a coupling mechanism; a distance to respective proximal and distal ends of the mesh; an axial length of the respective coupling portions coupled to the mesh; ora rotational orientation of the end loops.

23. The stent of claim 1, wherein the mesh comprises one or more machine-braided interwoven wires.

24. The stent of claim 23, wherein the mesh has a mesh density of at least 100 pores per inch (PPI).

25. The stent of claim 23, wherein the one or more machine-braided interwoven wires comprise a first wire having a first wire construction and a second wire having a second wire construction, wherein the first and second wire constructions are different.

26. The stent of claim 1, wherein the mesh and the set of proximal end loops are formed by a plurality of different material types.

27. The stent of claim 1, wherein the set of proximal end loops is formed of drawn- fi lied tube (DFT).

28. The stent of claim 1, wherein the set of proximal end loops are formed of wires that are thicker than wires forming the mesh.

29. The stent of claim 1, wherein the mesh has a cylindrical body, and the set of proximal end loops is approximately symmetrically distributed around a circumference of the proximal end of the cylindrical body of the mesh.

30. The stent of claim 1, wherein the mesh has a grid of pores, and a portion of each proximal end loop of the set of proximal end loops coupled to the mesh extends approximately parallel to a strand forming a pore of the grid of pores.

31. The stent of claim 1, further comprising a radiopaque element coupled to at least one of the set of proximal end loops.

32. The stent of claim 1, wherein each proximal-end-loop coupling portion has an interweaving pattern of p x q, where for each interweave p is a number of wires over which the proximal-end-loop coupling portion extends and q is a number of wires under which the proximal-end-loop coupling portion extends, and 1 < p < 5 and 1 < q < 5.

33. A method of manufacturing a stent, comprising: forming a mesh having a proximal end and a distal end; and coupling a set of proximal end loops to the mesh, the set of proximal end loops forming a single layer with the mesh, each proximal end loop being separate from the mesh, each proximal end loop having a proximal-end-loop coupling portion coupled to the mesh and a proximal-end-loop loop portion extending proximally beyond the proximal end of the mesh.

34. A stent, comprising: a first portion comprising a first plurality of wires and comprising a first end and a second end; a second portion comprising a second plurality of wires; wherein the second portion partially overlaps with the first portion along a first overlapping region and wherein at least a middle region of the first portion comprises a non-overlapping region; and, a first attachment mechanism between the first portion and the second portion.

35. A stent, compri sing : a first plurality of wires braided into a first tubular portion; a second plurality of wires braided into a second tubular portion; wherein the second tubular portion partially overlaps a first end region of the first tubular portion without overlapping a middle region of the first tubular portion; a third plurality of wires braided into a third tubular portion; wherein the third tubular portion partially overlaps a second end region of the first tubular portion without overlapping the middle region of the first tubular portion; and, a first attachment mechanism connecting the first tubular portion and the second tubular portion, and the first tubular portion and the third tubular portion;wherein the second plurality of wires and the third plurality of wires comprise wires having a larger wire diameter than a smaller wire diameter of the wires of the first plurality of wires, and wherein the second tubular portion and the third tubular portion have a higher porosity than the first tubular portion.

36. A stent, comprising: a first tubular portion means for diverting blood flow; a second tubular portion means for anchoring the first tubular portion means; wherein the second tubular portion means partially overlaps a first end region of the first tubular portion means; and, a third tubular portion means for anchoring the first tubular portion means; wherein the third tubular portion means partially overlaps a second end region of the first tubular portion means.

37. A method for creating a stent, comprising: braiding a first plurality of wires into a first tubular portion; braiding a second plurality of wires braided into a second tubular portion; braiding a third plurality of wires braided into a third tubular portion; and, attaching the second tubular portion so that it partially overlaps a first end region of the first tubular portion without overlapping a middle region of the first tubular portion; and, attaching the third tubular portion so that it partially overlaps a second end region of the first tubular portion without overlapping the middle region of the first tubular portion.

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