Connect public, paid and private patent data with Google Patents Public Datasets

High strength and high density intraluminal wire stent

Download PDF

Info

Publication number
US20020040238A1
US20020040238A1 US09977823 US97782301A US2002040238A1 US 20020040238 A1 US20020040238 A1 US 20020040238A1 US 09977823 US09977823 US 09977823 US 97782301 A US97782301 A US 97782301A US 2002040238 A1 US2002040238 A1 US 2002040238A1
Authority
US
Grant status
Application
Patent type
Prior art keywords
wire
stent
wave
fig
formed
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US09977823
Inventor
James Rudnick
Dominik Wiktor
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Boston Scientific Scimed Inc
Original Assignee
Meadox Medicals Inc
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Family has litigation

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/88Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure the wire-like elements formed as helical or spiral coils
    • BPERFORMING OPERATIONS; TRANSPORTING
    • B21MECHANICAL METAL-WORKING WITHOUT ESSENTIALLY REMOVING MATERIAL; PUNCHING METAL
    • B21FWORKING OR PROCESSING OF METAL WIRE
    • B21F45/00Wire-working in the manufacture of other particular articles
    • B21F45/008Wire-working in the manufacture of other particular articles of medical instruments, e.g. stents, corneal rings
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/04Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
    • A61F2/06Blood vessels
    • A61F2/07Stent-grafts
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, E.G. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2220/00Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2220/0025Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
    • A61F2220/0058Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements soldered or brazed or welded

Abstract

An intraluminally implantable stent is formed of helically wound wire. The stent has a generally elongate tubular configuration and is radially expandable after implantation in a body vessel. The wire includes successively formed waves along the length of the wire. When helically wound into a tube, the waves are longitudinally nested along the longitudinal extent of the stent so as to form a densely compacted wire configuration. After radial expansion the stent maintains high radial compressive strength and wire density to retard tissue ingrowth.

Description

    FIELD OF THE INVENTION
  • [0001]
    The present invention relates generally to implantable intraluminal stents and more particularly, the present invention relates to an improved high strength intraluminal stent having increased wire density.
  • BACKGROUND OF THE INVENTION:
  • [0002]
    It is well known to employ endoprostheses for the treatment of diseases of various body vessels. Intraluminal devices of this type are commonly referred to as stents. These devices are typically intraluminally implanted by use of a catheter into various body organs such as the vascular system, the bile tract and the urogenital tract. Many of the stents are radially compressible and expandable so that they may be easily inserted through the lumen in a collapsed or unexpanded state. Some stent designs are generally flexible so they can be easily maneuvered through the various body vessels for deployment. Once in position, the stent may be deployed by allowing the stent to expand to its uncompressed state or by expanding the stent by use of a catheter balloon.
  • [0003]
    As stents are normally employed to hold open an otherwise blocked, constricted or occluded lumen; a stent must exhibit a relatively high degree of radial or hoop strength in its expanded state. The need for such high strength stents is especially seen in stents used in the urogenital or bile tracts where disease or growth adjacent the lumen may exert an external compressive force thereon which would tend to close the lumen.
  • [0004]
    One particular form of stent currently being used is a wire stent. Stents of this type are formed by single or multiple strands of wire which may be formed into a shape such as a mesh coil, helix or the like which is flexible and readily expandable. The spaces between the coiled wire permit such flexibility and expansion. However, in certain situations, such as when the stent is employed in the urogenital or bile tract, it is also desirable to inhibit tissue ingrowth through the stent. Such ingrowth through the stent could have a tendency to reclose or occlude the open lumen. The open spaces between the wires forming the stent, while facilitating flexibility and expansion, have a tendency to allow such undesirable tissue ingrowth.
  • [0005]
    Attempts have been made to provide a stent which has less open space and more solid wire. U.S. Pat. No. 5,133,732 shows a wire stent where the wire forming the stent is overlapped during formation to provide less open space. However such overlapping wire increases the diameter of the stent and has a tendency to reduce flexibility and make implantation more difficult. It is therefore desirable to provide a wire stent which exhibits high compressive strength and full flexibility without allowing extensive ingrowth therethrough.
  • SUMMARY OF THE INVENTION
  • [0006]
    It is an object of the present invention to provide an intraluminal stent which exhibits high compressive strength and is resistive to tissue ingrowth.
  • [0007]
    It is a further object of the present invention to provide a flexible wire stent having high compressive strength and maximum wire density to inhibit tissue ingrowth.
  • [0008]
    In the efficient attainment of these and other objects, the present invention provides an intraluminal stent including a generally elongate tubular body formed of a wound wire. The wire forming the stent is formed into successively shaped waves, the waves being helically wound along the length of the tube. The longitudinal spacing between the helical windings of the tube is formed to be less than twice the amplitude of the waves thereby resulting in a dense wire configuration.
  • [0009]
    As more particularly shown by way of the preferred embodiment herein, an intraluminal wire stent includes longitudinally adjacent waves being nested along the length of the tubular body. The peaks or apices of the longitudinally nested waves are linerally aligned. Further, the intraluminal stent so constructed would have a percentage of open surface area in relationship to the total surface area of the stent which is less than 30% in the closed state, resulting in less open area upon expansion which would inhibit tissue ingrowth.
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • [0010]
    [0010]FIG. 1 is a perspective view of a conventional helical coil formed of a single wound wire.
  • [0011]
    [0011]FIG. 2 is a perspective view of the stent of the present invention.
  • [0012]
    [0012]FIG. 3 is a perspective view of the stent of FIG. 1 exhibiting longitudinal flexibility.
  • [0013]
    [0013]FIG. 4 is a schematic showing of one wave of the wire forming the stent of FIG. 2.
  • [0014]
    [0014]FIG. 5 is a schematic showing of nested longitudinally adjacent waves of the stent of FIG. 2.
  • [0015]
    [0015]FIG. 6 is a perspective view of the stent of FIG. 2 shown in the open or exposed condition.
  • [0016]
    [0016]FIG. 7 shows a portion of a further embodiment of a wire used to form a stent in accordance with the present invention.
  • [0017]
    [0017]FIG. 8 shows a still further embodiment of a wire used to form a stent of the present invention, partially wound around a forming mandrel.
  • DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS:
  • [0018]
    A simple helically formed coil spring 10 is shown in FIG. 1. Coil spring 10 is formed of a single metallic wire 12 which for stent purposes may be formed of a suitably flexible biocompatible metal. The wire coil spring 10 defines generally a cylindrical tubular shape which is radially expandable upon application of outward radial pressure from the interior thereof.
  • [0019]
    The present invention shown in FIG. 2, improves upon the simple coil spring 10 shown in FIG. 1. However with reference to FIG. 1, certain terminology used hereinthroughout may be defined. As mentioned, the spring defines a generally elongate cylindrically tubular shape lying along a central axis χ. Wire 12 is helically wound, for example against a constant diameter mandrel (not shown), to form a longitudinally extending structure consisting of wire 12 and spaces or pitch 16 therebetween. Each individual winding 14 may be defined as the wire segment traversing one complete revolution around axis χ. As the wire is helically coiled about axis χ, each winding is successively longitudinally spaced from the next adjacent winding by a given distance.
  • [0020]
    For present purposes, the axial spacing between any point on the wire coil spring 10 to the point defining the next successive winding may be thought of as the pitch 16 of the wire coil spring 10. As so defined, the pitch of the coil spring 10 defines the spacing between windings and therefore the degree of compactness or compression of the wire coil spring 10.
  • [0021]
    Also with reference to FIG. 1, as the wire coil spring 10 has a generally cylindrical tubular shape, it defines an outside diameter d1 and an inside diameter d2 which would typically differ by twice the diameter d3 of wire 12. Further, wire coil spring 10 generally defines an outer cylindrical surface area along its length which may be thought of as being composed of solid surface portions defined by the outward facing surface of wire 12 itself and open surface portions defined by the spaces or pitch 16 multiplied by the number of wire windings 14. The ratio of open surface space to solid surface space may be varied by varying the so-defined pitch 16 of the wire coil spring 10. A smaller pitch coil, where the windings are more compacted or compressed, would result in an outer surface area having less open space than a coil formed to have greater spacing or pitch between the wire windings.
  • [0022]
    Having set forth the definitional convention used hereinthroughout, the present invention may be described with reference specifically to FIGS. 2-6. A wire stent 20 of the present invention is shown in FIG. 2. Wire stent 20 is generally in the form of an elongate cylindrically shaped tubular member defining a central open passage 21 therethrough. Stent 20 is formed of multiple windings 24 of a single wire 22 which in the present invention is metallic, preferably tantalum, as such wire exhibits sufficient spring elasticity for purposes which will be described in further detail hereinbelow.
  • [0023]
    While stent 20 may be formed by helically winding wire 22 much in a manner shown with respect to FIG. 1 to form wire coil spring 10, the present invention contemplates preshaping the wire 22 itself along its length prior to helically coiling the wire.
  • [0024]
    Referring now to FIG. 4, wire 22 in an elongate pre-helically coiled configuration may be shaped in a manner having a longitudinally extending wave-like pattern. Wave pattern 25 is defined by a plurality of continuously repeating wave lengths 27 therealong. It has been found advantageously that the waves may take the form specifically shown in FIGS. 4 and 5 for optimum results as a wire stent. However, for explanation purposes, the wave-like pattern 25 generally functions mathematically as sinusoidal wave, having a given amplitude A as measured from a central axis y and a peak-to-peak amplitude of 2A. The wave pattern 25 has a uniform preselected period λ equal to the transverse extent of a single wave length. The geometry of each wave length 27 is shown in FIG. 4.
  • [0025]
    The wave-like configuration imparted to wire 22 may be accomplished in a variety of forming techniques. One such technique is to pass wire 22 between the teeth of intermeshed gears (not shown) which would place a generally uniform sinusoidal wave-like crimp along the length of the wire. Other techniques may be used to form the specific shape shown in FIG. 4. Wire 22 may be passed through a pair of gear-like overlapping wheels (not shown) having depending interdigitating pins. By arranging the size, position and spacing of the pins, various wave-like configurations may be achieved. The particular shape shown with reference to FIGS. 4 and 5 has been selected as each wave length 27 includes a pair of non-curved linear sections 29 between curved peaks 31. As will be described with respect to FIG. 5, this configuration allows the waves to be stacked or nested with maximum compactness when the wire is helically wound around a forming mandrel (FIG. 8) into the shape shown in FIG. 2.
  • [0026]
    Referring now to FIG. 5, schematically shown is a portion of stent 20 of FIG. 2 which has been cut once, parallel to the χ axis and flattened after being wound in a helical fashion such as that described with respect to the wire coil spring 10 of FIG. 1. Wire 22 formed in the manner shown and described with respect to FIG. 4, may be helically wound around an appropriately shaped mandrel (FIG. 8). The width of the mandrel is selected in combination with the frequency and period of the waves forming wire 22 so that upon helical coiling therearound the waves forming each winding 24 are longitudinally stacked or nested within the waves formed by the longitudinally adjacent winding successively spaced therefrom.
  • [0027]
    As can be seen with respect to FIG. 5, the peaks 31 of the waves of longitudinally adjacent windings 24 are each linearly aligned so that each wave is stacked or nested within the next adjacent wave. In optimum configuration, the spacing or pitch 26 between each longitudinally successive winding 24 is constructed to be minimal. However, nesting or stacking does occur where the pitch or spacing between longitudinally adjacent windings 24 is less than 2A i.e. the peak-to-peak amplitude. As long as the pitch remains less than 2A each longitudinally adjacent winding 24 will be nested within the wave formed by the previously formed winding 24. By minimizing the pitch or spacing 26 between adjacent windings 24, the open space between windings may be minimized. The particular wave-like pattern imparted to wire 22 as shown in FIG. 4 allows particularly tight stacking of longitudinally adjacent windings.
  • [0028]
    The particular configuration of the stent 20 shown in FIG. 2, provides significant advantages in medical applications. The stent 20 of the present invention is typically implanted by means of a balloon catheter (not shown). The stent 20 in a closed form is held around a deflatable catheter balloon. The stent is then inserted into the lumen and located at the desired position. The shape of the closed stent shown in FIG. 2 permits ease of insertability. As shown in FIG. 3, the stent may be easily bent or flexed along its longitudinal extent. The spacing or pitch 26 of windings 24 facilitate such bending. This helps in the insertion and deployment of the stent through a lumen, as typically body lumens traverse a torturous path through the body which must be followed by the stent which is being deployed therein. Once properly located, the balloon is inflated and the stent is radially expanded for deployment. The balloon is then deflated, and the catheter is removed leaving the expanded stent in place.
  • [0029]
    The windings of stent 20 in closed condition are tightly nested. The cylindrical surface area formed by the coiled wire has greater wire density, i.e. more of the surface area is composed of solid wire while less of the surface area is composed by open space between the wire windings then in previous non-nested single wire stents. The wire surface area in the closed condition equals the wire surface area in an expanded condition. By maximizing the closed condition wire surface area, even when the stent is expanded such as shown in FIG. 6, the expanded wire surface area is also maximized reducing tissue ingrowth between the expanded windings of the stent. Contrary to a simple coil spring such as that shown in FIG. 1, the stent 20 of the present invention expands without significant foreshortening of the stent or rotation of the ends of the coil. Rather, expansion is achieved by a flattening or elongation of the individual waves of the stent 20. Once the stent is expanded after deployment to a shape shown in FIG. 6, the increased wire surface area as well as the particular shape of the wire provides sufficient radial strength to resist the compressive forces of a blocked, constricted or impinged upon lumen.
  • [0030]
    Additionally, the above-described benefits of the stent of the present invention are achieved without the necessity of longitudinally overlapping adjacent wire windings. In many prior art stents, the stents include portions of wire windings which are longitudinally overlapped. This increases the wall thickness of the stent thereat and results in a stent which is more difficult to implant in the body lumen by means of a balloon catheter. Also, such stents create an undesirable, more turbulent fluid flow therethrough. The stent of the present invention maximizes wire density, maintains a high degree of flexibility and radial compressive strength without increasing the stent wall thickness beyond the single wire diameter.
  • EXAMPLE
  • [0031]
    Mathematically, the geometric analysis of the preferred embodiment of the stent of the present invention may be described as follows with reference to FIGS. 4 and 5.
  • [0032]
    Each wave length 27 of the wave pattern 25 forming stent 20 is formed to include a straight leg segment 29 with a bend radius at peak 31. The angle at which the helix coils around the center line χ (FIG. 1) is assumed to be close to 90°, so that the successive windings 24 are positioned to be as close to concentric as possible while still maintaining a helical pattern.
  • [0033]
    The integer number of waves N per single circumference or single winding follows the equation: N = π D λ ;
  • [0034]
    where D is the diameter of the closed stent and X is the period of a single wave.
  • [0035]
    The number of helical windings M per stent is defined by the equation: M = L sin θ d 3 ;
  • [0036]
    where L is the overall stent length; θ is the angle of the straight leg segments 29 with respect the line of amplitude of the wave pattern; and d3 is the wire diameter.
  • [0037]
    The exterior exposed surface area of the stent is equivalent to the amount of wire packed within a fixed stent length. The total length Lw of wire employed to form the stent follows the equation: L w = MN ( 4 l + 4 ( r + d 3 2 ) π 180 ( 90 - θ ) )
  • [0038]
    where r is the radius defining the peak curvative; and l is the length of the straight line segment 29 of the wire.
  • [0039]
    It follows that the projected solid wire area is Lwd3 and the percentage of open space coverage (% open) is given by the equation: % OPEN = 100 ( 1 - L w d 3 π DL )
  • [0040]
    In a specific example, a stent having the parameters listed in Table I and formed in accordance with the present invention yields a percentage of open space (% open) equivalent to 28.959%.
    TABLE I
    L Length of Stent 1.000 in
    D Diameter of Closed Stent 0.157 in
    d3 Wire Diameter 0.010 in
    r Radius of Curvative of Peak 0.020 in
    N Number of Waves per Winding 3
    M Number of Windings per Stent 22.47
    l Length of Straight Portion of Stent 0.097 in
  • [0041]
    Further, it is found that an expanded stent constructed in accordance with the example set forth above, exhibits superior resistance to pressure P acting upon the stent in a radially compressive manner (FIG. 6). In the present and illustrative example, P has been has been determined, both mathematically and empirically, to be 10 psi.
  • [0042]
    It is further contemplated that the stent-of the present invention may be modified in various known manners to provide for increased strength and support. For example the end of wire 22 may be looped around an adjacent wave or extended to run along the length of the stent. The wire may be welded to each winding to add structural support such as is shown in U.S. Pat. No. 5,133,732. Also, each windings may be directly welded to the adjacent winding to form a support spine such as shown in U.S. Pat. No. 5,019,090.
  • [0043]
    Further, as mentioned above, wire 22 is helically wound around a mandrel to form the helical pattern shown in FIG. 1. While the angle at which the helix coils around the mandrel is quite small, a certain angle must be imparted to the uniform windings to form a coil. It is further contemplated that a helix-like winding may be formed by concentrically wrapping a wave pattern around the mandrel where the length of the sides of each wave are unequal. As shown in FIG. 7 a wave pattern 125 may be formed having leg segments 129 of uneven length. Wave pattern 125 includes individual wave lengths 127 having a first leg segment 129 a and a second leg segment 129 b. Leg segment 129 a is constructed to be shorter than leg segment 129 b. Thus wave pattern 125 has a step-type shape so that upon winding around a mandrel, the windings 124 coil in a helical-like fashion therearound. This provides a lengthwise extent to the coil without having to impart a helical wrap thereto. Forming the stent length in this manner may tend to result in better flow characteristics through the stent in use.
  • [0044]
    Other modifications which are within the contemplation of the present invention may be further described. FIG. 8 shows a wire 222 which has been preformed to have a wave pattern 225 which is generally triangular in shape. This wave pattern 225 includes individual wave lengths 227 having straight leg segments 229 a and 229 b which meet at an apex 231. Wire 222 so formed, may be wound around a mandrel 200. As the individual wave lengths 227 nest in a manner above described, the apices 231 of the wave length 227 are longitudinally aligned.
  • [0045]
    The winding of wire 222 around mandrel 200 takes place in the following manner. The formed wire Z22 is held in position while the mandrel is rotated in the direction of arrow A, thereby coiling the wire 222 around mandrel 200. The spacing or pitch 216 is created by subsequent vertical movement of the of the formed wire 222 along mandrel 200 while rotation thereof is taking place. When the winding is complete, the ends 233 of the wire 222 may be “tied off” by looping the end 233 around the next longitudinally adjacent winding.
  • [0046]
    While in the embodiment shown above, the amplitude of each wave is relatively uniform, it is contemplated that the wire could be formed to have waves of varied amplitude. For example, the wire could be formed so that at the ends of the wound stent the amplitude of the waves is relatively small while in the central portion of the stent the amplitude is relatively large. This provides a stent with a more flexible central section and more crush-resistant ends.
  • [0047]
    In certain situations the stent of the present invention may include a membrane covering (not shown) which would cover the entire stent. The wire surface of the stent would serve as a support surface for the membrane covering. The membrane covering would act as a further barrier to tissue ingrowth. Any membrane covering may be employed with the present invention such as a fabric or elastic film. Further, this membrane covering may be completely solid or may be porous. In addition, as above described, employing a formed wire having varied amplitude where the amplitude of the wire is smaller at the ends of the stent would help support the membrane covering as the crush-resistant ends would serve as anchors to support the membrane covering with little support necessary at the more flexible central section of the stent.
  • [0048]
    Various changes to the foregoing described and shown structures would not be evident to those skilled in the art. Accordingly, the particularly disclosed scope of the invention is set forth in the following claims.

Claims (18)

What is claimed is:
1. An intraluminal stent comprising:
a generally elongate tubular body formed of an elongate helically wound wire, the wire being formed into successive waves along the length of the wire, the waves being arranged in non-overlapping longitudinally spaced succession along the length of said tube, the longitudinal spacing of the helical windings being less than twice the amplitude of the wave.
2. An intraluminal stent of claim 1 wherein longitudinally adjacent ones of said waves are longitudinally nested along the length of said tubular body.
3. An intraluminal stent of claim 2 wherein said longitudinally nested waves define peaks which are linerally aligned.
4. An intraluminal stent of claim 1 wherein said longitudinal spacing of the helical windings is less than the amplitude of the wave.
5. An intraluminal stent of claim 1 wherein said stent includes said wire being helically wound in non-overlapping disposition and wherein said wire defines an open area between said helically wound wire and wherein said percentage of open surface area of said stent in relationship to the total surface area of said stent is less than 30% in the closed condition.
6. An intraluminal stent of claim 1 wherein said tubular body is uniformly flexible along the length thereof.
7. An intraluminal stent of claim 6 wherein said stent is radially expandable after intraluminal implantation.
8. A radially expandable generally tubular endoluminal implantable prosthesis comprising:
a wire which is wound in a helical configuration to define a generally elongate tubular body, the wire including successively formed waves along the length of said wire, each wire wave being non-overlappingly nested within the wave formed longitudinally thereadjacent.
9. A prosthesis of claim 8 wherein said wire waves are of generally uniform configuration defining a peak-to-peak amplitude of a preselected first dimension.
10. A prosthesis of claim 9 wherein said longitudinally adjacent wire waves are spaced apart a preselected second dimension which is less than the preselected first dimension.
11. A prosthesis of claim 10 wherein said wire has a given wire diameter and wherein said wound wire defines a generally cylindrical outer surface having solid portions formed by said wire and open portions formed between said wound wire.
12. A prosthesis of claim 11 wherein said generally cylindrical outer surface defines a total surface area including an open surface and a wire surface and wherein said non-expanded wire surface substantially exceeds said open surface.
13. A prosthesis of claim 12 wherein said open surface area is less than 30% of said total surface area.
14. An intraluminal stent comprising:
an elongate tubular body formed of a single wound wire;
said wire having a wave-like pattern defining a plurality of waves formed along the length of said wire, each said wave defining a leg segment between wave peaks, each leg segment being of a length different from the next adjacent leg segment.
15. An intraluminal stent of claim 14 wherein said wire is wound about a central axis forming said tubular body.
16. An intraluminal stent of claim 15 wherein tubular body includes longitudinally successive waves along the length thereof, each said wave being nested within the wave formed longitudinally thereadjacent.
17. An intraluminal stent of claim 14 wherein each wave is defined by a peak and a pair of wave leg segments extending from said peak.
18. An intraluminal stent of claim 17 wherein one of said wave leg segments of said pair has a length greater than the other wave leg segment of said pair.
US09977823 1994-08-12 2001-10-15 High strength and high density intraluminal wire stent Abandoned US20020040238A1 (en)

Priority Applications (4)

Application Number Priority Date Filing Date Title
US08289791 US5575816A (en) 1994-08-12 1994-08-12 High strength and high density intraluminal wire stent
US08708651 US5906639A (en) 1994-08-12 1996-09-05 High strength and high density intraluminal wire stent
US09271304 US6319277B1 (en) 1994-08-12 1999-03-17 Nested stent
US09977823 US20020040238A1 (en) 1994-08-12 2001-10-15 High strength and high density intraluminal wire stent

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US09977823 US20020040238A1 (en) 1994-08-12 2001-10-15 High strength and high density intraluminal wire stent
US10775536 US8092512B2 (en) 1994-08-12 2004-02-10 Nested stent

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US09271304 Continuation US6319277B1 (en) 1994-08-12 1999-03-17 Nested stent

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US10775536 Continuation US8092512B2 (en) 1994-08-12 2004-02-10 Nested stent

Publications (1)

Publication Number Publication Date
US20020040238A1 true true US20020040238A1 (en) 2002-04-04

Family

ID=23113118

Family Applications (5)

Application Number Title Priority Date Filing Date
US08289791 Expired - Lifetime US5575816A (en) 1994-08-12 1994-08-12 High strength and high density intraluminal wire stent
US08708651 Expired - Lifetime US5906639A (en) 1994-08-12 1996-09-05 High strength and high density intraluminal wire stent
US09271304 Expired - Lifetime US6319277B1 (en) 1994-08-12 1999-03-17 Nested stent
US09977823 Abandoned US20020040238A1 (en) 1994-08-12 2001-10-15 High strength and high density intraluminal wire stent
US10775536 Expired - Fee Related US8092512B2 (en) 1994-08-12 2004-02-10 Nested stent

Family Applications Before (3)

Application Number Title Priority Date Filing Date
US08289791 Expired - Lifetime US5575816A (en) 1994-08-12 1994-08-12 High strength and high density intraluminal wire stent
US08708651 Expired - Lifetime US5906639A (en) 1994-08-12 1996-09-05 High strength and high density intraluminal wire stent
US09271304 Expired - Lifetime US6319277B1 (en) 1994-08-12 1999-03-17 Nested stent

Family Applications After (1)

Application Number Title Priority Date Filing Date
US10775536 Expired - Fee Related US8092512B2 (en) 1994-08-12 2004-02-10 Nested stent

Country Status (8)

Country Link
US (5) US5575816A (en)
JP (1) JPH0857057A (en)
CA (1) CA2147548C (en)
DE (2) DE69532573T2 (en)
DK (1) DK0705577T3 (en)
EP (2) EP1360943A3 (en)
ES (1) ES2216003T3 (en)
FI (1) FI952214A (en)

Cited By (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20060020324A1 (en) * 2004-07-21 2006-01-26 Schmid Eric V Balloon expandable crush-recoverable stent device
US20060026815A1 (en) * 2002-09-04 2006-02-09 Orlando Padilla Slide and lock stent and method of manufacture from a single piece shape
US20060052861A1 (en) * 2002-12-24 2006-03-09 Novostent Corporation Vascular prothesis having interdigitating edges and methods of use
US20060136041A1 (en) * 2004-12-17 2006-06-22 Schmid Eric V Slide-and-lock stent
US20070032857A1 (en) * 2005-08-02 2007-02-08 Schmid Eric V Axially nested slide and lock expandable device
WO2008050115A1 (en) * 2006-10-23 2008-05-02 Anson Medical Limited Helical stent graft
US20080167708A1 (en) * 2006-11-17 2008-07-10 Doug Molland Stent having reduced passage of emboli and stent delivery system
US20080183275A1 (en) * 2007-01-26 2008-07-31 Eric Schmid Circumferentially nested expandable device
US20090043371A1 (en) * 2005-12-29 2009-02-12 Fearnot Neal E Endoluminal device including a mechanism for proximal or distal fixation, and sealing and methods of use thereof
US7722662B2 (en) 1998-02-17 2010-05-25 Reva Medical, Inc. Expandable stent with sliding and locking radial elements
US7947071B2 (en) 2008-10-10 2011-05-24 Reva Medical, Inc. Expandable slide and lock stent
US7988721B2 (en) 2007-11-30 2011-08-02 Reva Medical, Inc. Axially-radially nested expandable device
US8523936B2 (en) 2010-04-10 2013-09-03 Reva Medical, Inc. Expandable slide and lock stent
US9149378B2 (en) 2005-08-02 2015-10-06 Reva Medical, Inc. Axially nested slide and lock expandable device
US9408732B2 (en) 2013-03-14 2016-08-09 Reva Medical, Inc. Reduced-profile slide and lock stent

Families Citing this family (176)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
RU2089131C1 (en) * 1993-12-28 1997-09-10 Сергей Апполонович Пульнев Stent-expander
US6001123A (en) 1994-04-01 1999-12-14 Gore Enterprise Holdings Inc. Folding self-expandable intravascular stent-graft
US6165210A (en) 1994-04-01 2000-12-26 Gore Enterprise Holdings, Inc. Self-expandable helical intravascular stent and stent-graft
US5575816A (en) * 1994-08-12 1996-11-19 Meadox Medicals, Inc. High strength and high density intraluminal wire stent
US6331188B1 (en) 1994-08-31 2001-12-18 Gore Enterprise Holdings, Inc. Exterior supported self-expanding stent-graft
US5591230A (en) * 1994-09-07 1997-01-07 Global Therapeutics, Inc. Radially expandable stent
US6015429A (en) 1994-09-08 2000-01-18 Gore Enterprise Holdings, Inc. Procedures for introducing stents and stent-grafts
US7204848B1 (en) 1995-03-01 2007-04-17 Boston Scientific Scimed, Inc. Longitudinally flexible expandable stent
US5776181A (en) * 1995-07-25 1998-07-07 Medstent Inc. Expandable stent
US6261318B1 (en) * 1995-07-25 2001-07-17 Medstent Inc. Expandable stent
US6638293B1 (en) 1996-02-02 2003-10-28 Transvascular, Inc. Methods and apparatus for blocking flow through blood vessels
US5931830A (en) * 1995-12-07 1999-08-03 Sarcos L.C. Hollow coil guide wire apparatus for catheters
US6042605A (en) 1995-12-14 2000-03-28 Gore Enterprose Holdings, Inc. Kink resistant stent-graft
EP0950385A3 (en) 1995-12-14 1999-10-27 Prograft Medical, Inc. Stent-graft deployment apparatus and method
DE69729137D1 (en) * 1996-03-10 2004-06-24 Terumo Corp Stent implantation
DE69719237D1 (en) * 1996-05-23 2003-04-03 Samsung Electronics Co Ltd Flexible, self-expanding stent and method for its production
US5776183A (en) * 1996-08-23 1998-07-07 Kanesaka; Nozomu Expandable stent
US6352561B1 (en) 1996-12-23 2002-03-05 W. L. Gore & Associates Implant deployment apparatus
US6551350B1 (en) * 1996-12-23 2003-04-22 Gore Enterprise Holdings, Inc. Kink resistant bifurcated prosthesis
US5733330A (en) * 1997-01-13 1998-03-31 Advanced Cardiovascular Systems, Inc. Balloon-expandable, crush-resistant locking stent
US5925061A (en) 1997-01-13 1999-07-20 Gore Enterprise Holdings, Inc. Low profile vascular stent
US5976182A (en) * 1997-10-03 1999-11-02 Advanced Cardiovascular Systems, Inc. Balloon-expandable, crush-resistant locking stent and method of loading the same
US6951572B1 (en) 1997-02-20 2005-10-04 Endologix, Inc. Bifurcated vascular graft and method and apparatus for deploying same
US5830229A (en) 1997-03-07 1998-11-03 Micro Therapeutics Inc. Hoop stent
US5810872A (en) 1997-03-14 1998-09-22 Kanesaka; Nozomu Flexible stent
US6033433A (en) * 1997-04-25 2000-03-07 Scimed Life Systems, Inc. Stent configurations including spirals
EP0884029B1 (en) 1997-06-13 2004-12-22 Gary J. Becker Expandable intraluminal endoprosthesis
WO1999002105A1 (en) * 1997-07-08 1999-01-21 Novo Rps Ulc Expandable stent
FR2771921B1 (en) * 1997-12-09 2000-03-24 Jean Marie Lefebvre Stainless steel stent for implantation in a vascular conduit by means of an inflatable balloon
US7520890B2 (en) * 1998-01-26 2009-04-21 Phillips Peter W Reinforced graft and method of deployment
US20050154446A1 (en) * 1998-01-26 2005-07-14 Peter Phillips Reinforced graft
JP4197842B2 (en) 1998-01-26 2008-12-17 アンソン メディカル リミテッド Strengthening graft
JP4801838B2 (en) * 1998-03-05 2011-10-26 ボストン サイエンティフィック リミテッド Intraluminal stent
US6171334B1 (en) * 1998-06-17 2001-01-09 Advanced Cardiovascular Systems, Inc. Expandable stent and method of use
US7235096B1 (en) 1998-08-25 2007-06-26 Tricardia, Llc Implantable device for promoting repair of a body lumen
KR100617375B1 (en) 1998-09-08 2006-08-29 가부시키가이샤 이가키 이료 세케이 Stent for vessels
US6071307A (en) * 1998-09-30 2000-06-06 Baxter International Inc. Endoluminal grafts having continuously curvilinear wireforms
US6042597A (en) 1998-10-23 2000-03-28 Scimed Life Systems, Inc. Helical stent design
US8382821B2 (en) 1998-12-03 2013-02-26 Medinol Ltd. Helical hybrid stent
US9039755B2 (en) * 2003-06-27 2015-05-26 Medinol Ltd. Helical hybrid stent
US9155639B2 (en) * 2009-04-22 2015-10-13 Medinol Ltd. Helical hybrid stent
US6660030B2 (en) 1998-12-11 2003-12-09 Endologix, Inc. Bifurcation graft deployment catheter
US6733523B2 (en) 1998-12-11 2004-05-11 Endologix, Inc. Implantable vascular graft
US6187036B1 (en) 1998-12-11 2001-02-13 Endologix, Inc. Endoluminal vascular prosthesis
DE69927055T2 (en) 1998-12-11 2006-06-29 Endologix, Inc., Irvine Endoluminal vascular prosthesis
US6355057B1 (en) 1999-01-14 2002-03-12 Medtronic, Inc. Staggered endoluminal stent
US8034100B2 (en) 1999-03-11 2011-10-11 Endologix, Inc. Graft deployment system
US6261316B1 (en) 1999-03-11 2001-07-17 Endologix, Inc. Single puncture bifurcation graft deployment system
US6364903B2 (en) * 1999-03-19 2002-04-02 Meadox Medicals, Inc. Polymer coated stent
WO2000071058A1 (en) 1999-05-20 2000-11-30 Boston Scientific Limited Stent delivery system with nested stabilizer and method of loading and using same
US6551351B2 (en) 1999-07-02 2003-04-22 Scimed Life Systems Spiral wound stent
US6652570B2 (en) * 1999-07-02 2003-11-25 Scimed Life Systems, Inc. Composite vascular graft
US6554857B1 (en) * 1999-07-20 2003-04-29 Medtronic, Inc Transmural concentric multilayer ingrowth matrix within well-defined porosity
US6402779B1 (en) 1999-07-26 2002-06-11 Endomed, Inc. Balloon-assisted intraluminal stent graft
US20010018609A1 (en) 1999-08-11 2001-08-30 Scott Smith Seamless braided or spun stent cover
EP1767169B1 (en) 1999-09-01 2009-03-04 Boston Scientific Scimed, Inc. Tubular stent-graft composite device and method of manufacture
US6183481B1 (en) 1999-09-22 2001-02-06 Endomed Inc. Delivery system for self-expanding stents and grafts
EP1230649B1 (en) * 1999-11-11 2003-06-11 Olaf Peters Coil
US7717708B2 (en) * 2001-04-13 2010-05-18 Orametrix, Inc. Method and system for integrated orthodontic treatment planning using unified workstation
US6210431B1 (en) 1999-12-10 2001-04-03 John A. Power Ostial bifurcation lesion stenting catheter
US6221080B1 (en) 1999-12-10 2001-04-24 John A. Power Bifurcation lesion stenting catheter
US6312458B1 (en) 2000-01-19 2001-11-06 Scimed Life Systems, Inc. Tubular structure/stent/stent securement member
US6210433B1 (en) * 2000-03-17 2001-04-03 LARRé JORGE CASADO Stent for treatment of lesions of bifurcated vessels
US7722663B1 (en) * 2000-04-24 2010-05-25 Scimed Life Systems, Inc. Anatomically correct endoluminal prostheses
US6805704B1 (en) 2000-06-26 2004-10-19 C. R. Bard, Inc. Intraluminal stents
ES2274902T3 (en) 2000-08-23 2007-06-01 Lemaitre Acquisition Llc Process for manufacturing intravascular devices made to measure.
US6613077B2 (en) 2001-03-27 2003-09-02 Scimed Life Systems, Inc. Stent with controlled expansion
US6585753B2 (en) * 2001-03-28 2003-07-01 Scimed Life Systems, Inc. Expandable coil stent
EP1258230A3 (en) 2001-03-29 2003-12-10 CardioSafe Ltd Balloon catheter device
GB0121980D0 (en) 2001-09-11 2001-10-31 Cathnet Science Holding As Expandable stent
CN100502806C (en) 2001-11-09 2009-06-24 诺沃斯特公司 Balloon catheter with non-deployable stent
US20030135266A1 (en) 2001-12-03 2003-07-17 Xtent, Inc. Apparatus and methods for delivery of multiple distributed stents
US7892273B2 (en) 2001-12-03 2011-02-22 Xtent, Inc. Custom length stent apparatus
US7351255B2 (en) 2001-12-03 2008-04-01 Xtent, Inc. Stent delivery apparatus and method
US7147656B2 (en) 2001-12-03 2006-12-12 Xtent, Inc. Apparatus and methods for delivery of braided prostheses
US7294146B2 (en) 2001-12-03 2007-11-13 Xtent, Inc. Apparatus and methods for delivery of variable length stents
US7137993B2 (en) 2001-12-03 2006-11-21 Xtent, Inc. Apparatus and methods for delivery of multiple distributed stents
US7182779B2 (en) 2001-12-03 2007-02-27 Xtent, Inc. Apparatus and methods for positioning prostheses for deployment from a catheter
US8080048B2 (en) 2001-12-03 2011-12-20 Xtent, Inc. Stent delivery for bifurcated vessels
US7309350B2 (en) 2001-12-03 2007-12-18 Xtent, Inc. Apparatus and methods for deployment of vascular prostheses
US20030225439A1 (en) * 2002-05-31 2003-12-04 Cook Alonzo D. Implantable product with improved aqueous interface characteristics and method for making and using same
EP1528901A1 (en) 2002-08-15 2005-05-11 GMP Cardiac Care, Inc. Stent-graft with rails
US20050033405A1 (en) * 2002-08-15 2005-02-10 Gmp/Cardiac Care, Inc. Rail stent-graft for repairing abdominal aortic aneurysm
US6878162B2 (en) * 2002-08-30 2005-04-12 Edwards Lifesciences Ag Helical stent having improved flexibility and expandability
US8221495B2 (en) 2002-11-07 2012-07-17 Abbott Laboratories Integration of therapeutic agent into a bioerodible medical device
US8524148B2 (en) * 2002-11-07 2013-09-03 Abbott Laboratories Method of integrating therapeutic agent into a bioerodible medical device
US9296011B2 (en) * 2002-11-07 2016-03-29 Abbott Laboratories Prosthesis having varied concentration of beneficial agent
US20050033410A1 (en) 2002-12-24 2005-02-10 Novostent Corporation Vascular prothesis having flexible configuration
US6896697B1 (en) * 2002-12-30 2005-05-24 Advanced Cardiovascular Systems, Inc. Intravascular stent
US20040186551A1 (en) 2003-01-17 2004-09-23 Xtent, Inc. Multiple independent nested stent structures and methods for their preparation and deployment
US20040193141A1 (en) * 2003-02-14 2004-09-30 Leopold Eric W. Intravascular flow modifier and reinforcement device and deployment system for same
US7241308B2 (en) 2003-06-09 2007-07-10 Xtent, Inc. Stent deployment systems and methods
US7763063B2 (en) 2003-09-03 2010-07-27 Bolton Medical, Inc. Self-aligning stent graft delivery system, kit, and method
US8500792B2 (en) 2003-09-03 2013-08-06 Bolton Medical, Inc. Dual capture device for stent graft delivery system and method for capturing a stent graft
US8292943B2 (en) 2003-09-03 2012-10-23 Bolton Medical, Inc. Stent graft with longitudinal support member
US20080264102A1 (en) * 2004-02-23 2008-10-30 Bolton Medical, Inc. Sheath Capture Device for Stent Graft Delivery System and Method for Operating Same
US9198786B2 (en) * 2003-09-03 2015-12-01 Bolton Medical, Inc. Lumen repair device with capture structure
US7403966B2 (en) * 2003-12-08 2008-07-22 Freescale Semiconductor, Inc. Hardware for performing an arithmetic function
US7326236B2 (en) 2003-12-23 2008-02-05 Xtent, Inc. Devices and methods for controlling and indicating the length of an interventional element
US7497872B2 (en) * 2004-03-08 2009-03-03 Cook Incorporated Retainer for a stent-graft
US7323006B2 (en) 2004-03-30 2008-01-29 Xtent, Inc. Rapid exchange interventional devices and methods
US8317859B2 (en) 2004-06-28 2012-11-27 J.W. Medical Systems Ltd. Devices and methods for controlling expandable prostheses during deployment
US20050288766A1 (en) 2004-06-28 2005-12-29 Xtent, Inc. Devices and methods for controlling expandable prostheses during deployment
EP1789107B1 (en) 2004-08-30 2009-05-27 Interstitial Therapeutics Medical stent provided with inhibitors of atp synthesis
US7780721B2 (en) 2004-09-01 2010-08-24 C. R. Bard, Inc. Stent and method for manufacturing the stent
JP2006271901A (en) * 2005-03-30 2006-10-12 Nippon Zeon Co Ltd Coiled contrast marker, its manufacturing method and catheter
US20060259005A1 (en) 2005-05-11 2006-11-16 Angioscore, Inc. Methods and systems for delivering substances into luminal walls
US7938851B2 (en) 2005-06-08 2011-05-10 Xtent, Inc. Devices and methods for operating and controlling interventional apparatus
US20060282149A1 (en) 2005-06-08 2006-12-14 Xtent, Inc., A Delaware Corporation Apparatus and methods for deployment of multiple custom-length prostheses (II)
US7637939B2 (en) * 2005-06-30 2009-12-29 Boston Scientific Scimed, Inc. Hybrid stent
US7815674B1 (en) 2005-07-27 2010-10-19 Ragazzo John R Self-expanding stent system
US7867176B2 (en) * 2005-12-27 2011-01-11 Cordis Corporation Variable stiffness guidewire
US9456911B2 (en) 2006-02-14 2016-10-04 Angiomed Gmbh & Co. Medizintechnik Highly flexible stent and method of manufacture
EP1998716A4 (en) 2006-03-20 2010-01-20 Xtent Inc Apparatus and methods for deployment of linked prosthetic segments
US7785317B2 (en) 2006-03-29 2010-08-31 Codman & Shurtleff, Inc. Joined metal tubing and method of manufacture
US8690938B2 (en) * 2006-05-26 2014-04-08 DePuy Synthes Products, LLC Occlusion device combination of stent and mesh with diamond-shaped porosity
US8118859B2 (en) * 2006-05-26 2012-02-21 Codman & Shurtleff, Inc. Occlusion device combination of stent and mesh having offset parallelogram porosity
US7670353B2 (en) * 2006-06-12 2010-03-02 Codman & Shurtleff, Inc. Modified headpiece for hydraulic coil deployment system
US7766935B2 (en) 2006-06-12 2010-08-03 Codman & Shurtleff, Inc. Modified headpiece for hydraulic coil deployment system
US8585732B2 (en) * 2006-06-14 2013-11-19 DePuy Synthes Products, LLC Retrieval device with sidewall grippers
EP2059189A4 (en) * 2006-08-29 2013-07-10 Bard Inc C R Helical high fatigue stent-graft
US9622888B2 (en) 2006-11-16 2017-04-18 W. L. Gore & Associates, Inc. Stent having flexibly connected adjacent stent elements
US8523931B2 (en) 2007-01-12 2013-09-03 Endologix, Inc. Dual concentric guidewire and methods of bifurcated graft deployment
US8388679B2 (en) 2007-01-19 2013-03-05 Maquet Cardiovascular Llc Single continuous piece prosthetic tubular aortic conduit and method for manufacturing the same
US8328865B2 (en) 2007-02-12 2012-12-11 C. R. Bard, Inc. Highly flexible stent and method of manufacture
US8333799B2 (en) * 2007-02-12 2012-12-18 C. R. Bard, Inc. Highly flexible stent and method of manufacture
WO2008100780A3 (en) 2007-02-12 2008-10-30 Bard Inc C R Highly flexible stent and method of manufacture
US20080199510A1 (en) 2007-02-20 2008-08-21 Xtent, Inc. Thermo-mechanically controlled implants and methods of use
US8486132B2 (en) 2007-03-22 2013-07-16 J.W. Medical Systems Ltd. Devices and methods for controlling expandable prostheses during deployment
US9757263B2 (en) 2009-11-18 2017-09-12 Cook Medical Technologies Llc Stent graft and introducer assembly
US9180030B2 (en) 2007-12-26 2015-11-10 Cook Medical Technologies Llc Low profile non-symmetrical stent
US9226813B2 (en) 2007-12-26 2016-01-05 Cook Medical Technologies Llc Low profile non-symmetrical stent
US8574284B2 (en) 2007-12-26 2013-11-05 Cook Medical Technologies Llc Low profile non-symmetrical bare alignment stents with graft
US8926688B2 (en) 2008-01-11 2015-01-06 W. L. Gore & Assoc. Inc. Stent having adjacent elements connected by flexible webs
US8287538B2 (en) 2008-01-14 2012-10-16 Conventus Orthopaedics, Inc. Apparatus and methods for fracture repair
US9101503B2 (en) 2008-03-06 2015-08-11 J.W. Medical Systems Ltd. Apparatus having variable strut length and methods of use
US20130165967A1 (en) 2008-03-07 2013-06-27 W.L. Gore & Associates, Inc. Heart occlusion devices
US8236040B2 (en) 2008-04-11 2012-08-07 Endologix, Inc. Bifurcated graft deployment systems and methods
ES2638293T3 (en) * 2008-06-30 2017-10-19 Bolton Medical Inc. Systems of abdominal aortic aneurysms
EP2520320B1 (en) 2008-07-01 2016-11-02 Endologix, Inc. Catheter system
CA2739007C (en) 2008-09-25 2017-10-31 Advanced Bifurcation Systems, Inc. Partially crimped stent
US8828071B2 (en) 2008-09-25 2014-09-09 Advanced Bifurcation Systems, Inc. Methods and systems for ostial stenting of a bifurcation
US8808347B2 (en) 2008-09-25 2014-08-19 Advanced Bifurcation Systems, Inc. Stent alignment during treatment of a bifurcation
US8821562B2 (en) 2008-09-25 2014-09-02 Advanced Bifurcation Systems, Inc. Partially crimped stent
WO2010042854A1 (en) * 2008-10-10 2010-04-15 Orbusneich Medical, Inc. Bioabsorbable polymeric medical device
US8641753B2 (en) 2009-01-31 2014-02-04 Cook Medical Technologies Llc Preform for and an endoluminal prosthesis
US9101506B2 (en) 2009-03-13 2015-08-11 Bolton Medical, Inc. System and method for deploying an endoluminal prosthesis at a surgical site
US8506622B2 (en) * 2009-04-17 2013-08-13 Medtronic Vascular, Inc. Mobile external coupling for branch vessel connection
US8945202B2 (en) 2009-04-28 2015-02-03 Endologix, Inc. Fenestrated prosthesis
US9579103B2 (en) 2009-05-01 2017-02-28 Endologix, Inc. Percutaneous method and device to treat dissections
US8491646B2 (en) 2009-07-15 2013-07-23 Endologix, Inc. Stent graft
ES2549000T3 (en) 2009-07-27 2015-10-22 Endologix, Inc. endoprosthesis
GB0920327D0 (en) 2009-11-19 2010-01-06 Cook William Europ Stent graft
US20110178520A1 (en) 2010-01-15 2011-07-21 Kyle Taylor Rotary-rigid orthopaedic rod
CA2823873A1 (en) 2010-01-20 2011-07-28 Conventus Orthopaedics, Inc. Apparatus and methods for bone access and cavity preparation
JP2013521880A (en) 2010-03-08 2013-06-13 コンベンタス オーソピディックス, インコーポレイテッド Apparatus and method for securing a bone implant
US9199066B2 (en) 2010-03-12 2015-12-01 Quattro Vascular Pte Ltd. Device and method for compartmental vessel treatment
EP2549958A4 (en) 2010-03-24 2016-09-14 Advanced Bifurcation Systems Inc Methods and systems for treating a bifurcation with provisional side branch stenting
EP2549952A4 (en) 2010-03-24 2017-01-04 Advanced Bifurcation Systems Inc System and methods for treating a bifurcation
EP2380604A1 (en) 2010-04-19 2011-10-26 InnoRa Gmbh Improved coating formulations for scoring or cutting balloon catheters
US8801775B2 (en) * 2010-04-27 2014-08-12 Medtronic Vascular, Inc. Helical stent with opposing and/or alternating pitch angles
US8389041B2 (en) 2010-06-17 2013-03-05 Abbott Cardiovascular Systems, Inc. Systems and methods for rotating and coating an implantable device
US8632559B2 (en) 2010-09-21 2014-01-21 Angioscore, Inc. Method and system for treating valve stenosis
WO2012068298A1 (en) 2010-11-17 2012-05-24 Endologix, Inc. Devices and methods to treat vascular dissections
US8696741B2 (en) 2010-12-23 2014-04-15 Maquet Cardiovascular Llc Woven prosthesis and method for manufacturing the same
WO2012109365A1 (en) 2011-02-08 2012-08-16 Advanced Bifurcation Systems, Inc. System and methods for treating a bifurcation with a fully crimped stent
CA2826760A1 (en) 2011-02-08 2012-08-16 Advanced Bifurcation Systems, Inc. Multi-stent and multi-balloon apparatus for treating bifurcations and methods of use
CN103561807B (en) 2011-03-01 2015-11-25 恩朵罗杰克斯股份有限公司 The catheter system and method of use
US9770232B2 (en) 2011-08-12 2017-09-26 W. L. Gore & Associates, Inc. Heart occlusion devices
JP6030667B2 (en) 2012-02-08 2016-11-24 クアトロ・ヴァスキュラー・ピーティーイー・リミテッド Limiting structure comprises a non-linear axial struts
US9216033B2 (en) 2012-02-08 2015-12-22 Quattro Vascular Pte Ltd. System and method for treating biological vessels
JP6238959B2 (en) 2012-04-12 2017-11-29 ボルトン メディカル インコーポレイテッド Vascular prosthesis delivery device and methods of use
US20140121756A1 (en) * 2012-10-25 2014-05-01 W. L. Gore & Associates, Inc. Stent with varying cross-section
US9439751B2 (en) 2013-03-15 2016-09-13 Bolton Medical, Inc. Hemostasis valve and delivery systems
US8734198B1 (en) 2013-03-15 2014-05-27 Edward B. Seldin Educational toy, geometric puzzle construction system
US9808230B2 (en) 2014-06-06 2017-11-07 W. L. Gore & Associates, Inc. Sealing device and delivery system

Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5019085A (en) * 1988-10-25 1991-05-28 Cordis Corporation Apparatus and method for placement of a stent within a subject vessel
US5183085A (en) * 1991-09-27 1993-02-02 Hans Timmermans Method and apparatus for compressing a stent prior to insertion
US5330500A (en) * 1990-10-18 1994-07-19 Song Ho Y Self-expanding endovascular stent with silicone coating
US5554181A (en) * 1994-05-04 1996-09-10 Regents Of The University Of Minnesota Stent
US5653727A (en) * 1987-10-19 1997-08-05 Medtronic, Inc. Intravascular stent
US6165210A (en) * 1994-04-01 2000-12-26 Gore Enterprise Holdings, Inc. Self-expandable helical intravascular stent and stent-graft

Family Cites Families (62)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2780274A (en) * 1955-12-01 1957-02-05 Fred T Roberts Method of making flexible corrugated hose
US3029819A (en) * 1959-07-30 1962-04-17 J L Mcatee Artery graft and method of producing artery grafts
US3657744A (en) * 1970-05-08 1972-04-25 Univ Minnesota Method for fixing prosthetic implants in a living body
US3805301A (en) * 1972-07-28 1974-04-23 Meadox Medicals Inc Tubular grafts having indicia thereon
US4047252A (en) * 1976-01-29 1977-09-13 Meadox Medicals, Inc. Double-velour synthetic vascular graft
US4130904A (en) * 1977-06-06 1978-12-26 Thermo Electron Corporation Prosthetic blood conduit
US4164045A (en) * 1977-08-03 1979-08-14 Carbomedics, Inc. Artificial vascular and patch grafts
US4300244A (en) * 1979-09-19 1981-11-17 Carbomedics, Inc. Cardiovascular grafts
DE3342798T (en) * 1982-04-30 1985-01-10
US4517687A (en) * 1982-09-15 1985-05-21 Meadox Medicals, Inc. Synthetic woven double-velour graft
US4580568A (en) * 1984-10-01 1986-04-08 Cook, Incorporated Percutaneous endovascular stent and method for insertion thereof
EP0201466A3 (en) * 1985-04-10 1987-10-14 Medinvent S.A. Coil spring for transluminal implantation and planar blank for the manufacture thereof
US4733665C2 (en) * 1985-11-07 2002-01-29 Expandable Grafts Partnership Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft
DE3640745A1 (en) * 1985-11-30 1987-06-04 Ernst Peter Prof Dr M Strecker Catheter for producing or extending connections to or between body cavities
US4665918A (en) * 1986-01-06 1987-05-19 Garza Gilbert A Prosthesis system and method
US4649922A (en) * 1986-01-23 1987-03-17 Wiktor Donimik M Catheter arrangement having a variable diameter tip and spring prosthesis
EP0556940A1 (en) * 1986-02-24 1993-08-25 Robert E. Fischell Intravascular stent
US4878906A (en) * 1986-03-25 1989-11-07 Servetus Partnership Endoprosthesis for repairing a damaged vessel
GB2189150B (en) * 1986-04-21 1990-02-14 Medinvent Sa Prosthesis and process for its manufacture
US4762128A (en) * 1986-12-09 1988-08-09 Advanced Surgical Intervention, Inc. Method and apparatus for treating hypertrophy of the prostate gland
US4893623A (en) * 1986-12-09 1990-01-16 Advanced Surgical Intervention, Inc. Method and apparatus for treating hypertrophy of the prostate gland
US4907336A (en) * 1987-03-13 1990-03-13 Cook Incorporated Method of making an endovascular stent and delivery system
US5041126A (en) * 1987-03-13 1991-08-20 Cook Incorporated Endovascular stent and delivery system
US4800882A (en) * 1987-03-13 1989-01-31 Cook Incorporated Endovascular stent and delivery system
US4816028A (en) * 1987-07-01 1989-03-28 Indu Kapadia Woven vascular graft
US4969458A (en) * 1987-07-06 1990-11-13 Medtronic, Inc. Intracoronary stent and method of simultaneous angioplasty and stent implant
US4886062A (en) * 1987-10-19 1989-12-12 Medtronic, Inc. Intravascular radially expandable stent and method of implant
US5019090A (en) * 1988-09-01 1991-05-28 Corvita Corporation Radially expandable endoprosthesis and the like
US4913141A (en) * 1988-10-25 1990-04-03 Cordis Corporation Apparatus and method for placement of a stent within a subject vessel
US4950227A (en) * 1988-11-07 1990-08-21 Boston Scientific Corporation Stent delivery system
US4886500A (en) * 1988-11-07 1989-12-12 Lazarus Harrison M External guide wire
US4856516A (en) * 1989-01-09 1989-08-15 Cordis Corporation Endovascular stent apparatus and method
US5163958A (en) * 1989-02-02 1992-11-17 Cordis Corporation Carbon coated tubular endoprosthesis
US4994071A (en) * 1989-05-22 1991-02-19 Cordis Corporation Bifurcating stent apparatus and method
US5171262A (en) * 1989-06-15 1992-12-15 Cordis Corporation Non-woven endoprosthesis
US5015253A (en) * 1989-06-15 1991-05-14 Cordis Corporation Non-woven endoprosthesis
EP0408245B1 (en) * 1989-07-13 1994-03-02 American Medical Systems, Inc. Stent placement instrument
CA2026604A1 (en) * 1989-10-02 1991-04-03 Rodney G. Wolff Articulated stent
US5578071A (en) * 1990-06-11 1996-11-26 Parodi; Juan C. Aortic graft
US5064435A (en) * 1990-06-28 1991-11-12 Schneider (Usa) Inc. Self-expanding prosthesis having stable axial length
US5139480A (en) * 1990-08-22 1992-08-18 Biotech Laboratories, Inc. Necking stents
US5176625A (en) * 1990-10-25 1993-01-05 Brisson A Glen Stent for ureter
US5160341A (en) * 1990-11-08 1992-11-03 Advanced Surgical Intervention, Inc. Resorbable urethral stent and apparatus for its insertion
US5217483A (en) * 1990-11-28 1993-06-08 Numed, Inc. Intravascular radially expandable stent
US5161547A (en) * 1990-11-28 1992-11-10 Numed, Inc. Method of forming an intravascular radially expandable stent
US5135536A (en) * 1991-02-05 1992-08-04 Cordis Corporation Endovascular stent and method
CA2065634C (en) * 1991-04-11 1997-06-03 Alec A. Piplani Endovascular graft having bifurcation and apparatus and method for deploying the same
US5147370A (en) * 1991-06-12 1992-09-15 Mcnamara Thomas O Nitinol stent for hollow body conduits
US5270213A (en) * 1991-06-21 1993-12-14 Porton Instruments, Inc. Protein sequencing
US5314472A (en) * 1991-10-01 1994-05-24 Cook Incorporated Vascular stent
US5290305A (en) * 1991-10-11 1994-03-01 Kanji Inoue Appliance collapsible for insertion into human organs and capable of resilient restoration
US5507767A (en) * 1992-01-15 1996-04-16 Cook Incorporated Spiral stent
JPH0641745A (en) 1992-07-24 1994-02-15 Hitachi Zosen Corp Vapor deposition method of aluminum on both surfaces of band-shaped substrate
BE1006440A3 (en) * 1992-12-21 1994-08-30 Dereume Jean Pierre Georges Em Luminal endoprosthesis AND METHOD OF PREPARATION.
JP3570434B2 (en) 1993-05-10 2004-09-29 住友電気工業株式会社 Stent and a method of manufacturing the same
KR970004845Y1 (en) * 1993-09-27 1997-05-21 이재용 Stent for expanding a lumen
US5643312A (en) 1994-02-25 1997-07-01 Fischell Robert Stent having a multiplicity of closed circular structures
ES2141576T5 (en) 1994-02-25 2006-08-01 David R. Fischell stent.
US5549663A (en) * 1994-03-09 1996-08-27 Cordis Corporation Endoprosthesis having graft member and exposed welded end junctions, method and procedure
DE69531239T2 (en) * 1994-04-01 2004-04-22 Prograft Medical, Inc., Palo Alto Selbstausdehnbarer stent and stent-graft transplant
US5575816A (en) * 1994-08-12 1996-11-19 Meadox Medicals, Inc. High strength and high density intraluminal wire stent
US6331188B1 (en) * 1994-08-31 2001-12-18 Gore Enterprise Holdings, Inc. Exterior supported self-expanding stent-graft

Patent Citations (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5653727A (en) * 1987-10-19 1997-08-05 Medtronic, Inc. Intravascular stent
US5019085A (en) * 1988-10-25 1991-05-28 Cordis Corporation Apparatus and method for placement of a stent within a subject vessel
US5330500A (en) * 1990-10-18 1994-07-19 Song Ho Y Self-expanding endovascular stent with silicone coating
US5183085A (en) * 1991-09-27 1993-02-02 Hans Timmermans Method and apparatus for compressing a stent prior to insertion
US6165210A (en) * 1994-04-01 2000-12-26 Gore Enterprise Holdings, Inc. Self-expandable helical intravascular stent and stent-graft
US5554181A (en) * 1994-05-04 1996-09-10 Regents Of The University Of Minnesota Stent

Cited By (36)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7722662B2 (en) 1998-02-17 2010-05-25 Reva Medical, Inc. Expandable stent with sliding and locking radial elements
US20060026815A1 (en) * 2002-09-04 2006-02-09 Orlando Padilla Slide and lock stent and method of manufacture from a single piece shape
US20060052861A1 (en) * 2002-12-24 2006-03-09 Novostent Corporation Vascular prothesis having interdigitating edges and methods of use
US7901448B2 (en) 2002-12-24 2011-03-08 Novostent Corporation Vascular prothesis having interdigitating edges and methods of use
US7763065B2 (en) 2004-07-21 2010-07-27 Reva Medical, Inc. Balloon expandable crush-recoverable stent device
US8512394B2 (en) 2004-07-21 2013-08-20 Reva Medical Inc. Balloon expandable crush-recoverable stent device
US20060020324A1 (en) * 2004-07-21 2006-01-26 Schmid Eric V Balloon expandable crush-recoverable stent device
US9173751B2 (en) 2004-12-17 2015-11-03 Reva Medical, Inc. Slide-and-lock stent
US8277500B2 (en) 2004-12-17 2012-10-02 Reva Medical, Inc. Slide-and-lock stent
US20060136041A1 (en) * 2004-12-17 2006-06-22 Schmid Eric V Slide-and-lock stent
US8292944B2 (en) 2004-12-17 2012-10-23 Reva Medical, Inc. Slide-and-lock stent
US20070032854A1 (en) * 2004-12-17 2007-02-08 Eric Schmid Slide-and-lock stent
US8617235B2 (en) 2005-08-02 2013-12-31 Reva Medical, Inc. Axially nested slide and lock expandable device
US9149378B2 (en) 2005-08-02 2015-10-06 Reva Medical, Inc. Axially nested slide and lock expandable device
US20070032857A1 (en) * 2005-08-02 2007-02-08 Schmid Eric V Axially nested slide and lock expandable device
US7914574B2 (en) 2005-08-02 2011-03-29 Reva Medical, Inc. Axially nested slide and lock expandable device
US20110172759A1 (en) * 2005-08-02 2011-07-14 Reva Medical, Inc. Axially nested slide and lock expandable device
US8728144B2 (en) * 2005-12-29 2014-05-20 Cook Medical Technologies Llc Endoluminal device including a mechanism for proximal or distal fixation, and sealing and methods of use thereof
US20090043371A1 (en) * 2005-12-29 2009-02-12 Fearnot Neal E Endoluminal device including a mechanism for proximal or distal fixation, and sealing and methods of use thereof
US20100324650A1 (en) * 2006-10-23 2010-12-23 Duncan Keeble Helical stent graft
WO2008050115A1 (en) * 2006-10-23 2008-05-02 Anson Medical Limited Helical stent graft
US20080167708A1 (en) * 2006-11-17 2008-07-10 Doug Molland Stent having reduced passage of emboli and stent delivery system
US7704275B2 (en) 2007-01-26 2010-04-27 Reva Medical, Inc. Circumferentially nested expandable device
US20100211159A1 (en) * 2007-01-26 2010-08-19 Reva Medical, Inc. Circumferentially nested expandable device
US8172894B2 (en) 2007-01-26 2012-05-08 Reva Medical, Inc. Circumferentially nested expandable device
US8540762B2 (en) 2007-01-26 2013-09-24 Reva Medical, Inc. Circumferentially nested expandable device
US20080183275A1 (en) * 2007-01-26 2008-07-31 Eric Schmid Circumferentially nested expandable device
US9314354B2 (en) 2007-11-30 2016-04-19 Reva Medical, Inc. Axially-radially nested expandable device
US7988721B2 (en) 2007-11-30 2011-08-02 Reva Medical, Inc. Axially-radially nested expandable device
US8460363B2 (en) 2007-11-30 2013-06-11 Reva Medical, Inc. Axially-radially nested expandable device
US7947071B2 (en) 2008-10-10 2011-05-24 Reva Medical, Inc. Expandable slide and lock stent
US9066827B2 (en) 2008-10-10 2015-06-30 Reva Medical, Inc. Expandable slide and lock stent
US8545547B2 (en) 2008-10-10 2013-10-01 Reva Medical Inc. Expandable slide and lock stent
US8523936B2 (en) 2010-04-10 2013-09-03 Reva Medical, Inc. Expandable slide and lock stent
US9452068B2 (en) 2010-04-10 2016-09-27 Reva Medical, Inc. Expandable slide and lock stent
US9408732B2 (en) 2013-03-14 2016-08-09 Reva Medical, Inc. Reduced-profile slide and lock stent

Also Published As

Publication number Publication date Type
DK705577T3 (en) grant
EP0705577B1 (en) 2004-02-18 grant
FI952214A0 (en) 1995-05-08 application
EP1360943A2 (en) 2003-11-12 application
US5575816A (en) 1996-11-19 grant
FI952214D0 (en) grant
ES2216003T3 (en) 2004-10-16 grant
US8092512B2 (en) 2012-01-10 grant
DE69532573T2 (en) 2004-12-16 grant
JPH0857057A (en) 1996-03-05 application
CA2147548A1 (en) 1996-02-13 application
US5906639A (en) 1999-05-25 grant
FI952214A (en) 1996-02-13 application
CA2147548C (en) 2004-08-31 grant
EP0705577A1 (en) 1996-04-10 application
US20040193251A1 (en) 2004-09-30 application
DE69532573D1 (en) 2004-03-25 grant
DK0705577T3 (en) 2004-03-08 grant
US6319277B1 (en) 2001-11-20 grant
EP1360943A3 (en) 2004-04-14 application

Similar Documents

Publication Publication Date Title
US6010529A (en) Expandable shielded vessel support
US5554181A (en) Stent
US6132461A (en) Stent with dual support structure
US5824077A (en) Clad composite stent
US6488703B1 (en) Helical stent design
US6146416A (en) Medical stents for body lumens exhibiting peristaltic motion
US5980565A (en) Sandwich stent
EP0466518B1 (en) Endovascular grafting apparatus and system
US6416539B1 (en) Controlled length intraluminal implant
US5993482A (en) Flat wire stent
US5681274A (en) Variable length uretheral stent
US6371979B1 (en) Stent delivery system
US5741333A (en) Self-expanding stent for a medical device to be introduced into a cavity of a body
US7556644B2 (en) Flexible stent
US6419694B1 (en) Medical prosthesis
US7419502B2 (en) Stent
US6117165A (en) Expandable intraluminal endoprosthesis
US20020055770A1 (en) Flexible and expandable stent
US3731671A (en) Low-friction catheter guide
EP1229864B1 (en) Multi-section filamentary endoluminal stent
US4760849A (en) Planar blank and a coil spring manufactured therefrom
US6409752B1 (en) Flexible stent having a pattern formed from a sheet of material
US5133732A (en) Intravascular stent
US20090024205A1 (en) Radially Expandable Stent
DE4407079B4 (en) Intraluminally jig and graft

Legal Events

Date Code Title Description
AS Assignment

Owner name: SCIMED LIFE SYSTEMS, INC., MINNESOTA

Free format text: MERGER;ASSIGNOR:MEADOX TECHNOLOGY, INC.;REEL/FRAME:018480/0181

Effective date: 19971231

Owner name: MEADOX TECHNOLOGY, INC., MINNESOTA

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:MEADOX MEDICALS, INC.;REEL/FRAME:018463/0917

Effective date: 19960401

AS Assignment

Owner name: BOSTON SCIENTIFIC SCIMED, INC., MINNESOTA

Free format text: CHANGE OF NAME;ASSIGNOR:SCIMED LIFE SYSTEMS, INC.;REEL/FRAME:018463/0593

Effective date: 20050101