Patent Document

FIELD 
     The subject technology relates to delivery of implantable devices. 
     BACKGROUND 
     The use of endovascular techniques for the implantation of medical devices and the occlusion of body cavities such as arteries, veins, fallopian tubes or vascular deformities is known in the art. For example, occlusion of vascular aneurysms can be performed using an implantable device, such as an intrasaccular implant, which is introduced with the aid of an endovascular delivery wire through a catheter. Once moved to the treatment site, the intrasaccular implant can be moved into the aneurysm cavity to occlude the aneurysm. 
     The severance of the intrasaccular implant from the endovascular delivery wire can be particularly problematic. On the one hand, the device must be as small as possible to be guided through the fine bore of the catheter to its destination, while on the other hand it must bring about a reliable severance of the intrasaccular implant. Absent a reliable severance of the intrasaccular implant, withdrawal of the delivery wire and catheter may cause unintended removal of the intrasaccular implant from the cavity to be occluded and thus injure and/or rupture of the wall of the cavity or vessel. 
     Traditional mechanical methods for the severance of intrasaccular implants from the insertion means do not take much time to perform. However, the necessary rigidity of the technical features of the connection between the intrasaccular implant and the introduction means can impede the introduction of the implant. Furthermore, the low load carrying capacity of the connection due to its rigidity entails an appreciable risk of premature detachment of the insertion means from the occluding implant. Moreover, in the case of mechanical separation of the inserting wire and the intrasaccular implant, energy must be transmitted (e.g., by rotation of the inserting wire), which may cause the implant to be dislodged out of the correct position. 
     Traditional electrolytic severance of the intrasaccular implant involves using an electrolytically corrodible design on the end of the delivery wire at the connection between the delivery wire and the intrasaccular implant. Such a device can elegantly make use of the voltage applied to the intrasaccular implant serving as an anode for electro-thrombization. However, the connection of the implant to the delivery wire is limited by the requirements of the electrolytically corrodible region. For example, the only materials that can be utilized are those which have a sufficiently high degree of strength to enable reliable guidance of the occluding wire through the delivery wire. The selection of materials for forming the point of eventual electrolytic severance is consequently extremely limited. 
     In the case of traditional devices for the electrolytic severance of intrasaccular implants, the intrasaccular implant and the delivery wire are not produced integrally, but instead are produced mechanically connected with each other. This design has the inherent disadvantage that the delivery wire must be tapered toward its end in an involved grinding operation in order to ensure sufficient strength in the proximal zone of the delivery wire and to facilitate electrolytic, corrosive severance of the wire end in the distal part of the delivery wire. In order to ensure sufficient strength of the connection point, the corrodible zone of the end of the delivery wire must not have a diameter below a certain minimum value since it is subjected to a high flexural load. The corrodible wire end representing the connection point between the intrasaccular implant and the delivery wire can be consequently extremely rigid and require a relatively long time for electrolytic corrosive severance. 
     SUMMARY 
     Electrolytic severance of the implantable medical devices can involve using an electrolytically corrodible design on the end of a delivery wire at the connection between the delivery wire and the medical device. Such a device can elegantly make use of the voltage applied to the intrasaccular implant serving as an anode for electro-thrombization. 
     According to some embodiments, a delivery system includes an electrolytically corrodible core wire comprising a proximal portion, a distal portion, and a detachment zone between the proximal portion and the distal portion; a proximal insulating layer annularly contacting the proximal portion; a coil helically winding about and contacting at least a portion of the proximal insulating layer; a tube annularly contacting at least a portion of the helical coil; a distal insulating layer annularly contacting the distal portion; and a hub of an implant annularly contacting at least a portion of the distal insulating layer; wherein a distal end of the proximal insulating layer and a proximal end of the distal insulating layer can be axially spaced apart to expose the detachment zone. 
     The detachment zone can have an axial length that is less than 0.010 inches. The detachment zone can have an axial length greater than or equal to 0.005 inches and less than 0.010 inches. The core wire can include a distalmost end that is axially coterminous with (i) a distalmost end of the distal insulating layer and (ii) a distalmost end of the hub. The detachment zone can be axially between the proximal portion and the distal portion. The proximal portion and the distal portion each can have a microstructure with a crystallinity that is greater than a crystallinity of a microstructure of the detachment zone. The detachment zone can include a microstructure that is more amorphous than each of (i) a microstructure of the proximal portion and (ii) a microstructure of the distal portion. The core wire can provide an anchor end that is distal to a distalmost end of the hub, the anchor end having a maximum cross-sectional dimension that is greater than an inner cross-sectional dimension of a lumen of the hub. 
     According to some embodiments, a delivery system includes an electrolytically corrodible core wire comprising a proximal portion, a distal portion, and a detachment zone between the proximal portion and the distal portion; a proximal insulating layer annularly contacting a proximal portion; and a distal insulating layer annularly contacting a distal portion; wherein a distal end of the proximal insulating layer and a proximal end of the distal insulating layer can be axially spaced apart to expose the detachment zone; wherein the detachment zone comprises a microstructure that is more amorphous than each of (i) a microstructure of the proximal portion and (ii) a microstructure of the distal portion. 
     The proximal portion, the detachment zone, and the distal portion can be of a conductive material. The detachment zone can be axially between the proximal portion and the distal portion. The proximal portion and the distal portion each can have a microstructure with a crystallinity that is greater than a crystallinity of a microstructure of the detachment zone. The delivery system can further include a coil helically winding about and contacting at least a portion of the proximal insulating layer; and a tube annularly contacting at least a portion of the helical coil. The delivery system can further include a hub of an implant annularly contacting at least a portion of the distal insulating layer. The detachment zone can have an axial length that is less than 0.010 inches. The detachment zone can have an axial length greater than or equal to 0.005 inches and less than 0.010 inches. The core wire can provide an anchor end that is distal to a distalmost end of the hub, the anchor end having a maximum cross-sectional dimension that is greater than an inner cross-sectional dimension of a lumen of the hub. 
     A method of forming an assembly can include: providing an electrolytically corrodible core wire comprising a proximal portion, a distal portion, and a detachment zone between the proximal portion and the distal portion, the distal portion being attached to an implant; annularly covering the proximal portion with a proximal insulating layer; annularly covering the distal portion with a distal insulating layer; treating the detachment zone to produce a microstructure in the detachment zone that is more amorphous than each of (i) a microstructure of the proximal portion and (ii) a microstructure of the distal portion. 
     The proximal portion, the detachment zone, and the distal portion can be of a conductive material. The detachment zone can be axially between the proximal portion and the distal portion. The treating can include applying laser energy to the detachment zone. 
     Additional features and advantages of the subject technology will be set forth in the description below, and in part will be apparent from the description, or may be learned by practice of the subject technology. The advantages of the subject technology will be realized and attained by the structure particularly pointed out in the written description and claims hereof as well as the appended drawings. 
     It is to be understood that both the foregoing general description and the following detailed description are exemplary and explanatory and are intended to provide further explanation of the subject technology as claimed. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
       The accompanying drawings, which are included to provide further understanding of the subject technology and are incorporated in and constitute a part of this description, illustrate aspects of the subject technology and, together with the specification, serve to explain principles of the subject technology. 
         FIG. 1  shows a perspective view providing an overview of a treatment system, in accordance with one or more embodiments of the present disclosure. 
         FIG. 2  shows a perspective side view of a braid ball, in accordance with one or more embodiments of the present disclosure. 
         FIG. 3  shows a side-sectional view of a braid ball implant deployed within a bifurcation aneurysm, in accordance with one or more embodiments of the present disclosure. 
         FIG. 4  shows a side view of a distal end of a delivery system, in accordance with one or more embodiments of the present disclosure. 
         FIG. 5  shows a sectional view of a distal end of a delivery system, in accordance with one or more embodiments of the present disclosure. 
         FIG. 6  shows a sectional view of a distal end of a delivery system, in accordance with one or more embodiments of the present disclosure. 
         FIG. 7  shows a sectional view of a distal end of a delivery system, in accordance with one or more embodiments of the present disclosure. 
     
    
    
     DETAILED DESCRIPTION 
     In the following detailed description, specific details are set forth to provide an understanding of the subject technology. It will be apparent, however, to one ordinarily skilled in the art that the subject technology may be practiced without some of these specific details. In other instances, well-known structures and techniques have not been shown in detail so as not to obscure the subject technology. 
     In accordance with some embodiments disclosed herein is the realization that detachment of a medical device from a delivery assembly can be improved by enhancing features to focus the electrolytic corrosion activity. Thus, various embodiments provide for detachment zones that can facilitate electrolytic detachment of a delivery mechanism, making the detachment process faster and more reliable. 
     The medical device can be implanted in body cavities or blood vessels. In addition to the medical device, the delivery system can comprise a voltage source, a cathode, and a catheter. The medical device can be slid in the catheter in the longitudinal direction. A delivery wire may engage the medical device and be adapted to serve as an anode, such that a portion of the delivery wire is designed to be electrolytically corroded at one or more points so that while in contact with a body fluid, one or more portions of the medical device may be released from the delivery wire. 
     According to some embodiments,  FIG. 1  presents an overview of a treatment system  10  including an implant  20  and a handle  42 . The handle  42  shown provides proximal access to a delivery wire that engages the implant  20  at a distal end. The catheter/pusher shaft  12  can include a simple extrusion (e.g., PTFE, FEP, PEEK, etc.) or can be constructed using conventional catheter construction techniques and include a liner, braid support and outer jacket (not shown). A loading sheath  48  is typically provided over the shaft of a pusher  12 . 
     A power supply  46  may be coupled to a proximal portion of the delivery wire  44 . The power supply  46  may also be coupled to a proximal portion of the handle  42  or to the patient. A current can flow from the power supply  46 , to a detachment zone at or near the implant  20 , and to a return path via the catheter shaft  12  (and/or another structure extending near the detachment zone. Alternatively, the current from the detachment zone may flow to the patient, and subsequently to ground or to the power supply  46 . Power supply  46 , for example, may be a direct current power supply, an alternating current power supply, or a power supply switchable between a direct current and an alternating current. A positive terminal of a direct current power supply, as shown in  FIG. 1 , may be coupled to the proximal portion of the delivery wire  44  and a negative terminal of a direct current power supply may be coupled to the proximal portion of the handle  42 . Power supply  46  may provide a current through the treatment system  10  to initiate an electrolytic process during use of the assembly in a fluid medium such as a bloodstream, which may be used as an electrolyte. A power supply, such as an alternating or direct current power supply, may additionally be used to initiate an electrothrombosis process. 
     According to some embodiments, as shown in  FIGS. 2 and 3 , an implant  20  delivered by the system  10  can be a braid ball. The braid ball  20  can be formed from tubular braid stock including a resilient material, such as Nitinol, that defines an open volume (generally round, spherical, ovular, heart-shaped, etc.) in an uncompressed/unconstrained state. The size of the implant can be selected to fill an aneurysm  2 , so the proximal end  53  of the device helps direct blood flow along the surface of the braid from which it is constructed to the branch vessels  8 . A distal end  56  of the ball can be dome-shaped. The braid ball  20  can include a single layer or two layers  26 ,  28  (inner and outer layer, respectively) construction at least where impacted by flow at the neck  9  of the aneurysm  2 . As shown, one or more turns of a coil (e.g., Pt wire) or a band (not shown) can provide a distal radiopaque feature to mark the location of the implant  20 . Some exemplary implants that can be used in conjunction with the systems described herein are disclosed at U.S. Pub. No. 2013/0123830, published on May 16, 2013, the entirety of which is incorporated herein by reference. 
     According to some embodiments, the implant  20  can include a hub  50  at a proximal end  53  thereof. The hub  50  can be fixedly attached to the remainder of the implant  20 . For example, the hub  50  can grasp braided filaments of the layers  26 ,  28  of the implant  20 . The hub  50  can provide an aperture  54  for receiving engagement and release mechanisms of a delivery system. 
     According to some embodiments, the implant  20  can be set within an aneurysm sac  2  at a vascular bifurcation  4 , formed by trunk vessel  6  and efferent vessels  8 . The implant  20  can be delivered by access through the trunk vessel  6  (e.g., the basilar artery), preferably through a commercially available microcatheter with a delivery system as detailed below. To deliver the implant  20 , the pusher sleeve  12  is positioned such that the implant  20  can be delivered at least partially into the aneurysm sac  2 . After final positioning is achieved as shown in  FIG. 3 , engagement members are released from the implant  20  (e.g., from a hub  50  of the implant  20 ), as discussed further herein. Finally, the pusher sleeve  12  is withdrawn into the delivery catheter  48 . 
     While the implant  20  can be a braid ball as illustrated herein, the implant  20  can have any other form or structure, according to various embodiments. For example, the implant  20  can be a vasoocclusive coil, a cylindrical, tube-like stent, or a filter. Other types of implants are generally known. The subject technology can be applied to any such implant for delivery and detachment thereof. For example, a given implant can include a hub  50  for engagement and release by a delivery system, as disclosed further herein. 
     Traditional electrolytic detachment members are generally a single wire with a constant diameter. These detach wires are generally as drawn and are very corrosion resistant due to the crystalline structure. Generally, when these detach wires are used they will leave behind small particulates and these particulates interfere with MRI imaging and also could lead to secondary stroke if particulates flow to distal vessels. Detachment time can be reduced by concentrating erosion to a limited area. 
     According to some embodiments, as shown in  FIGS. 4 and 5 , a delivery system  10  includes an electrolytically corrodible core wire  29 , having a proximal portion  31 , a distal portion  33 , and a detachment zone  30  is between the proximal portion  31  and the distal portion  33 . At least a portion of the core wire  29 , including the detachment zone  30 , can be coated with a conductive material, such as carbon, gold, platinum, tantalum, combinations thereof, and the like. One or more metallic coatings can be applied using known plating techniques. 
     The core wire  29 , including the detachment zone  30 , can include one or more of the following materials: ceramic materials, plastics, base metals or alloys thereof, and preferably stainless steel. Some of the most suitable material combinations for forming the electrolytically corrodible points can include one or more of the following: stainless steels, preferably of the type AISI 301, 304, 316, or subgroups thereof; Ti or TiNi alloys; Co-based alloys; noble metals; or noble metal alloys, such as Pt, Pt metals, Pt alloys, Au alloys, or Sn alloys. Further, ceramic materials and plastics employed for forming the medical device can be electrically conductive. 
     According to some embodiments, portions of the core wire  29  can be coated with a nonconductive material. A proximal insulating layer  34  can be provided over at least a portion of an outer surface of the proximal portion  31  of the core wire  29 . For example, the proximal insulating layer  34  can circumferentially surround an outer surface of the proximal portion  31 . A distal insulating layer  32  can be provided over at least a portion of an outer surface of the distal portion  33  of the core wire  29 . For example, the distal insulating layer  32  can circumferentially surround and contact an outer surface of the distal portion  33 . The proximal and distal insulating layers  34 ,  32  can be of an electrically nonconductive or insulative polymer, such as polyimide, polypropylene, polyolefins, combinations thereof, and the like. 
     According to some embodiments, proximal and distal insulating layers  34 ,  32  leave exposed the detachment zone  30  of the core wire  29 . When in contact with a body fluid, such as blood, the fluid serves as an electrolyte allowing current to be focused on the non-coated detachment zone  30 . The proximal and distal insulating layers  34 ,  32  prevent exposure of the proximal portion  31  and distal portion  33  to the fluid. Accordingly, electrical energy conducted along the core wire  29  is concentrated at the detachment zone  30 , thereby reducing the time required to erode away the detachment zone  30 . The proximal and distal insulating layers  34 ,  32  can be over-molded, co-extruded, sprayed on, or dip-coated with respect to the core wire  29 . 
     Laser ablation can be employed to selectively remove the coating to a controlled length minimizing the time required to erode through the component. Lengths as small as 0.0005″ and as large as 0.1″ or longer can be removed. According to some embodiments, lengths of detachment zone  30  can be greater than 0.005″ and/or less than 0.010″ to provide sufficient exposure to achieve detachment times of less than 30 seconds. 
     According to some embodiments, the distal insulating layer  32  is disposed radially between the distal portion  33  of the core wire  29  and the hub  50  of an implant  20 . As shown in  FIG. 5 , an inner band  52  of the hub  50  circumferentially surrounds and contacts the distal insulating layer  32 . An outer band  51  surrounds the inner band  52 , such distal portions of the layers  26 ,  28  of the implant  20  are grasped between the inner and outer bands  52 ,  51  of the hub  50 . 
     As shown in  FIG. 5 , the distal insulating layer  32  electrically isolates the implant  20  from an electrical charge conducted along a length of the core wire  29 . A proximal end of the distal insulating layer  32  may be positioned proximal to the hub  50 , and a distal end of the distal insulating layer  32  may be positioned distal to the hub  50 . Likewise, a proximal end of the distal portion  33  may be positioned proximal to the hub  50 , and a distal end of the distal portion  33  may be positioned distal to the hub  50 , such that the distal portion  33  extends through and distally beyond a lumen formed by the hub  50 . Alternatively, the proximal end of the distal insulating layer  32  may be coterminous with a proximal end of the hub  50 , and/or a distal end of the distal insulating layer  32  may be coterminous with a distal end of the hub  50 . Likewise, the proximal end of the distal portion  33  may be coterminous with a proximal end of the hub  50 , and/or a distal end of the distal portion  33  may be coterminous with a distal end of the hub  50 . 
     According to some embodiments, a distal marker coil  36  is wound helically about an outer surface of the proximal insulating layer  34 . The distal marker coil  36  can be of a radiopaque material, such as platinum, gold, palladium, iridium, and alloys thereof. The distal marker coil  36  terminates at a proximal end thereof adjacent to a core wire end cap  60 . The distal marker coil  36  can be between about 10 and about 40 mm in length, for example, about 30 mm. The distal marker coil  36  can be attached to the core wire end cap  60  by one or more welds  62 . The core wire end cap  60  can be in physical contact and electrical conduction with the core wire  29 . 
     An insulative layer  38  can be provided about an outer surface of the distal marker coil  36 . For example, as shown in  FIG. 5 , the insulative layer  38  can extend over an entire length of the distal marker coil  36  and distally beyond the distal marker coil  36 , such that every portion of the distal marker coil  36  is covered by the insulative layer  38 . A distal end of the insulative layer  38  may contact and/or be adhered to the proximal insulating layer  34 . The insulative layer  38  can be of an insulative biocompatible polymer material, such as polytetrafluoroethylene (PTFE). The insulative layer  38  may be shrink-wrapped over the corresponding portion of the delivery wire  10 . 
     The distal marker coil  36  terminates at a proximal end thereof adjacent to a core wire end cap  60 . The distal marker coil  36  can be attached to the core wire end cap  60  by one or more welds  62 . The core wire end cap  60  can be attached to a pusher wire end cap  70 , located at a distal end of a pusher wire  74 . 
     According to some embodiments, a proximal marker coil  66  is wound helically about an outer surface of the pusher wire  74 . The proximal marker coil  66  can be of a radiopaque material, such as platinum, gold, palladium, iridium, and alloys thereof. The proximal marker coil  66  terminates at a distal end thereof adjacent to the pusher wire end cap  70 . The proximal marker coil  66  can be about 1 mm in length. The proximal marker coil  66  can be attached to the pusher wire end cap  70  by one or more welds  64 . The pusher wire end cap  70  can be in physical contact and electrical conduction with the pusher wire  74 . The pusher wire end cap  70  and the core wire end cap  60  can be connected by an interface  68  (e.g., a weld), configured to provide an electrically conductive connection between the pusher wire end cap  70  and the core wire end cap  60 . Furthermore, an interface  68  can provide sufficient column strength to transfer an axial force applied to the pusher wire  74  to the proximal portion  31  of the core wire  29 . 
     According to some embodiments, an insulative cover  72  can be provided about an outer surface of the proximal marker coil  66 . For example, as shown in  FIG. 5 , the insulative cover  72  can extend over an entire length of the proximal marker coil  66  and proximally beyond the proximal marker coil  66 , such that every portion of the proximal marker coil  66  is covered by the insulative cover  72 . A distal end of the insulative cover  72  may contact and/or be adhered to the pusher wire  74 . The insulative cover  72  can be of an insulative biocompatible polymer material, such as polytetrafluoroethylene (PTFE). The insulative cover  72  may be shrink-wrapped over the corresponding portion of the delivery wire  10 . The insulative cover  72  can be adjacent to or integral with the insulative layer  38 . A cover  76  may be provided over at least a portion of the delivery wire  10 , including portions of the insulative layer  38  and the insulative cover  72 . 
     According to some embodiments, as shown in  FIG. 6 , a pusher wire  74  can be integrally connected to the proximal portion  31  of the core wire  29 . Accordingly, an electric charge applied to the pusher wire  74  can be conducted through the pusher wire  74 , the proximal portion  31  of the core wire  29 , and the detachment zone  30 . Furthermore, an axial force applied to the pusher wire  74  can result in an axial movement of the core wire  29  and the implant  20 . 
     According to some embodiments, as shown in  FIG. 7 , the core wire  29  can include an anchor end  27  at a terminal distal end of the core wire  29 . The anchor end  27  can be located distal to the hub  50 . For example, the anchor end  27  can be located within an interior portion of the implant  20 . The anchor end  27  can have a maximum cross-sectional dimension that is greater than an inner cross-sectional dimension of the inner band  52 . Accordingly, the core wire  29  is prevented from moving proximally entirely through the inner band  52 . For example, an interface between the distal insulating layer  32  and the inner band  52  or an interface between the distal insulating layer  32  and the core wire  29  may allow a degree of movement of the core wire  29  relative to the inner band  52 . To prevent the core wire  29  from being removed distally from within the inner band  52 , the anchor end  27  can be of a size that cannot pass entirely proximally through the inner band  52 . 
     According to some embodiments, a detachment zone  30  can be configured such that the corrodible portion thereof defines a unique structure configured to enhance electrolytic corrosion while preserving the structural characteristics thereof, A reduction in corrosion resistance will reduce a time required to deploy an intravascular and/or intrasaccular implant, thus reducing the overall procedure time. According to some embodiments, corrosion resistance of detachment zone  30  is decreased by exposure to laser or other energy, causing the detachment zone  30  to be structurally modified by heat. As a result, the detachment zone  30  will have a different microstructure than the material outside of the zone (e.g., the proximal portion  31  and/or the distal portion  33  of the core wire  29 ). The result will decrease the time to electrolytically plate off the material, resulting in faster detachment times. 
     The laser energy will create surface defects for a reduction in corrosion resistance. The laser energy will also alter the microstructure at a specific area, leading to a non-uniform corrosion rate. Accordingly, the preferred corrosion site can have a faster detach time. 
     According to some embodiments, the proximal portion  31  and/or the distal portion  33  have a microstructure with a crystallinity that is greater than a crystallinity of a microstructure of the detachment zone  30 . According to some embodiments, the detachment zone  30  comprises a microstructure that is more amorphous than each of (i) a microstructure of the proximal portion  31  and (ii) a microstructure of the distal portion  33 . According to some embodiments, a method of treating a delivery system includes providing an electrolytically corrodible core wire  29  comprising a proximal portion  31 , a distal portion  33 , and a detachment zone  30  between the proximal portion  31  and the distal portion  33 . The detachment zone  30  is treated to produce a microstructure in the detachment zone  30  that is more amorphous than each of (i) a microstructure of the proximal portion  31  and (ii) a microstructure of the distal portion  33 . 
     According to some embodiments, a detachment zone  30  can be configured such that the corrodible portion thereof defines a unique surface structure or texture configured to enhance electrolytic corrosion while preserving the structural characteristics thereof. 
     For example, the cross-sectional profile of the detachment zone can define at least one concavity, valley, recess, and/or indentation formed therein. In accordance with some embodiments, the cross-sectional profile of the detachment zone can define areas of positive curvature, such as one or more peaks, protrusions, and/or convexities, with areas of negative curvature, such as one or more valleys, recesses, concavities, and/or indentations. The one or more peaks, protrusions, and/or convexities and the one or more valleys, recesses, concavities, or indentations can be formed from surface structures such as grooves, channels, pits, threads, elongate troughs, circumferential or annular grooves, slots, apertures, coils, crimped ribbon, slotted ribbon, perforated ribbon, and/or other such structures that are precisely or randomly arranged. The shape of the cross-sectional profile of the connector body can be defined by one or more linear edges, parallel linear edges, intersecting linear edges, continuous curves, and/or combinations thereof. 
     By providing a surface structure or texture, some embodiments can thereby provide an increased surface area of the detachment zone in order to enhance the contact area of the component  206 , reduce the overall volume of the detachment zone, and thereby improve the rate of corrosion. Further, various embodiments can be provided that are configured to provide excellent structural characteristics in order to ensure that the detachment zone is sufficiently robust and durable. 
     For example, in some embodiments, the component can have a component body comprising at least one structure, such as a trough, valley, recess, concavity, or indentation defining a recess surface area. In accordance with some embodiments, the component can be configured such that the valley, recess, concavity, or indentation can be used in the component without reducing structural characteristics of the component. 
     Further, the structure of the detachment zone can add recess surface area to the overall surface area of the detachment zone, thereby enhancing electrolytic corrosion of the detachment zone. Thus, the ratio of surface area to volume of the detachment zone can increase with an increase in overall surface area and a decrease in volume of the component. As discussed herein, the increase in the overall surface area of the detachment zone can be achieved by the incremental addition of surface area of the structure (e.g., the valley, recess, concavity, or indentation) versus the surface area of a surface without such a structure (e.g., a planar surface). The decrease in volume can be achieved by the addition of the void created by the valley, recess, concavity, or indentation. 
     Additionally, the detachment zone can be fabricated to provide features that will lead to an increased current density in one or more areas of the detachment zone. Such features can include, for example, ridges, edges, small radius corners, valleys, troughs, concavities, recesses, indentations, and/or other structures. In some embodiments, the presence of some of these structures on the detachment zone can reduce the local cross sectional area and/or otherwise contribute to the galvanic reaction. Features that increase current density can accelerate the galvanic reaction. 
     Additionally, according to some embodiments, the electrolytically corrodible detachment zone can be fabricated using a mechanical cold working operation. The cold working of the detachment zone can be performed through operations such as stamping, drawing, squeezing, bending, and/or other processes. The cold working of the detachment zone can enhance the galvanic reaction or corrosion. For example, as discussed herein, the detachment zone can comprise one or more structures or have a cross section that increases the surface area to volume ratio, which can enhance the galvanic reaction. Further, the process of cold working can alter the material properties of the detachment zone, which can improve the anodic quality or corrodibility of the detachment zone. Cold working can induce stresses in the material of the detachment zone, which can be released during the galvanic reaction, thus facilitating the galvanic reaction. Thus, fabrication of the detachment zone through a cold working operation can further enhance the galvanic reaction. 
     Furthermore, in accordance with some embodiments, the body of detachment zone can comprise a hollow portion that extends at least partially along the length of the body of detachment zone. The hollow portion can be formed as a discrete bubble or as an internal tubular vacuity extending within the body of detachment zone. In accordance with some embodiments, the tubular vacuity can extend longitudinally within the body of detachment zone. The hollow portion can define one or more sections that are exposed or open to an exterior of the connector body. Accordingly, in such embodiments, the rate of corrosion can be enhanced. Further, it is possible to thereby provide one or more areas where corrosion can be accelerated significantly as the corrosion process reaches the hollow portion(s) of the body of detachment zone. As such, one or more hollow portions can be present at one or more sections or points along the body of detachment zone. 
     Accordingly, in some embodiments, the presence of the surface structure(s) on the detachment zone can provide an increased ratio of surface area to volume, compared to a detachment zone that does not have such a structure. Thus, with a higher ratio of surface area to volume, the galvanic reaction can be faster, more predictable, and more effective for some embodiments. 
     Further, in some embodiments, the presence of a surface feature(s) on the detachment zone can provide increased current density at such feature(s), compared to a detachment zone that does not have such a feature(s). With a higher current density, the galvanic reaction can be faster, more predictable, and more effective for some embodiments. 
     Other features and discussion of electrolytically corrodible connections is provided in other applications of the present assignee, including the discussion and disclosure of U.S. Patent Application Publication No. 2012/0010648 and U.S. Pat. Nos. 7,323,000, and 8,048,104, the entirety of each of which is incorporated herein by reference. 
     Electrolytically non-corrodible sections of the delivery wire  44  can contain one or more of the following materials: noble metals or noble metal alloys, corrosion-resistant ceramic materials, corrosion-resistant plastics, and preferably platinum metal alloys. 
     The use of the above mentioned materials for the formation of electrolytically non-corrodible sections and of the electrolytically corrodible flanges ensures specific electrolytic corrosion of the flanges at the predetermined points. 
     In accordance with some embodiments, the electrolytically corrodible detachment zone can also be pre-corroded by etching or other methods. Thus, the structure(s) of a given cross-sectional profile can be modified to reduce the presence of corners, increase the recess depth, and/or otherwise enhance the corrosion rate. Further, various excellent structural designs can be provided to achieve desired corrosion performance through the teachings disclosed herein without pre-corrosion of the corrodible points. 
     Some embodiments can include a corrodible detachment zone that has a partial coating of a material to provide a greater or lesser electrochemical resistance. Thus, in embodiments that have one or more corrodible points, the electrochemical resistance of the points can be varied to achieve staged or preferential electrochemical resistance. Coatings of Zn, Sn, or alloys of such metals on fittings of stainless steel have been found to be particularly satisfactory. Further, some embodiments, the end of the delivery wire can be insulated, for example, by a material coating with reduced corrosion properties or a shrunk-on sleeve to improve its electrochemical resistance. 
     Embodiments disclosed herein can be used in veterinary or human medicine and more particularly, for the endovascular treatment of intracranial aneurysms and acquired or innate arteriovenous blood vessel deformities and/or fistulas and/or for the embolization of tumors by thrombozation. 
     The apparatus and methods discussed herein are not limited to the deployment and use of an occluding device within any particular vessels, but can include any number of different types of vessels. For example, in some aspects, vessels can include arteries or veins. In some aspects, the vessels can be suprathoracic vessels (e.g., vessels in the neck or above), intrathoracic vessels (e.g., vessels in the thorax), subthoracic vessels (e.g., vessels in the abdominal area or below), lateral thoracic vessels (e.g., vessels to the sides of the thorax such as vessels in the shoulder area and beyond), or other types of vessels and/or branches thereof. 
     In some aspects, the stent delivery systems disclosed herein can be deployed within superthoracic vessels. The suprathoracic vessels can comprise at least one of intracranial vessels, cerebral arteries, and/or any branches thereof. In some aspects, the stent delivery systems disclosed herein can be deployed within intrathoracic vessels. The intrathoracic vessels can comprise the aorta or branches thereof. In some aspects, the stent delivery systems disclosed herein can be deployed within subthoracic vessels. In some aspects, the stent delivery systems disclosed herein can be deployed within lateral thoracic vessels. 
     The foregoing description is provided to enable a person skilled in the art to practice the various configurations described herein. While the subject technology has been particularly described with reference to the various figures and configurations, it should be understood that these are for illustration purposes only and should not be taken as limiting the scope of the subject technology. 
     There may be many other ways to implement the subject technology. Various functions and elements described herein may be partitioned differently from those shown without departing from the scope of the subject technology. Various modifications to these configurations will be readily apparent to those skilled in the art, and generic principles defined herein may be applied to other configurations. Thus, many changes and modifications may be made to the subject technology, by one having ordinary skill in the art, without departing from the scope of the subject technology. 
     A phrase such as “an aspect” does not imply that such aspect is essential to the subject technology or that such aspect applies to all configurations of the subject technology. A disclosure relating to an aspect may apply to all configurations, or one or more configurations. An aspect may provide one or more examples of the disclosure. A phrase such as “an aspect” may refer to one or more aspects and vice versa. A phrase such as “an embodiment” does not imply that such embodiment is essential to the subject technology or that such embodiment applies to all configurations of the subject technology. A disclosure relating to an embodiment may apply to all embodiments, or one or more embodiments. An embodiment may provide one or more examples of the disclosure. A phrase such “an embodiment” may refer to one or more embodiments and vice versa. A phrase such as “a configuration” does not imply that such configuration is essential to the subject technology or that such configuration applies to all configurations of the subject technology. A disclosure relating to a configuration may apply to all configurations, or one or more configurations. A configuration may provide one or more examples of the disclosure. A phrase such as “a configuration” may refer to one or more configurations and vice versa. 
     It is understood that the specific order or hierarchy of steps in the processes disclosed is an illustration of exemplary approaches. Based upon design preferences, it is understood that the specific order or hierarchy of steps in the processes may be rearranged. Some of the steps may be performed simultaneously. The accompanying method claims present elements of the various steps in a sample order, and are not meant to be limited to the specific order or hierarchy presented. 
     As used herein, the phrase “at least one of” preceding a series of items, with the term “and” or “or” to separate any of the items, modifies the list as a whole, rather than each member of the list (i.e., each item). The phrase “at least one of” does not require selection of at least one of each item listed; rather, the phrase allows a meaning that includes at least one of any one of the items, and/or at least one of any combination of the items, and/or at least one of each of the items. By way of example, the phrases “at least one of A, B, and C” or “at least one of A, B, or C” each refer to only A, only B, or only C; any combination of A, B, and C; and/or at least one of each of A, B, and C. 
     Terms such as “top,” “bottom,” “front,” “rear” and the like as used in this disclosure should be understood as referring to an arbitrary frame of reference, rather than to the ordinary gravitational frame of reference. Thus, a top surface, a bottom surface, a front surface, and a rear surface may extend upwardly, downwardly, diagonally, or horizontally in a gravitational frame of reference. 
     Furthermore, to the extent that the term “include,” “have,” or the like is used in the description or the claims, such term is intended to be inclusive in a manner similar to the term “comprise” as “comprise” is interpreted when employed as a transitional word in a claim. 
     The word “exemplary” is used herein to mean “serving as an example, instance, or illustration.” Any embodiment described herein as “exemplary” is not necessarily to be construed as preferred or advantageous over other embodiments. 
     A reference to an element in the singular is not intended to mean “one and only one” unless specifically stated, but rather “one or more.” Pronouns in the masculine (e.g., his) include the feminine and neuter gender (e.g., her and its) and vice versa. The term “some” refers to one or more. Underlined and/or italicized headings and subheadings are used for convenience only, do not limit the subject technology, and are not referred to in connection with the interpretation of the description of the subject technology. All structural and functional equivalents to the elements of the various configurations 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 intended to be encompassed by the subject technology. Moreover, nothing disclosed herein is intended to be dedicated to the public regardless of whether such disclosure is explicitly recited in the above description. 
     While certain aspects and embodiments of the subject technology have been described, these have been presented by way of example only, and are not intended to limit the scope of the subject technology. Indeed, the novel methods and systems described herein may be embodied in a variety of other forms without departing from the spirit thereof. The accompanying claims and their equivalents are intended to cover such forms or modifications as would fall within the scope and spirit of the subject technology.

Technology Category: 1