Patent Publication Number: US-2023160116-A1

Title: Atraumatic stent and method and apparatus for making the same

Description:
CROSS-REFERENCE TO RELATED APPLICATIONS 
     This application is a continuation of U.S. application Ser. No. 17/181,474, filed Feb. 22, 2021; which is a continuation of U.S. application Ser. No. 16/364,772, filed Mar. 26, 2019, now U.S. Pat. No. 10,947,651; which is a continuation of U.S. application Ser. No. 15/204,508, filed Jul. 7, 2016, now U.S. Pat. No. 10,278,842; which is a continuation of U.S. application Ser. No. 14/096,307, filed Dec. 4, 2013, issued as U.S. Pat. No. 9,388,517; which is a continuation of U.S. application Ser. No. 13/912,445, filed Jun. 7, 2013, issued as U.S. Pat. No. 8,677,874; which is a continuation of U.S. application Ser. No. 13/441,649, filed Apr. 6, 2012, issued as U.S. Pat. No. 8,459,164; which is a continuation of U.S. application Ser. No. 12/630,068, filed on Dec. 3, 2009, issued as U.S. Pat. No. 8,151,682; which claims priority to U.S. Provisional Application No. 61/147,307, filed Jan. 26, 2009; the content of each incorporated herein by reference. 
    
    
     FIELD OF THE INVENTION 
     The present invention is related to an atraumatic stent and methods, apparatus and systems for making the same. More particularly, the present invention is related to an atraumatic braided stent and braiding methods, braiding mandrels and braiding machines for making the same. 
     BACKGROUND OF THE INVENTION 
     Braided stents have typically been braided on a smooth mandrel. The ends of the braiding wires were typically gathered beyond an end of a braiding mandrel, and the wires where then secured, typically by tying or taping, to the mandrel end portion, after which braiding, either by hand or machine, commenced. 
     The braiding angle was controlled by the angle at which the stent wires were disposed over the mandrel. Many stents, however, use metallic wires which may shift or move during braiding as a result of forces imparted on the wires during the braiding. This may result in a variation of the braiding angle though the stent, in particular for stents braided with varied diameters, such as flared, flanged and/or tapered stents. Variation in the braiding angle may result in undesirable variation of radial expansion or compression forces or deployment forces of the so formed stent. Such variations may also affect the consistency of the size of the openings, e.g., cell size, across the stent. 
     Wire used in the fabrication of the stent is generally fed from a spool onto the mandrel. In this manner, multiple stents could be formed by feeding enough material to the mandrel during the braiding process and thereafter cutting the resulting long stent into multiple smaller stents. After braiding the long stent, the wire portions gathered beyond the mandrel end were trimmed. The trimming of such excess wire needlessly wastes material. As many early stents were braided simply with stainless steel wires, the cost of discarding this excess wire material was minimal. More recently, however, stent wires of more expensive materials, such as nitinol or composite nitinol have been used. The cost of the discarded material has become much more costly. 
     Thus, there is a need in the art to provide a method for braiding a stent where material costs are minimized and where variations in the stent configuration, including braiding angle, are also minimized. Further, there is a need in the art to provide a method for braiding a stent with atraumatic ends from discrete wire lengths so that the braiding angle(s) of the stent and the size and orientation of the atraumatic ends are controllably provided to produce atraumatic stents with consistency while allowing for mass production of the atraumatic stents. Moreover, there is a need optimize stent manufacturing to more tightly control stent specifications, including optimizing material control and including ability to create any specific quantity of custom stents as desired. 
     SUMMARY OF THE INVENTION 
     The present invention provides braiding methods, braiding mandrels, braiding machines and braided stents which avoid and solve the undesirable concerns of the prior art. The braided stents of the present invention have a substantially controlled braiding angle, including a substantially constant braiding angle, if desired, throughout its longitudinal expanse, including portions having varied diameters, such as tapered portions, flared portions and/or flanged portions. For example, a substantially constant braiding angle, for example but not limited to 110°, may be desired throughout the longitudinal expanse of a stent, including portions having varied diameters. Additionally, the braided stents of the present invention may have varied diameter portions where the braiding angle is controllably different in one varied diameter portion as compared to another varied diameter portion and/or is controllably different in one or more varied diameter portions as compared to the longitudinal expanse of the stent. Further, the controlled braiding angle of the inventive stent may vary from one angle, for example but not limited to 90°, at one end, to a different angle, for example but not limited to 120°, at an opposed second end where not only the end angles but also all of the transition angles between the opposed ends are controlled. Such inventive stents are produced by methods and devices of the present invention which include, inter alia, braiding mandrels having specifically designed grooves and projections and constant force braiding carriers for tangentially delivering stent filaments for braiding the filaments onto such specifically designed mandrels. 
     In one embodiment of the present invention, a method of braiding a stent is provided. The method may include the steps of (a) providing a number of elongate filaments, each of the filaments having opposed ends and an intermediate portion between the opposed ends; (b) providing a number of tensioned braiding carriers; (c) providing a braiding mandrel having opposed proximal and distal ends, the braiding mandrel comprising a number of circumferentially spaced-apart securement projections at the distal end of the braiding mandrel; (d) securably disposing the intermediate portion of one of the filaments to one of the securement projections; (e) securing one of the opposed ends of the one filament to one of the tensioned braiding carriers without spooling the one filament to the one constant force braiding carrier; (f) securing the other opposed end of the one filament to a different second tensioned braiding carrier without spooling the one filament to the second tensioned braiding carrier; (g) repeating steps (d) through (f) until all of the intermediate portions of the filaments are securably disposed to different ones of the securement projections and until each end of the number of filaments are secured to a different one of the tensioned braiding carriers; (h) moving the constant force carriers around the mandrel, for example in a generally circular and serpentine motion; and (i) longitudinally advancing the mandrel in a direction substantially perpendicular to the motion of the constant force carriers to braid the filaments to form a braided stent. Advancing the mandrel may include moving the mandrel with respect to the perpendicular motion of the tensioned braiding carriers, moving the tensioned braiding carriers longitudinally with respect to the mandrel, and combinations thereof. The tensioned braiding carriers each may include a retractable carrier filament for releasably securing a stent filament thereto. The tensioned braiding carriers each may also include a wheel around which the retractable carrier filament may be coiled. 
     In another embodiment of the present invention, a method for braiding a stent comprises the steps of (a) providing a number of elongate filaments, each of the filaments having opposed ends and an intermediate portion between the opposed ends; (b) providing a number of braiding carriers; (c) providing a braiding mandrel having opposed proximal and distal ends, the braiding mandrel comprising a number of circumferentially spaced-apart securement projections at the distal end, the mandrel further comprising a plurality of grooves; (d) securably disposing the intermediate portion of one of the filaments to one of the securement projections at the distal end of the mandrel; (e) securing one of the opposed ends of the one filament to one of the braiding carriers; (f) securing the other opposed end of the one filament to a different second braiding carrier; (g) repeating steps (d) through (f) until all of the intermediate portions of the filaments are securably disposed to different ones of the securement projections and until each end of the number of filaments are secured to a different one of the braiding carriers; (h) moving the braiding carriers around the mandrel, for example in a generally circular and serpentine motion; (i) longitudinally advancing the mandrel relative to a direction substantially perpendicular to the motion of the braiding carriers to braid the filaments to form a braided stent; and (j) applying a constant tension force from the braiding barriers to the filaments during the braiding steps (h) through (i). 
     In yet another embodiment of the present invention, a method for braiding a stent comprises the steps of (a) providing a number of elongate filaments, each of the filaments having opposed ends and an intermediate portion between the opposed ends; (b) providing a number of tensioned braiding carriers; (c) providing a braiding mandrel having opposed proximal and distal ends, the braiding mandrel comprising a number of circumferentially spaced-apart securement projections at the distal end, the braiding mandrel further comprising a plurality of grooves; (d) securably disposing the intermediate portion of one of the filaments to one of the securement projections at the distal end of the braiding mandrel; (e) securing one of the opposed ends of the one filament to one of the tensioned braiding carriers without spooling the one filament to the one tensioned braiding carrier; (f) securing the other opposed end of the one filament to a different second tensioned carrier without spooling the one filament to the second tensioned carrier; (g) repeating steps (d) through (f) until all of the intermediate portions of the filaments are securably disposed to different ones of the securement projections and until each end of the number of filaments are secured to a different one of the tensioned carriers; (h) moving the tensioned carriers around the mandrel, for example in a generally circular and serpentine motion; and (i) longitudinally advancing the mandrel relative to a direction substantially perpendicular to the motion of the tensioned carriers to braid the filaments by tangentially disposing the filaments into the grooves to braid the filaments to form a braided stent. 
     In a still further embodiment of the present invention, a braided stent is provided. The braided stent comprises a plurality of elongate filaments inter-braided to form a tubular well structure, the filaments being inter-braided at a braiding angle formed at crossing filament locations; the tubular wall structure comprising a first portion having a first diameter, a second portion having a second diameter which is different from the second diameter and a transition portion disposed between the first portion and the second portion; wherein the braiding angles in the first portion, the second portion and the transition portion are substantially equal. Alternatively, the braiding angles of these portions may be different, but nevertheless controlled. Moreover, the stents of the present invention are not limited to those having a varied diameter and/or flared or flanged portions. A constant diameter or substantially constant diameter may also be provided. Such a constant or substantially constant diameter stent may have improved tolerances, i.e., fewer variations, of cell configuration, for example braiding angles, cell size and the like. 
     Further, a braiding mandrel for braiding the tubular stent of the present invention desirably comprises an elongate tubular member having opposed proximal and distal ends; securement projections circumferentially disposed at spaced-apart locations at the distal end for engaging a filament from a braiding machine; a plurality of annular or annular disposed grooves along the longitudinal length of the member. The grooves may extend at an angle from about 5° to about 85° from a longitudinal axis of the member. 
     Use of the optimized braiding techniques and braiding components of the present invention allow a manufacturer to make a customized stent. Such a customized stent may be specific to any one set of specifications, including but not limited to braiding angle, stent diameter, stent length, stent shape and then like. Moreover, such customized stents may be produced with optimized manufacturing techniques, thereby providing customized stents with improved quality control as compared to the prior art. 
     These and other features and advantages of the present invention will become apparent from the following detailed description of illustrative embodiments thereof, which is to be read in connection with the accompanying drawings. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         FIG.  1    is a side elevational schematic view of braiding machine of the present invention. 
         FIG.  2    is a front view of the braiding machine of  FIG.  1    taken along the 2-2 axis. 
         FIG.  3    is an alternate embodiment of the braiding machine of  FIG.  2   . 
         FIG.  4 A  depicts a stent according to the present invention. 
         FIG.  4 B  is an exploded view of the stent of  FIG.  4 A  illustrating a one-under and one-over braiding configuration. 
         FIG.  4 C  is an exploded view of the stent of  FIG.  4 A  illustrating a two-under and two-over braiding configuration. 
         FIG.  4 D  is an exploded view of the stent of  FIG.  4 A  illustrating a pair of filaments in a one-under and one-over braiding configuration. 
         FIG.  5    is a side elevational view of the braiding mandrel of the present invention. 
         FIG.  6    depicts a braiding mandrel having a substantially constant diameter according to the present invention. 
         FIG.  7    is an exploded view of a portion of the mandrel of  FIG.  5    depicting the raised mandrel projections. 
         FIGS.  8 - 10    depict details of the raised mandrel projections of  FIG.  7   . 
         FIG.  11    is an exploded view of a portion of the distal end of the braiding mandrel of  FIG.  5  or  6    depicting raised projection on the distal end. 
         FIG.  12    is a top view of a raised projection of  FIG.  11   . 
         FIG.  13    depicts the braiding mandrel having middle portions of the stent filaments secured to the raised projections. 
         FIG.  14    depicts stent filaments being braided over the mandrel of the present invention. 
         FIG.  15    is an exploded view of the proximal end of the braiding mandrel of the present invention. 
         FIGS.  16 A and  16 B  are partial exploded views of a transitional portion of the braiding mandrel of the present invention. 
         FIG.  17    depicts a braiding mandrel of the present which is free of the raised projections. 
         FIGS.  18 - 21    illustrate alternate embodiments for securing stent filaments at the distal end of the braiding mandrel. 
         FIG.  22    is a schematic depiction of a constant force carrier of the present invention. 
         FIG.  23    is a schematic of a clip mentioned in  FIG.  1   . 
         FIG.  24    is a schematic of an alternate embodiment of a constant force bobbin carrier of the present invention. 
         FIG.  25    is a schematic of a method of forming the stent of the present invention. 
         FIG.  26    is a schematic of another method of forming the stent of the present invention. 
     
    
    
     DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS 
       FIG.  1    is a side elevational schematic view of braiding machine  10  of the present invention. Certain features of the braiding machine  10 , such as motors, controls, safety features, etc., are not shown for simplicity. The braiding machine  10  of the present invention, however, may suitably include such features without limitation. Braiding machine  10  includes a number of notch gears  12 . Each notch gear  12  may include a one or more, typically a pair of, tensioned or constant force braiding carriers  14  disposed thereon. The tensioned or constant force braiding carriers  14  have a retractable carrier filament  16 . The retractable carrier filament  16  is releasably secured to a stent-forming filament  20  via a clip  18 . The stent-forming filaments  20  are braided over a mandrel  22  to form a stent  24  of the present invention. 
     The stent-forming filaments  20  are braided typically in a one-over and one-under pattern to form a braided tubular structure, i.e., stent  24 . Other braiding arrangements are possible, including but not limited to those depicted in  FIGS.  4 C and  4 D . The braiding operation is schematically depicted in  FIG.  2   , which is a front view of the braiding machine  10  of  FIG.  1    taken along the 2-2 axis. Note that as used herein the term braiding includes weaving and the like.  FIG.  2    depicts the braiding machine  10  as having twenty notch gears  12  arranged in a generally circular configuration  26 . The number of notch gears  12  used with the braiding machine  10  is not limited to twenty and any suitable number of notch gears  12  may be used. Each notch gear  12  is adapted to rotate in the opposite direction as its neighboring notch gear  12 , as illustrated by arrows A and B in  FIG.  2   . This counter-rotation movement of the notch gears  12  passes the braiding carriers  14  in a sinusoidal fashion from one notch gear  12  to an adjacent or juxtaposed notch gear  12 , thus causing the carriers  14  to revolve, or move in a circumferential manner, about a longitudinal axis L on which the circle of notch gears  12  is desirably centered. The circular configuration  26  of the notch gears  12  and carriers  14  achieve a generally circular but sinusoidal movement of the carriers  14  to braid the filaments  20  over the mandrel  22  in a one-over and one-under fashion to form the stent  24 . 
     As depicted in  FIG.  3   , not every carrier  14  need have a filament  16 ,  20  disposed there with. For example, carriers  14 ′ may not have a filament  16 ,  20  while carriers  14  may have the filaments  16 ,  20 . In such a manner, the number of filaments  20  making the stent  24  may be altered while using the same braiding machine  10 . 
     During braiding, the mandrel  22 , around which braided stent  24  is formed, is moved in a controlled manner substantially along a longitudinal axis L about which the circle  26  of notch gears  12  is centered and about which the carriers  14  revolve.  FIG.  1    illustrates, from the side, such a configuration. During braiding, filaments  20  extend from the braiding machine  10  to the mandrel  22  in a generally conical configuration, as shown in  FIG.  1   . The present invention, however, is not so limited. For example, as an alternative or in addition to, the mandrel may stay fixed in place and the braiding or weaving machine may be moved the length of the mandrel. 
     As illustrated in  FIG.  2   , as two carriers  14  cross one another along their generally circular but sinusoidal movement, their respective filaments  20  form an overlap such that the filament  20  associated with a carrier  14  on the outer radius  28  of the circle  26  of the notch gears  12  is disposed radially outward (with respect to the axis of the stent being assembled) relative to the filament  20  associated with a carrier  14  on the inner radius  30  of the circle  26  of notch gears  12 . The carriers  14  depicted toward the outer radius  28  of the circle  26  of notch gears  12  move in a generally counterclockwise direction, and the carriers  14  disposed toward the inner radius  30  of the circle  26  of notch gears  12  move in a generally clockwise direction. 
     The space contained within the cone formed by the filaments  16 , 18  extending between the carriers  14  and the mandrel  22  and including the space occupied by the mandrel  22  is referred to herein as the “braiding zone”  32 , as depicted in  FIG.  1   . Although the angles α 1  and α 2  of the filament  16 ,  20  to the mandrel  22  may be varied as desired, α 1  and α 2  preferably each comprise an angle of approximately 55° when the braiding angle of a braided stent β is approximately 110°. These angles may vary dependent upon, inter alia, the exact radial position of the carriers  14  relative to the mandrel  22 . Further, these angles are nonlimiting and any suitable braiding angle β, including acute or obtuse braiding angle β. For example, the braiding angle β may vary from about 10° to about 170°, desirably from about 30° to about 150°, preferably from about 100° to about 120°. As used herein, the phrase “substantially along the longitudinal axis” as used with respect to the alignment of the moving mandrel means that the mandrel does not have to be perfectly centered in the braiding zone, but merely needs to be aligned close enough to the longitudinal axis L such that the angles of the filaments between the mandrel and the carriers allows the braiding operation to create a functional braid without tangling the filaments. 
       FIG.  4 A  depicts a stent  24  according to the present invention. The stent  24  may include a first atraumatic end  34  and an opposed second atraumatic end  38 . The first atraumatic end may be formed by bending the filaments  20  at or about the middle portion of the length of the filaments  20  to form bends  36  thereat. The second opposed atraumatic end  38  may be formed by bending the filaments  20  into closed loops  39 . The filaments  20  forming the closed loops  39  may be secured to one and the other by welds  41 . The stent  24  of the present invention is not limited to the use of welds  41  to join stent filaments  20 , and other mechanical means, such as the use of hypotubes, twisting or tying of the filaments and the like, may suitably be used. The stent  24  of the present invention may also include one or more outwardly flared or flanged portions  40 . In such a case, the diameter of the flared portion  40  is greater than the diameter of the longitudinal expanse portion  42  of the stent  24 . The longitudinal expanse portion  42  of the stent  24  may be a constant diameter, including a substantially constant diameter. Such stent configurations are non-limiting, and other stent configurations may be achieved with the systems, devices and methods of the present invention. For example, the stent  24  may include outwardly flared portions at both ends  34 ,  38 , may have a tapered configuration in place of or in conjunction with the longitudinal expanse portion  42  of the stent  24 . 
     Further, the braiding angle β throughout the stent  24 , including the flanged portion  40  and the longitudinal expanse portion  42 , is substantially constant. For example, as depicted in  FIG.  4 A , the braiding angle β is about 110°±3°, desirably about 110°±1°. Stents of the prior art typically have a variation of ±10° or greater in stent transitional regions, such as the flared or flanged portions of their stents. Such variations, however, present undesirable variability in stent performance, such as radial expansion force, radial compression force or deployment force. The present invention avoids such undesirable variations through the use of, inter alia, the tensioned or constant force braiding carriers  14  (described in further detail below in conjunction with the description of  FIG.  22   ), the constant force bobbin carriers  110  (described in further detail below in conjunction with the description of  FIG.  24   ), the braiding mandrel  22  having raised projections  52 ,  56 , (optionally)  70  (described in further detail below in conjunction with the description of  FIGS.  5 - 16 B ), and/or stent-filament-holding securement projections  48  on the mandrel  22  (described in further detail below in conjunction with the description of  FIGS.  6 ,  14  and  15   ). 
     The one-under and one-over braiding configuration of the stent  24  of  FIG.  4 A  is depicted in an exploded view in  FIG.  4 B . As depicted in  FIG.  4 B , the filaments  20  alternate in a braiding pattern having a 1/1 intersection, i.e., one-under and one-over pattern. The stent  24 , however, is not so limited. As depicted in  FIG.  4 C , stent  24  may include the filaments  20  braided in a two-under and a two-over pattern. Other braiding patterns known in the art may also be suitably be used. Further, as illustrated in  FIG.  4 D , stent  24  may be braided by using a pair of filaments  20 ′ in a one-under and one-over pattern. The filaments  20 ′ may be the same or may be different, i.e., may have the same or different dimensions, shapes and/or materials of construction. Moreover, the filaments  20 ′ may suitably be braided in other braided patterns, such as but not limited to, for example, the two-under and two-over pattern. Desirably, the braided filaments  20 ,  20 ′ non-interlockingly engage one and the other in the braided pattern. Such non-interlocking braiding pattern excludes, if desired, inter-twisting, inter-looping, inter-engaging and the like at the intersection of the braided filaments  20 ,  20 ′. If desired, the braided or woven filaments  20 ,  20 ′ may be braided or woven in an interlocking manner. 
     Desirably, the filaments  20  are made from any suitable implantable material, including without limitation nitinol, stainless steel, cobalt-based alloy such as Elgiloy®, platinum, gold, titanium, tantalum, niobium, polymeric materials and combinations thereof. Useful polymeric materials may include, for example, polyesters, including polyethylene terephthalate (PET) polyesters, polypropylenes, polyethylenes, polyurethanes, polyolefins, polyvinyls, polymethylacetates, polyamides, naphthalane dicarboxylene derivatives, natural silk, polyvinyl chloride, polytetrafluoroethylene, including expanded polytetrafluoroethylene (ePTFE), fluorinated ethylene propylene copolymer, polyvinyl acetate, polystyrene, poly(ethylene terephthalate), naphthalene dicarboxylate derivatives, such as polyethylene naphthalate, polybutylene naphthalate, polytrimethylene naphthalate and trimethylenediol naphthalate, polyurethane, polyurea, silicone rubbers, polyamides, polycarbonates, polyaldehydes, natural rubbers, polyester copolymers, styrene-butadiene copolymers, polyethers, such as fully or partially halogenated polyethers, and copolymers and combinations thereof. Further, useful and nonlimiting examples of polymeric stent materials include poly(L-lactide) (PLLA), poly(D,L-lactide) (PLA), poly(glycolide) (PGA), poly(L-lactide-co-D,L-lactide) (PLLA/PLA), poly(L-lactide-co-glycolide) (PLLA/PGA), poly(D,L-lactide-co-glycolide) (PLA/PGA), poly(glycolide-co-trimethylene carbonate) (PGA/PTMC), polydioxanone (PDS), Polycaprolactone (PCL), polyhydroxybutyrate (PHBT), poly(phosphazene) poly(D,L-lactide-co-caprolactone) PLA/PCL), poly(glycolide-co-caprolactone) (PGA/PCL), poly(phosphate ester) and the like. Wires made from polymeric materials may also include radiopaque materials, such as metallic-based powders, particulates or pastes which may be incorporated into the polymeric material. For example the radiopaque material may be blended with the polymer composition from which the polymeric wire is formed, and subsequently fashioned into the stent as described herein. Alternatively, the radiopaque material may be applied to the surface of the metal or polymer stent. In either embodiment, various radiopaque materials and their salts and derivatives may be used including, without limitation, bismuth, barium and its salts such as barium sulphate, tantalum, tungsten, gold, platinum and titanium, to name a few. Additional useful radiopaque materials may be found in U.S. Pat. No. 6,626,936, which is herein incorporated in its entirely by reference. Metallic complexes useful as radiopaque materials are also contemplated. The stent may be selectively made radiopaque at desired areas along the wire or made be fully radiopaque, depending on the desired end-product and application. Further, the filaments  20  have an inner core of tantalum, gold, platinum, iridium or combination of thereof and an outer member or layer of nitinol to provide a composite wire for improved radiopacity or visibility. Desirably, the inner core is platinum and the outer layer is nitinol. More desirably, the inner core of platinum represents about at least 10% of the wire based on the overall cross-sectional percentage. Moreover, nitinol that has not been treated for shape memory such as by heating, shaping and cooling the nitinol at its martensitic and austenitic phases, is also useful as the outer layer. Further details of such composite wires may be found in U.S. Patent Application Publication 2002/0035396 A1, the contents of which is incorporated herein by reference. Preferably, the filaments  20  are made from nitinol, or a composite wire having a central core of platinum and an outer layer of nitinol. 
       FIG.  5    is a side elevational view of a braiding mandrel  22  according to the present invention. The braiding mandrel  22  is a tubular, typically metal such as stainless steel, cylindrical member having a distal end  44  (distal from the circle  26  of notch gears  12  when disposed on the braiding machine  10 ) and an opposed proximal end  46  (proximal to the circle  26  of notch gears  12  when disposed on the braiding machine  10 ). The distal end  44  includes securement projections  48 , which, as described below, are useful for engaging the stent filaments  20  prior to the commencement of braiding. The distal end  44  further includes a distal portion  50  which has a larger diameter than the longitudinal portion  54  of the mandrel  22 . After braiding the filaments  20 , the distal mandrel portion  50  forms the flared stent portion  40 , and the longitudinal mandrel portion  54  forms the longitudinal expanse stent portion  42 . Both the distal mandrel portion  50  and the longitudinal mandrel portion  54  may include raised mandrel projections  52  and  56 , respectively. As described below, the raised mandrel projections  52 ,  56  are useful for forming guides for receiving the filaments  20  during braiding. The larger diameter portion may include a flared portion, a stepped portion and the like. Further, the larger diameter portion may be disposed anywhere along the length of the mandrel  22 . Moreover, the mandrel  22  may have multiple larger diameter portions, which may be the same or different. 
     The present invention, however, is not limited to the use of a dual sized or flared mandrel  22 . For example, as depicted in  FIG.  6   , braiding mandrel  22 ′ may be a substantially constant diameter mandrel, which is useful for braiding substantially constant diameter stents  24 . The depicted shapes of the mandrels  22 ,  22 ′ are non-limiting and other shaped mandrels may suitably be used, such as dual flared or flanged mandrel, tapered mandrels, and the like. Moreover, the raised mandrel projections  52 ,  56  need not be present along the whole braiding length and/or circumference of the braiding mandrel  22 . Selected portion of the braiding mandrel  22  may be free or partially free of the raised mandrel projections  52 ,  56  depending on the characteristics of the stent  24  to be produced. 
       FIG.  7    is an exploded view of a portion of the mandrel  22  further depicting the raised mandrel projections  52 ,  56 . The raised mandrel projections  52 ,  56  are arranged in a regular pattern over the mandrel  22  so that adjacent or juxtaposed raised mandrel projections  52 ,  56  form guides or channels  58  for receiving the stent filaments  20  during braiding.  FIGS.  8 - 10    further detail the raised mandrel projections  52 ,  56  of the present invention. As depicted in  FIG.  8    the raised mandrel projections  52 ,  56  are in the shape of a square or rectangular pyramid, having a square or rectangular base  60  and four triangular sides  62 . As depicted in  FIG.  9   , the raised mandrel projections  52 ,  56  may have a truncated top portion  64 . The top portion  64  may be somewhat rounded (not shown), if desired. Truncated and/or rounded top portions  64  are useful for easy removal of the stent  24  from the mandrel  22 . For example, to remove the stent  24  from the mandrel  22  the stent  24  may be longitudinally compressed which causes the diameter of the stent  24  to increase. The stent filaments  20  may then clear over the truncated and/or rounded top portions  64 , thereby releasing the stent  24  from the mandrel  22 . Depending upon, for example, the braiding angle of the stent filaments  20  and/or the height of the raised mandrel projections  52 ,  56 , the raised mandrel projections  52 ,  56  may be truncated to so form the truncated and/or rounded top portions  64  of the mandrel  22 . Truncated and/or rounded top portions  64  may also be useful for guiding the stent filaments  20  into the guides or channels  58  of the mandrel  22 . Further, as depicted in  FIG.  10   , the raised mandrel projections  52 ,  56  may further include a square or rectangular base portion  66  to further define the guides or channels  58  of the mandrel  22 . Such features of the raised mandrel projections  52 ,  56  are useful for forming mandrel guides or channels  58  so that accurate placement of the stent filaments  20  is achieved during braiding, including accurate placement of the stent filaments  20  over dimensional variations of the mandrel  22 , such as flared or tapered portions. The present invention, however, is not limited to the use square or rectangular pyramid shaped raised mandrel projections  52 ,  56 , and other suitably shaped projection may suitably be used. For example, pins or projections, including removable pins or projections may suitably be used. The raised mandrel projections  52 ,  56  may be formed by cutting or etching away portion of the mandrel, such as by laser cutting, machine cutting, chemical etching, and the like. Further, the guides or channels  58  may be formed as grooves in the mandrel. Moreover, the raised mandrel projections  52 ,  56  forming the channels  58  may be on a collar or sleeve which may be releasably secured to the braiding mandrel itself. 
       FIG.  11    is an exploded view of a portion of the distal end  44  of the braiding mandrel  22 . The securement projections  48  are depicted as being raised tabs  48 ′. The raised tabs  48 ′ have a rounded face  49  for ease of securement of the stent filaments  20  and for safety by generally eliminating shape and pointed faces on the mandrel  22 . As depicted in  FIG.  12   , the raised tab  48 ′ is useful for bending a stent filament  22  about an under portion  51  of the raised tab  48 ′. The under portion  51  of the raised tab  48 ′ is recessed from the rounded face  49  to secure the stent filament wire  20  thereat. Further, the under portion  51  of the raised tab  48 ′ may be contoured so that the shape of the bend  36  of at the distal end  34  of the stent  24  corresponds to the shape of the under portion  51  of the raised tab  48 ′. The present invention, however, is not limited to such described under portion  51  of the raised tab  48 ′ as securement projections  48 , and as described below other configurations for the securement projections  48  may suitably be used. Moreover, the present invention is not limited to the securement of one stent filament  20  around one raised tab  48 ′. For example, if desired, two or more stent filaments  20 , which may be the same or different including different material and/or specifications, may be secured about one raised tab  48 ′ and then braided according to the techniques of the present invention. 
       FIG.  13    depicts the braiding mandrel  22  having middle portions of the stent filaments  20  secured to the raised projections  48 ′. Further, the stent filaments  20  are disposed within the channels  58  of the mandrel  22  formed between juxtaposed raised projections  52 ,  56 .  FIG.  14    depicts the stent filaments  22  being braided over the mandrel  20 . Further, one end, for example the proximal end  46 , of braiding mandrel  22  may be releasably secured to the mandrel  22 ′ of the braiding machine  10  by a sleeve  47 . Other arrangements may be suitably be used to secure the braiding mandrel  22  to the mandrel  22 ′ of the braiding machine  10 . 
       FIG.  15    is an exploded view of the proximal end  46  of the braiding mandrel  22 . The proximal end of the braiding mandrel  22  may include projections  45  which are useful for forming the closed loops  39  of stent  24 . Such closed loops may be formed by bending the filaments  20  around the projections  45  (not shown). Details for forming such closed loops  39  may be found in U.S. Patent Application Publication Nos. 2005/0049682 A1 to Leanna et al.; 2005/0256563 A1 to Clerc et al.; and 2006/0116752 A1 to Norton et al., the contents of which are incorporated herein by reference. 
     The braiding mandrels  22  of  FIGS.  5 - 15    are depicted as being useful for manufacturing a single stent. The braiding mandrels  22  of the present invention, however, are not so limited. For example, several stents  24  may be produced on a single mandrel  22  by providing different mandrel regions each having the securement projections  48  for commencing the braiding of a stent portion; channels  58  for receiving and controlling the stent filaments  20  within the particular section; and projections  45  for finishing the atraumatic stents  24  of the present invention. The several or multiple stents  24 , i.e., two or more, may be the same or may have different stent configurations including stent diameters and stent lengths. In other words, the techniques and devices of the present invention allow for the manufacture of a highly customizable stent or highly customizable stents. Such customizable aspects of the stent may include but are not limited to the customization of stent lengths, stent diameters, stent curvatures, stent geometries, including atraumatic stent end geometries, and the like. 
       FIGS.  16 A and  16 B  are partial exploded views of a portion of the braiding mandrel  22  of the present invention. As depicted in  FIG.  16 A , the distal mandrel portion  50  has a larger diameter than a diameter of the longitudinal mandrel portion  54 . The transition  53  between the distal mandrel portion  50  and the longitudinal mandrel portion  54  is a simple step down in mandrel  22  diameters. As depicted in  FIG.  16 B , a transition region  68  is disposed between the larger distal portion  50  and the smaller the longitudinal mandrel portion  54 . The transition region  68  is a sloped, desirably conical, region between the two diameters. The transition region  68  may further include raised mandrel projections  70 , similar to the above-described shaped raised projections  52 ,  56 . 
     While aspects of the present invention have been described as using a mandrel  22 ,  22 ′ having raised projections  52 ,  56  to provide, the present invention is not so limited. For example, as depicted in  FIG.  17   , where it is desirable, a braiding mandrel  22 ″ which is free or substantially free of the above described raised projections  52 ,  56  may suitably be used. Such a mandrel  22 ″ may still include the above described securement projections  48  at its distal end  44  and projections  45  (not shown) at its proximal end  46 . 
       FIGS.  18 - 21    illustrate alternate embodiments of the securement projections  48  for securing stent filaments  20  at the distal end  44  of the braiding mandrel  22 . These embodiments may be releasably secured to the distal end  44  of the braiding mandrel  22  or in some cases integrally formed with the distal end  44  of the braiding mandrel  22 , such as but not limited to the above described raised tabs  48 ′.  FIGS.  18 - 19    depict a wagon wheel arrangement  72  for securing stent filaments  20  at the distal end  44  of the braiding mandrel  22 . The wagon wheel  72  may include pins  74  around which the stent filaments  20  may be disposed. The stent filaments  20  may be disposed about the inner portions  76  of the pins  74 , but if desired the stent filaments  20  may be disposed outer pin portion  77 . The wagon wheel  72  may further include an undulating surface  78 . The undulating surface  78  is useful in positioning the stent filaments  20  within the wagon wheel  72 . Further, the shape of the undulating surface  78  may be altered to conform to the desired angle of the bends  36  of the stent  24 . 
       FIG.  20    depicts a mandrel  22 ″ having holes  80  at its distal end. Screws, pins, tabs, detents and the like (not shown) may be inserted into the holes  80  for securing stent filaments  20  (not shown) thereat. As depicted in  FIG.  21   , a cap  82  may be used in conjunction with the embodiment of  FIG.  20   . The cap  82  may have a plurality of semicircular notches  84  which receive the pins or screws described in conjunction with  FIG.  20   . The cap  82  may further include projections  86  with angular or sloped surfaces  85  which are useful for setting and orientation, configuration and/or angle of the bends  36  of the stent  24 . While this embodiment of the projections for securing the stent filaments  20  is shown as being integrally formed into the mandrel  22 ″, the holes  80  may be integrally formed in any of the other described mandrels  22 ,  22 ′, or may be formed as a separate device which may be releasably secured to any of the braiding mandrels  22 ,  22 ′,  22 ″. 
       FIG.  22    is a schematic depiction of a tensioned or constant force braiding carrier  14  of the present invention. The constant force carrier  14  may include a frame  88  for holding wheels  90 ,  92 ,  94 ,  96  and spring  98 . The retractable carrier filament  16  may have one end securably wound around wheel  92 . The retractable carrier filament  16  may exit the constant force carrier  14  via wheels  94 ,  96 , as shown. The wheels  94 ,  96  are useful in guiding the retractable carrier filament  16  toward the braiding zone  32 . Spring  98  generally imparts a constant force from wheel  90  to wheel  92  to provide, in part, a constant tension to the retractable carrier filament  16 . The retractable carrier filament  16  may itself coil or wrap around wheel  92  to be in communication with the tension applied by the spring  98 . Further, as the stent  24  is being braided, the retractable carrier filament  16  may uncoil or unwrap from the wheel  92  to accommodate the movement of the stent filaments  20  within the braiding zone  32 . The bottom portion  89  of the frame  88  of constant force carrier  14  may be releasably secured to the notch gear  14  as schematically depicted in  FIGS.  1 - 2   . The constant force carrier  14  of  FIG.  22    does not include a bobbin having stent forming filaments  20  wound thereon. In other words the constant force carrier  14  of  FIG.  22    includes the retractable carrier filament  16  to the exclusion of the stent forming filament  20 . 
     The constant force or tensioned braiding carrier  14  is useful for braiding discrete lengths of stent forming filaments  20 . With the use of the constant force or tensioned braiding carriers  14 , all or substantially all of the stent forming filaments  20  are disposed directly within the braiding zone  32 . Thus, constant tension or substantially constant tension on the stent forming filaments  20  is controlled and maintained directly within the braiding zone  32 . Braiding techniques of the prior art do not have such direct control of filament tension within the braiding zone, leading to possible greater variation of braiding angles and stent cell sizes. 
       FIG.  23    is a schematic of one embodiment of the clip  18  described above in conjunction with  FIG.  1   . The clip  18  is depicted as a quick release clip, but any clip or securing mechanism may suitably be used to secure the stent forming filament  20  to the retractable carrier filament  16 . The retractable carrier filament  16  may be securably disposed to releasably secure to the clip  18 . The stent forming filament  20  is desirably releasably secured to the clip  18 . A spring  100  may be used between a knob  102  and a body  104  of the clip  18 . Moving the knob  102  toward the clip body  104 , which is against the force of the spring  100 , releases the stent forming element  20  from the clip  18  by moving filament engaging portions (not shown) within the body  104  of the clip  18 . 
       FIG.  24    schematically depicts an alternate embodiment of a constant force bobbin carrier  110  which may be used in accordance with the present invention. The constant force bobbin carrier  110  includes a bobbin  114  upon which the stent forming filament  20  is wound. The constant force bobbin carrier  110  includes a latch spring  116  which provides constant tension to the stent forming filament  20 . The latch spring  116  typically includes an eyelet (not shown) or a small wheel to guide the stent forming filament  20 . The latch spring  116  is typically moveable away from the bobbin  114 , as indicated by the vector, to provide tension to the stent forming filament  20 . The stent forming filament  20  then travels about a first wheel  118  and a second wheel  120 . The stent forming wire  20  exits the constant force bobbin carrier  110  toward the braiding zone  32  for braiding the stent  24  in accordance with the present invention. Typically, the stent forming filament  20  is partially unwound from one bobbin  114  and then the unwound portion is rewound onto another bobbin  114  of another the constant force bobbin carrier  110  (not shown). After the constant force bobbin carriers  110  are secured to the notch gears  12 , the middle portion of the stent forming filament  20  may be then engaged to the securement projections  48  of the braiding mandrel  22  to braid the stent in accordance with the present invention. This alternative embodiment may be, however, more time consuming as the stent filaments must be rewound onto bobbins  114 . 
     Use of the constant force bobbin carriers  110  in conjunction with the braiding mandrels  22 ,  22 ′ having distal securement projections  48  and braiding channels  58  provide for suitable tension control to braid the stents of the present invention. The constant force braiding carriers  110 , however, may require greater lengths of filaments  20  as compared to the use of the tensioned braiding carriers  14 . As such, greater portions of the filaments  20  may be outside the braiding zone  32  with the use of the bobbin carriers  110 , which may lead to less direct control of the tension on the filaments  20  within the braiding zone  32 . 
     In yet an alternate embodiment, a combination of constant force carriers  14  and constant force bobbin carriers  110  may be used where instead of rewinding the stent filament  20  onto another bobbin  114  the stent filament end exiting the bobbin  114  may be releasably secured to a constant force carrier  14  via the clip  18 . 
     Desirably, the constant force carriers  14  and the constant force bobbin carrier  110 , in conjunction with the other embodiments of the present invention, are configured and controlled to provide a controlled tension to the filaments  16 ,  20  during braiding of the stent  24  over mandrel  22 . Useful tension forces include substantially constant tensile forces from about ⅛ or 0.125 pound-force (about 0.5 Newtons) to about 10 pound-force (about 45 Newtons). Desirably, the tensile force is from about ¼ or 0.25 pound-force (about 1 Newton) to about 10 pound-force (about 22 Newtons). Preferably, the tensile force is from about ½ or 0.5 pound-force (about 2 Newtons) to about 3 pound-force (about 13 Newtons). In general, the larger the diameter of the filament  20  the larger tensile force will be applied. Minimum force levels are necessary to securely hold the filaments  20  on the mandrel  22  during braiding and subsequent processing steps. If too much force is applied, then the filaments  20  may stretch or deform on the mandrel  22 , in particular if the stent is heat treated while on the mandrel  22 , which is referred to as necking of filaments or wires. Such necking is undesirable as it may weaken the filament or wire and possibly leading toward fracture of the filament or wire. These above-described tensile forces are desirably useful for braiding metallic filaments  20 . When non-metallic, for example polymeric, filaments  20  are braided to form the stent  24 , the tension force applied may be less than the values for metallic filaments  20 . For example, a tensile force from about 0.5 pound-force (about 2 Newton) to about 1 pound-force (about 2 Newtons) is useful for braiding polymeric filaments  20 . 
       FIG.  25    depicts a method for braiding the stent  24  of the present invention. At step  200 , a number of elongate stent filaments are provided. Each of the filaments has opposed ends and an intermediate portion between the opposed ends. At step  210 , a number of tensioned braiding carriers is provided. At step  220 , a braiding mandrel having opposed proximal and distal ends is provided. The braiding mandrel may include a number of circumferentially spaced-apart securement projections at the distal end of the braiding mandrel and may optionally include a plurality of grooves or channels for receiving the stent filaments during braiding. At step  230 , the intermediate portion of one of the filaments is securably disposed to one of the securement projections. At step  240 , one of the opposed ends of the one filament is secured to one of the tensioned braiding carriers without spooling the one filament to the one tensioned braiding carrier. At step  250 , the other opposed end of the one filament is secured to a different second tensioned carrier without spooling the one filament to the second tensioned carrier. At step  260 , steps  230 - 250  are repeated until all of the intermediate portions of the filaments are securably disposed to different ones of the securement projections and until each end of the number of filaments are secured to a different one of the tensioned carriers. At step  270 , the tensioned carriers are moved in a generally circular and serpentine motion. At step  280 , the mandrel is longitudinally advanced relative to a direction substantially perpendicular to the motion of the tensioned carriers to braid the filaments to form a braided stent. 
     The method of this embodiment may further include the step of applying a constant tension from the tensioned braiding carriers to the filaments, wherein the constant tension force is form about 0.25 pound-force (1.1 Newtons) to about 5 pound-force (22.2 Newtons). Further, the number of securement projections may be about one-half the number of filaments, but any suitable number of securement projections may be used. The number of tensioned carriers may be about twice the number of filaments, but any suitable number of tensioned carriers may be used. Desirably, the number of filaments may be from about 6 to about 40 or more. Such numbers of securement projections and tensioned carriers are non-limited, and any suitable relative numbers of securement projections and tensioned carriers may be used. For example, the number and type of filaments  20  may be increased and/or decreased during braiding stent, including braiding different sections of stents with different types of material and/or different number of filaments. 
     The mandrel may include a plurality of grooves or channels and further where the filaments are disposed into the grooves during the braiding of steps  270  through  280 . The filaments may be tangentially disposed within the grooves during the braiding steps  270  through  280 . Desirably, the steps  270  through  280  are continued until the filaments are braided to a portion of the mandrel near the proximal end of the mandrel. The braiding method may further include the step of securing the filaments to the portion of the mandrel while maintaining the filaments under a tension force from about 0.25 pound-force (1.1 Newtons) to about 5 pound-force (22.2 Newtons). Further, the stent may be heat treated. Desirably, the heat treating of the stent filaments may be performed while the filaments are disposed on the mandrel and also while the filaments are under the tension force. 
     The securement projections at the distal end of the braiding mandrel may be selected from hooks, pins, tabs, screws and combinations thereof. The securement projections may be removable from the mandrel. The distal end of the braiding material may further include a collar having the securement projections disposed thereto. 
     Further, the mandrel may include a first portion having a first diameter, and a second portion having a second diameter, where the first diameter is different from the second diameter. The mandrel may include a plurality of portions having different diameters. Moreover, the mandrel may include interchangeable portions which may be connectable along the length of the mandrel or even along the circumference of the mandrel, or combinations thereof. Grooves may be disposed throughout the first and second portions. Further, a constant tension force may be applied from the constant force braiding carriers to the filaments so that a braiding angle between intersecting braided filaments is substantially equal in the first and second portions. The mandrel may further include a transition portion between the first and second portions. Desirably, the braiding angle is substantially equal in the first portion, the transition portion and the second portion. The present invention, however, is not so limited, and the braiding angles may be controlled to any custom values, including controlled variation of the braiding angle over straight stent section and non-straight stent sections, such as flared sections, flanged sections, curved sections and the like. 
     The filaments may be selected from metallic filaments, polymeric filaments, and combinations thereof. The filaments may be single strand or multi-strand filaments. The strands of the multi-strand filaments may be the same or different, such as but not limited to different materials, different geometries, different mechanical properties, different physical properties, different chemical properties, and the like. Desirably, the filaments are metallic filaments, including nitinol filaments or nitinol-containing filaments. 
       FIG.  26    depicts another embodiment of a method for braiding the stent  24  of the present invention. At step  300 , a number of elongate filaments are provided with each of the filaments having opposed ends and an intermediate portion between the opposed ends. At step  310 , a number of braiding carriers are provided. At step  320 , a braiding mandrel having opposed proximal and distal ends is provided. The braiding mandrel may include a number of circumferentially spaced-apart securement projections at the distal end and may optionally further include a plurality of grooves. At step  330 , the intermediate portion of one of the filaments is securably disposed to one of the securement projections at the distal end of the mandrel. At step  340 , one of the opposed ends of the one filament is secured to one of the braiding carriers. At step  350 , the other opposed end of the one filament is secured to a different second braiding carrier. At step  360 , steps  330  through  350  are repeated until all of the intermediate portions of the filaments are securably disposed to different ones of the securement projections and until each end of the number of filaments are secured to a different one of the braiding carriers. At step  370 , the braiding carriers are moved in a generally circular and serpentine motion. At step  380 , the mandrel is longitudinally advanced relative to the braiding machine in a direction substantially perpendicular to the motion of the braiding carriers to braid the filaments to form a braided stent; and optionally a constant tension force, for example from about 0.25 pound-force (1.1 Newtons) to about 5 pound-force (22.2 Newtons), is applied from the braiding barriers to the filaments during the braiding of the filaments. 
     The braiding carriers of this embodiment may be constant force carriers. The ends of the filaments may be securably disposed to the constant force carriers without spooling the filaments to the constant force carriers. Alternatively or in addition to, some or all of the braiding carriers may include a bobbin where a portion of the filament is spooled about the bobbin. 
     While the invention has been described through the use of a braiding machine, certain aspects of the present invention may also be useful with hand braiding or hand weaving method to form a stent. In such a case the braiding mandrel may further include additional tabs, pins or the like along its longitudinal length about which a tension of the braiding filaments may be obtained. 
     The stent  24  of the present invention may include a therapeutic agent in a coating. The therapeutic agent in a coating of the stent  24  of the present invention may be any suitable biologically acceptable agent such as a non-genetic therapeutic agent, a biomolecule, a small molecule, or cells. 
     Exemplary non-genetic therapeutic agents include anti-thrombogenic agents such as heparin, heparin derivatives, prostaglandin (including micellar prostaglandin E1), urokinase, and PPack (dextrophenylalanine proline arginine chloromethyl ketone); anti-proliferative agents such as enoxaparin, angiopeptin, sirolimus (rapamycin), tacrolimus, everolimus, zotarolimus, biolimus, monoclonal antibodies capable of blocking smooth muscle cell proliferation, hirudin, and acetylsalicylic acid; anti-inflammatory agents such as dexamethasone, rosiglitazone, prednisolone, corticosterone, budesonide, estrogen, estradiol, sulfasalazine, acetylsalicylic acid, mycophenolic acid, and mesalamine; anti-neoplastic/anti-proliferative/anti-mitotic agents such as paclitaxel, epothilone, cladribine, 5-fluorouracil, methotrexate, doxorubicin, daunorubicin, cyclosporine, cisplatin, vinblastine, vincristine, epothilones, endostatin, trapidil, halofuginone, and angiostatin; anti-cancer agents such as antisense inhibitors of c-myc-oncogene; anti-microbial agents such as triclosan, cephalosporins, aminoglycosides, nitrofurantoin, silver ions, compounds, or salts; biofilm synthesis inhibitors such as non-steroidal anti-inflammatory agents and chelating agents such as ethylenediaminetetraacetic acid, O,O′-bis(2-aminoethyl)ethyleneglycol-N,N,N′,N′-tetraacetic acid and mixtures thereof; antibiotics such as gentamicin, rifampin, minocycline, and ciprofloxacin; antibodies including chimeric antibodies and antibody fragments; anesthetic agents such as lidocaine, bupivacaine, and ropivacaine; nitric oxide; nitric oxide (NO) donors such as linsidomine, molsidomine, L-arginine, NO-carbohydrate adducts, polymeric or oligomeric NO adducts; anti-coagulants such as D-Phe-Pro-Arg chloromethyl ketone, an RGD peptide-containing compound, heparin, antithrombin compounds including anti-thrombin antibodies, platelet receptor antagonists, anti-platelet receptor antibodies, enoxaparin, hirudin, warfarin sodium, dicumarol, aspirin, prostaglandin inhibitors, platelet aggregation inhibitors such as cilostazol and tick antiplatelet factors; vascular cell growth promoters such as growth factors, transcriptional activators, and translational promoters; vascular cell growth inhibitors such as growth factor inhibitors, growth factor receptor antagonists, transcriptional repressors, translational repressors, replication inhibitors, inhibitory antibodies, antibodies directed against growth factors, bifunctional molecules consisting of a growth factor and a cytotoxin, bifunctional molecules consisting of an antibody and a cytotoxin; cholesterol-lowering agents; vasodilating agents; agents which interfere with endogenous vasoactive mechanisms; inhibitors of heat shock proteins such as geldanamycin; angiotensin converting enzyme (ACE) inhibitors; beta-blockers; βAR kinase (βARK) inhibitors; phospholamban inhibitors; protein-bound particle drugs such as ABRAXANE™; and any combinations and prodrugs of the above. 
     Exemplary biomolecules include peptides, polypeptides and proteins; oligonucleotides; nucleic acids such as double or single stranded DNA (including naked and cDNA), RNA, antisense nucleic acids such as antisense DNA and RNA, small interfering RNA (siRNA), and ribozymes; genes; carbohydrates; angiogenic factors including growth factors; cell cycle inhibitors; and anti-restenosis agents. Nucleic acids may be incorporated into delivery systems such as, for example, vectors (including viral vectors), plasmids or liposomes. 
     Non-limiting examples of proteins include SERCA 2 protein, monocyte chemoattractant proteins (“MCP-1”) and bone morphogenic proteins (“BMPs”), such as, for example, BMP-2, BMP-3, BMP-4, BMP-5, BMP-6 (VGR-1), BMP-7 (OP-1), BMP-8, BMP-9, BMP-10, BMP-11, BMP-12, BMP-13, BMP-14, BMP-15. Preferred BMPs are any of BMP-2, BMP-3, BMP-4, BMP-5, BMP-6, and BMP-7. These BMPs can be provided as homodimers, heterodimers, or combinations thereof, alone or together with other molecules. Alternatively, or in addition, molecules capable of inducing an upstream or downstream effect of a BMP can be provided. Such molecules include any of the “hedgehog” proteins, or the DNAs encoding them. Non-limiting examples of genes include survival genes that protect against cell death, such as anti-apoptotic Bcl-2 family factors and Akt kinase; serca 2 gene; and combinations thereof. Non-limiting examples of angiogenic factors include acidic and basic fibroblast growth factors, vascular endothelial growth factor, epidermal growth factor, transforming growth factors α and β, platelet-derived endothelial growth factor, platelet-derived growth factor, tumor necrosis factor α, hepatocyte growth factor, and insulin-like growth factor. A non-limiting example of a cell cycle inhibitor is a cathepsin D (CD) inhibitor. Non-limiting examples of anti-restenosis agents include p15, p16, p18, p19, p21, p27, p53, p57, Rb, nFkB and E2F decoys, thymidine kinase and combinations thereof and other agents useful for interfering with cell proliferation. 
     Exemplary small molecules include hormones, nucleotides, amino acids, sugars, and lipids and compounds that have a molecular weight of less than 100 kD. 
     Exemplary cells include stem cells, progenitor cells, endothelial cells, adult cardiomyocytes, and smooth muscle cells. Cells can be of human origin (autologous or allogeneic) or from an animal source (xenogeneic), or genetically engineered. Non-limiting examples of cells include side population (SP) cells, lineage negative (Lin) cells including Lin −  CD34 − , Lin − CD34 + , Lin − c Kit + , mesenchymal stem cells including mesenchymal stem cells with 5-aza, cord blood cells, cardiac or other tissue derived stem cells, whole bone marrow, bone marrow mononuclear cells, endothelial progenitor cells, skeletal myoblasts or satellite cells, muscle derived cells, Go cells, endothelial cells, adult cardiomyocytes, fibroblasts, smooth muscle cells, adult cardiac fibroblasts+5-aza, genetically modified cells, tissue engineered grafts, MyoD scar fibroblasts, pacing cells, embryonic stem cell clones, embryonic stem cells, fetal or neonatal cells, immunologically masked cells, and teratoma derived cells. 
     Any of the therapeutic agents may be combined to the extent such combination is biologically compatible. 
     Any of the above mentioned therapeutic agents may be incorporated into a polymeric coating on the stent  24  or applied onto a polymeric coating on the stent  24 . The polymers of the polymeric coatings may be biodegradable or non-biodegradable. Non-limiting examples of suitable non-biodegradable polymers include polystyrene; polystyrene maleic anhydride; polyisobutylene copolymers such as styrene-isobutylene-styrene block copolymers (SIBS) and styrene-ethylene/butylene-styrene (SEBS) block copolymers; polyvinylpyrrolidone including cross-linked polyvinylpyrrolidone; polyvinyl alcohols, copolymers of vinyl monomers such as EVA; polyvinyl ethers; polyvinyl aromatics; polyethylene oxides; polyesters including polyethylene terephthalate; polyamides; polyacrylamides including poly(methylmethacrylate-butylacetate-methylmethacrylate) block copolymers; polyethers including polyether sulfone; polyalkylenes including polypropylene, polyethylene and high molecular weight polyethylene; polyurethanes; polycarbonates, silicones; siloxane polymers; cellulosic polymers such as cellulose acetate; polymer dispersions such as polyurethane dispersions (BAYHYDROL®); squalene emulsions; and mixtures and copolymers of any of the foregoing. 
     Non-limiting examples of suitable biodegradable polymers include polycarboxylic acid, polyanhydrides including maleic anhydride polymers; polyorthoesters; poly-amino acids; polyethylene oxide; polyphosphazenes; polylactic acid, polyglycolic acid and copolymers and mixtures thereof such as poly(L-lactic acid) (PLLA), poly(D,L-lactide), poly(lactic acid-co-glycolic acid), 50/50 (DL-lactide-co-glycolide); polydioxanone; polypropylene fumarate; polydepsipeptides; polycaprolactone and co-polymers and mixtures thereof such as poly(D,L-lactide-co-caprolactone) and polycaprolactone co-butyl acrylate; polyhydroxybutyrate valerate and blends; polycarbonates such as tyrosine-derived polycarbonates and acrylates, polyiminocarbonates, and polydimethyltrimethylcarbonates; cyanoacrylate; calcium phosphates; polyglycosaminoglycans; macromolecules such as polysaccharides (including hyaluronic acid; cellulose, and hydroxypropyl methyl cellulose; gelatin; starches; dextrans; alginates and derivatives thereof), proteins and polypeptides; and mixtures and copolymers of any of the foregoing. The biodegradable polymer may also be a surface erodible polymer such as polyhydroxybutyrate and its copolymers, polycaprolactone, polyanhydrides (both crystalline and amorphous), maleic anhydride copolymers, and zinc calcium phosphate. 
     Such coatings used with the present invention may be formed by any method known to one in the art. For example, an initial polymer/solvent mixture can be formed and then the therapeutic agent added to the polymer/solvent mixture. Alternatively, the polymer, solvent, and therapeutic agent can be added simultaneously to form the mixture. The polymer/solvent/therapeutic agent mixture may be a dispersion, suspension or a solution. The therapeutic agent may also be mixed with the polymer in the absence of a solvent. The therapeutic agent may be dissolved in the polymer/solvent mixture or in the polymer to be in a true solution with the mixture or polymer, dispersed into fine or micronized particles in the mixture or polymer, suspended in the mixture or polymer based on its solubility profile, or combined with micelle-forming compounds such as surfactants or adsorbed onto small carrier particles to create a suspension in the mixture or polymer. The coating may comprise multiple polymers and/or multiple therapeutic agents. 
     The coating can be applied to the medical device by any known method in the art including dipping, spraying, rolling, brushing, electrostatic plating or spinning, vapor deposition, air spraying including atomized spray coating, and spray coating using an ultrasonic nozzle. 
     The coating is typically from about 1 to about 50 microns thick. It is also within the scope of the present invention to apply multiple layers of polymer coatings onto the medical device. Such multiple layers may contain the same or different therapeutic agents and/or the same or different polymers. Methods of choosing the type, thickness and other properties of the polymer and/or therapeutic agent to create different release kinetics are well known to one in the art. 
     The stent  24  may also contain a radio-opacifying agent within its structure to facilitate viewing the medical device during insertion and at any point while the device is implanted. Non-limiting examples of radio-opacifying agents are bismuth subcarbonate, bismuth oxychloride, bismuth trioxide, barium sulfate, tungsten, and mixtures thereof. 
     The stent  24  are implanted or otherwise used in body structures, cavities, or lumens such as the vasculature, gastrointestinal tract, abdomen, peritoneum, airways, esophagus, trachea, colon, rectum, biliary tract, urinary tract, prostate, brain, spine, lung, liver, heart, skeletal muscle, kidney, bladder, intestines, stomach, pancreas, ovary, uterus, cartilage, eye, bone, joints, and the like. Further, the stent  24  may contain any of the above described polymer coatings with or without any of the above described therapeutic agents. Moreover, only portions, such as but not limited to portions of the stent  24  disposed between stent ends  34 ,  38  or even just portions of one or both stent ends  24 ,  38 , may contain any of the above described polymer coatings with or without any of the above described therapeutic agents. 
     The embodiments or aspects of the invention, including the embodiments presented in the claims, may be combined in any fashion and combination and be within the scope of the present invention. As a nonlimiting example, the following embodiments or aspects of the invention may be combined in any fashion and combination and be within the scope of the present invention, as follows:
     Embodiment 1. A method of braiding a stent comprising: (a) providing a number of elongate filaments, each of the filaments having opposed ends and an intermediate portion between the opposed ends; (b) providing a number of tensioned braiding carriers; (c) providing a braiding mandrel having opposed proximal and distal ends, the braiding mandrel comprising a number of circumferentially spaced-apart securement projections at the distal end of the braiding mandrel; (d) securably disposing the intermediate portion of one of the filaments to one of the securement projections; (e) securing one of the opposed ends of the one filament to one of the tensioned braiding carriers; (f) securing the other opposed end of the one filament to a different second tensioned braiding carrier; (g) repeating steps (d) through (f) until all of the intermediate portions of the filaments are securably disposed to different ones of the securement projections and until each end of the number of filaments are secured to a different one of the tensioned braiding carriers; (h) moving the tensioned braiding carriers around the mandrel; and (i) longitudinally advancing the mandrel in a direction substantially perpendicular to the motion of the tensioned braiding carriers to braid the filaments to form a braided stent.   Embodiment 2. The method of embodiment 1, wherein step (h) includes moving the tensioned braiding carriers in a generally circular and serpentine motion about a circumferential plane of the mandrel.   Embodiment 3. The method of embodiment 1, wherein the tensioned braiding carriers each comprise a retractable carrier filament and further wherein step (e) includes securing the one opposed end of the one filament to the retractable carrier filament of the one tensioned braiding carrier and step (f) includes securing the other opposed end of the one filament to the retractable carrier filament of the second tensioned braiding carrier.   Embodiment 4. The method of embodiment 2, wherein the tensioned braiding carriers each comprise a wheel and wherein the retractable carrier filament of the tensioned braiding carrier is coiled about the wheel.   Embodiment 5. The method of embodiment 1, further comprising: applying a constant tension from the tensioned braiding carriers to the filaments, wherein the constant tension force is form about 0.25 pound-force to about 5 pound-force.   Embodiment 6. The method of embodiment 1, wherein the number of securement projections is about one-half the number of filaments.   Embodiment 7. The method of embodiment 1, wherein the number of tensioned braiding carriers is about twice the number of filaments.   Embodiment 8. The method of embodiment 1, wherein the number of filaments is from about 6 or more.   Embodiment 9. The method of embodiment 1, wherein the mandrel comprises a plurality of grooves and further wherein the filaments are disposed into the grooves during the braiding of steps (h) through (i).   Embodiment 10. The method of embodiment 9, wherein the filaments are tangentially disposed on the mandrel within the grooves during the braiding steps (h) through (i).   Embodiment 11. The method of embodiment 1, wherein the securement projections at the distal end of the braiding mandrel are selected from the group consisting of hooks, pins, tabs, screws and combinations thereof.   Embodiment 12. The method of embodiment 1, wherein the securement projections at the distal end of the braiding mandrel are removable from the mandrel.   Embodiment 13. The method of embodiment 1, wherein the distal end of the braiding material further comprises a collar having the securement projections disposed thereto, and further wherein the securement projections are selected from the group consisting of hooks, pins, tabs, screws and combinations thereof.   Embodiment 14. The method of embodiment 9, wherein steps (h) through (i) are continued until the filaments are braided to a portion of the mandrel near the proximal end of the mandrel, and further comprising the step of securing the filaments to the portion of the mandrel while maintaining the filaments under a tension force from about 0.25 pound-force to about 5 pound-force.   Embodiment 15. The method of embodiment 14, further comprising heat treating the filaments while the filaments are disposed on the mandrel.   Embodiment 16. The method of embodiment 9, wherein the mandrel comprises a first portion having a first diameter, and a second portion having a second diameter, wherein the first diameter is different from the second diameter, and wherein the grooves are disposed throughout said first and second portion, and further comprising the step of applying a tension force from the constant force braiding carriers to the filaments so that a braiding angle between intersecting braided filaments is substantially equal in the first and second portions.   Embodiment 17. The method of embodiment 16, wherein the mandrel further comprises a transition portion between the first and second portions and further wherein the braiding angle is substantially equal in the first portion, the transition portion and the second portion.   Embodiment 18. The method of embodiment 1, wherein the filaments are selected from the group of metallic filaments, polymeric filaments, and combinations thereof.   Embodiment 19. The method of embodiment 1, wherein the filaments are metallic filaments comprise nitinol.   Embodiment 20. A method for braiding a stent comprising: (a) providing a number of elongate filaments, each of the filaments having opposed ends and an intermediate portion between the opposed ends; (b) providing a number of braiding carriers; (c) providing a braiding mandrel having opposed proximal and distal ends, the braiding mandrel comprising a number of circumferentially spaced-apart securement projections at the distal end, the mandrel further comprising a plurality of grooves; (d) securably disposing the intermediate portion of one of the filaments to one of the securement projections at the distal end of the mandrel; (e) securing one of the opposed ends of the one filament to one of the braiding carriers; (f) securing the other opposed end of the one filament to a different second braiding carrier; (g) repeating steps (d) through (f) until all of the intermediate portions of the filaments are securably disposed to different ones of the securement projections and until each end of the number of filaments are secured to a different one of the braiding carriers; (h) moving the braiding carriers around the mandrel; (i) longitudinally advancing the mandrel relative to a direction substantially perpendicular to the motion of the braiding carriers to braid the filaments to form a braided stent; and (j) applying a constant tension force from the braiding barriers to the filaments during the braiding steps (h) through (i).   Embodiment 21. The method of embodiment 20, wherein step (h) includes moving the braiding carriers in a generally circular and serpentine motion about a circumferential plane of the mandrel.   Embodiment 22. The method of embodiment 20, wherein the braiding carriers are constant force carriers and further wherein the ends of the filaments are securably disposed to the constant force carriers without spooling the filaments to the constant force carriers.   Embodiment 23. The method of embodiment 20, wherein the braiding carriers comprise a bobbin and wherein a portion of the filament is spooled about the bobbin.   Embodiment 24. The method of embodiment 20, wherein the constant tension force is from about 0.25 pound-force to about 5 pound-force.   Embodiment 25. A method for braiding a stent comprising: (a) providing a number of elongate filaments, each of the filaments having opposed ends and an intermediate portion between the opposed ends; (b) providing a number of tensioned braiding carriers; (c) providing a braiding mandrel having opposed proximal and distal ends, the braiding mandrel comprising a number of circumferentially spaced-apart securement projections at the distal end, the braiding mandrel further comprising a plurality of grooves; (d) securably disposing the intermediate portion of one of the filaments to one of the securement projections at the distal end of the braiding mandrel; (e) securing one of the opposed ends of the one filament to one of the tensioned braiding carriers without spooling the one filament to the one tensioned braiding carrier; (f) securing the other opposed end of the one filament to a different second tensioned carrier without spooling the one filament to the second tensioned carrier; (g) repeating steps (d) through (f) until all of the intermediate portions of the filaments are securably disposed to different ones of the securement projections and until each end of the number of filaments are secured to a different one of the tensioned carriers; (h) moving the tensioned carriers around the mandrel; and (i) longitudinally advancing the mandrel relative to a direction substantially perpendicular to the motion of the tensioned carriers to braid the filaments by tangentially disposing the filaments into the grooves to braid the filaments to form a braided stent.   Embodiment 26. The method of embodiment 25, wherein step (h) includes moving the braiding carriers in a generally circular and serpentine motion about a circumferential plane of the mandrel.   Embodiment 27. The method of embodiment 25, further comprising applying a constant tension force is from about 0.25 pound-force to about 5 pound-force.   Embodiment 28. A braided stent comprising: a plurality of elongate filaments inter-braided to form a tubular well structure, the filaments being inter-braided at a braiding angle formed at crossing filament locations; the tubular wall structure comprising a first portion having a first diameter, a second portion having a second diameter which is different from the second diameter and a transition portion disposed between the first portion and the second portion; wherein the braiding angles in the first portion are substantially equal, wherein the braiding angles in the second portion are substantially equal, and wherein the braiding angles in the transition portion are substantially equal.   Embodiment 29. The braided stent of embodiment 28, wherein the braiding angles in the first portion, wherein the braiding angles in the second portion and wherein the braiding angles in the transition portion are substantially equal.   Embodiment 30. The braided stent of embodiment 29, wherein the braiding angles in the first portion, the second portion and the transition portion are all within 5 degrees of one and the other.   Embodiment 31. The braided stent of embodiment 29, wherein the braiding angles in the first portion, the second portion and the transition portion are all within 1 degree of one and the other.   Embodiment 32. The braided stent of embodiment 29, wherein the braiding angle is an obtuse angle between longitudinally extending inter-braided filaments.   Embodiment 33. The braided stent of embodiment 28, wherein at least one of the braiding angles in the first portion, in the second portion or in the transition portion are different from the braiding angles from the other portions.   Embodiment 34. The braided stent of embodiment 28, wherein the filaments are selected from the group consisting of metallic filaments, polymeric filaments and combinations thereof.   Embodiment 35. The braided stent of embodiment 28, wherein the filaments are metallic filaments comprising nitinol.   Embodiment 36. A braiding mandrel for braiding a tubular stent comprising: an elongate tubular member having opposed proximal and distal ends; securement projections circumferentially disposed at spaced-apart locations at the distal end for engaging a filament from a braiding machine; a plurality of angularly disposed grooves along the longitudinal length of the member.   Embodiment 37. The braiding mandrel of embodiment 36, wherein the angularly disposed grooves extend at an angle from about 5° to about 85° from a longitudinal axis of the member.   Embodiment 38. The braiding mandrel of embodiment 36, further comprising: a plurality of spaced-apart projections wherein spaces between the projections define the plurality of angularly disposed grooves in the elongate member.   Embodiment 39. The braiding mandrel of embodiment 36, wherein the securement projections are selected from the group consisting of hooks, pins, tabs, screws and combinations thereof.   Embodiment 40. The braiding mandrel of embodiment 36 further comprising a collar disposed at the distal end of the tubular member, wherein the securement projections are disposed on the collar.   Embodiment 41. The braiding mandrel of embodiment 36, wherein the tubular member is a metallic member.   Embodiment 42. The braiding mandrel of embodiment 36, wherein the tubular member has a substantially constant diameter.   Embodiment 43. The braiding mandrel of embodiment 36, wherein the tubular member as a varied diameter.   Embodiment 44. The method of embodiment 1, wherein step (e) is performed without spooling the one filament to the one tensioned braiding carrier and step (f) is performed without spooling the one filament to the second tensioned braiding carrier.   

     While various embodiments of the present invention are specifically illustrated and/or described herein, it will be appreciated that modifications and variations of the present invention may be effected by those skilled in the art without departing from the spirit and intended scope of the invention. Further, any of the embodiments or aspects of the invention as described in the claims or in the specification may be used with one and another without limitation.