CA2246386A1 - Medical stents, apparatus and method for making same - Google Patents
Medical stents, apparatus and method for making same Download PDFInfo
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- CA2246386A1 CA2246386A1 CA002246386A CA2246386A CA2246386A1 CA 2246386 A1 CA2246386 A1 CA 2246386A1 CA 002246386 A CA002246386 A CA 002246386A CA 2246386 A CA2246386 A CA 2246386A CA 2246386 A1 CA2246386 A1 CA 2246386A1
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- Prior art keywords
- stent
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
- A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
- A61F2/958—Inflatable balloons for placing stents or stent-grafts
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/02—Prostheses implantable into the body
- A61F2/04—Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
- A61F2/06—Blood vessels
- A61F2002/065—Y-shaped blood vessels
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
- A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
- A61F2002/91525—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other within the whole structure different bands showing different meander characteristics, e.g. frequency or amplitude
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
- A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
- A61F2002/91533—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other characterised by the phase between adjacent bands
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
- A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
- A61F2002/9155—Adjacent bands being connected to each other
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
- A61F2/91—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
- A61F2/915—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
- A61F2002/9155—Adjacent bands being connected to each other
- A61F2002/91583—Adjacent bands being connected to each other by a bridge, whereby at least one of its ends is connected along the length of a strut between two consecutive apices within a band
Abstract
An expandable stent and stent graft having a small initial diameter, flexibility along its longitudinal axis prior to expansion and a large expanded and rigid Local strain on the stent material is minimized, as and after the balloon is expanded. More particularly, the stent has rotation joints having minimal strain during stent expansion. The stent is substantially the same length before and after expansion and being flexible longitudinally when constrained, it is easy to locate. A method of manufacturing stents is described comprising rotation of a tube beneath a moving fil, with light passing through the film onto the tube, at selected locations. A laser scanning system for stent manufacture is also disclosed.
Description
W 0 98133546 rCTnB97/00231 Medical Stents~ ADParatus and Method for M~lkin~ Same Field of the Invention The present invention relates to an improved stent and stent graft for use in constricted body tubes, and for widening a stenosis in a body cavity such as in an artery, in the bile ducl, esophagus, and so forth. The present invention alsorelates to stent production technology, ancJ a method for manufacture of the improved stent device.
BackYround of the Invention and Dc~ tion of the Prior Art Intraluminal endovascular stenting is a method by which a prosthesis is inserted into a body tube and expanded so as to reopen a collapsed vessel wall and prevent the wall from recoll~r~ing into the lu~nen. Endovascular stenting is particularly useful for arteries which are blocked or narrowed and is an alternative to surgical procedures that intend to bypass the occlusion.
Previous structures used as stents or intraluminal vascular grafts have included coiled stainless steel springs; helical wound spring coil made from shape memory alloy; expanding metal stents formed in a zig-zag pattem; diamond shaped, rectangular .shaped, and other mesh and non-mesh clçsign~ Some of the stents currently available employ a self e~p~n(1ing concept, whereby stent expansion is primarily achieved by removing a restraint mech~ni~m holding the stent in a constricted configuration. Other stents in the prior art are delivered to the site by a balloon catheter system, and primarily employ balloon dilation to achieve proper stent expansion.
Problems with this variety of stents is inadequate radial force to m~int~in expansion; inal,propliate scaffolding of tissue to the wall; pre-dilated longitudinal rigidity which negatively impacts on stent delivery; and shortening of the stent as a consequence of radial expansion. Pre-dilation stent longitudinal rigidity is asignificant shortcoming, and prevents the threading of the stent through long . , ~. . .. .
Wo 98133546 PCrlIB97/0023 tortuous vessels and lesions. Shortening of the stent is also a problem, as it is important that the stent cover the entire lesion to minimi7e the risk of post-operative complications. Obviously, therefore, there is a need for a long yet ilexible stent that will provide the appropriate scaffolding effect, will be able to track well in-curved vessels, will not shorten during radial expansion, and yet will have sufficient out~ard radial force to hold the artery open, even in the presence of hard calcified lesions. The stent disclosed herein overcomes these disadvantages. No stent having all of the desired features appears to exist, prior to this invention which achieves most of these properties.
As is well known. a traditional :~lrf~rnz-tive to conventional vascular surgery has been percutaneous transluminal balloon angioplasty (PCTA). In this procedure, the angioplasty balloon is inflated within the stenosed artery to create, through ~hP~ing and mechanical trauma, a larKer inner lumen. This process, while succes.cful in achieving a larger lumen in most cases, can sometimes causelocal tears, dissections ;md p~ ion of plate into the lumen so that vessel blockage is caused rather than the desired vessel opening. In addition, the phenomenon of elastic recoil and intimal growth following arterial dilation often causes late restenosis (within six months) in more than about 30% of the patients undergoing the angloplasty balloon procedure. Because of the fear of the acute complication of sudden occlusion (abrupt closure), a surgical backup is needed in most places where PTCA is performed, This is yet another limitation of the mechanical balloon dilatation procedure.
It has beesl shown that stenting results in excellent acute results with adequate scaffolding of tears to the wall of the artery and wi~ generation of a large inner lumen. This large inner lumen, initially present after stenting~ has a lower restenosis rate after the procedure, as shown in the STRESS (N. Engl. J.
Med. 1994; 331:L 496-5~1) and BENESTENT (N. Engl. J. Med. 1994; 331: 489-95) studies. While the irmer lumen achieved using the self-exp~n-ling stents depends on the sizing of the stents relative to the vessel, the inner }umens that can "". ,~ .~ , . ...
Wo 98133546 PCT/IB97/00231 be achieved with balloon expandable stents depend both on the size and radially exr~nrling pressure of the balloon. The inner lumens achievable with balloon exp~n-l~ble stents can be further increased with further inflation of the balloon.
One of the major complications associated with stent use has been thrombosis. The problem occurs most commonly between day 2 and 6 of the implantation, but may also occur as late as 3 weeks after stenting. This complication is causcd hy clotting of the stent and is associated with high morbidity and mortality. It has been recently shown that the better the stent apposition against the wall and the larger the lumen is, the less likely that this complication will occur. In addition, it is very important that the stent cover the entire lesion since the existence of obstructions before or after the stent may also cause a complication.
The current balloon expandable stents have the significant limitation of relative, longitudinal rigiclity during delivery, and so do not allow for a very long stent to traverse the usual curves in the artery. This longihl-1in~1 rigidity during delivery is sought to be avaided by devices taught in the patents to Wolff (U.S.Patent No. 5,104,404) and to Pinchasik (U.S. Patent No. 5,449,373) in which the rigid Palmaz stent sections are c~-nnected together with flexible connections. For this reason, it is required ~hat the stent be long (to allow treatment of long lesions) and flexible upon insertion to site (to allow passage to and through tortuous locations) but yet have iarge radial force to unblock the vessel and excellent scaffolding so as to be able to hold the atherosclerotic material against the wall, even in bends and in hard calcified lesions. The stent should also allow for further balloon expansion if further lumen enlargement is required at particularlocations.
In U.S. Patent 5,104,404, Pinchasik attempts to address some of the shortcomings of the prior art by te~hing the use of different connectors ~articulation) between the rigid Palmaz stent segments, enabling more flexibility between the rigid parts.
.. " , "
It would be highly desirable, however, to have a stent having few or no longitlldin:~lly rigid parts so that it will be homogeneously flexible along its entire longitudinal axis when delivered on the catheter. Furthermore it would be extremely desirable to eliminzlte the longitudinal shortening of the stent during radial expansion to minimi7P stent misplacement.
Furthermore, in Palmas' stents marketed by Johnson & Johnson, as well as in others, during plastic deformation of the stent (i.e. balloon expansion) the strain is concentrated at small zones. This limits the properties of the m~teri~l that can be used as well as the radial force and the expansion rate. By distributing the strain over large zones, a less thick annealed material can be used to both avoid deterioration of the radial force of the stent when expanded, and to reduce the stent's constricted profile. There are obvious advantages to reduced stent thickness.
According to the prior art method ol manufacturing stents, the material is originally flat. The screen-like m~tP.ri~l is then rolled into a cylinder shape and laser welded or otherwise connected to forrn a tube - - the weld running the length of the longitudinal axis. This is a difficult and expensive manufacturing procedure. It also leads lo a potential lack of uniformity. The present invention, a new method of stent manufacture, as will be explained, results in a more uniformly expandable stent, one not having a weld line forrned after mesh formation.
Patents which relate to the field of stent geometry are as follows: U.S.
Patent Nos.5,354,309; 4,776,337; 5,356,423; 5,383,892; 5,178,618; 5,449,373; and~,104,404.
Summary of the Invention The object of the present invention is to provide a stent which has flexibility sub~n~ y along its lon~it~1~1in~l axis when constrained on a catheter ."" . . .. ..
W 0 98~3546 PCTnBg7/00231 to allow it to easily pass through and along highly curved body vessels and fluid-carrying tubes.
It is further an object of the invention to supply the constricted stent (i.e., before balloon expansion) with a minimum diameter to ease its passage for placement through a minisn~l diameter vascular port as well as to enable it to enter through narrow }umens of constricted body tubes.
It is further an object of the invention to provide a stent geometry which results in a more homogenous distribution of the strain on the stent material, reducing the maximum strain on the stent when expanded so that less material canbe used. Subjecting less material to the same balloon-expanding force can resultin greater radial expansion. This allows both a greater expansion ratio for the stent and smaller stent wall thickness.
It is further an object of this invention to allow a stent geometry and proper material to provide additional stent diameter expansion by elongatinn of the stent material (such aSt~ llm) and not by çll~nging the shape of the stent.
It is further an object of the invention to provide a stent which does not substantially change in length as the stent diameter is expanded during balloon inflation.
A further object of the present invention is to provide a method for fabricating stents and, in particular, the stents disclosed herein.
It is a further object of the invention to supply the stent with a graft material to be a stent graph as well as a stent graft of Y-shape for aortic aneurism.
Brief D~s~ ,tion of the D.~wi ~
Figure 1 is an elevational view of a stent (shown as a cylinder for illustrative purposes) in cylindrical coordinates;
Figure 2 is a parlial section of a stent, showing a pair of radial rings, unconnected in the longitudinal direction (for illustration) and showing a stentbefore expansion, having points or dots on the rings which will rotate 45'' upon WO 98/33S46 PCT~Bg7/00231 expansion due to balloon inflation. (In Figures 2- l 1, the interconnections hetween the adjacent radial rings of the stent are not shown.). A ring of the stent resembles a lock washer an un-hll~ting ring shape;
Figure 3 is a partial section of a stent showing the pair of adjacent radial rings of Figure 2, after expansion of the stent;
Figure 4 is a partial section of a pair of radial rings of a second embodiment of a stent, without longitudinal connection (for ease of illustration) before expansion, having points or dots on the rings which will rotate 90~ upon stent expansion;
Figure 5 is a partial section of another embodiment of a stent showing a pair of radial rings~ before expansion, having points or dots on the rings whichwill rotate 180~ upon expansion;
Figure 6 is a partial section of a pair of radial rings of another embodiment of the stent, again, before expansion, having points or dots on the rings which will rotate 360~ upon expansion;
Figure 7 is a partial section of a pair of radial rings of another embodiment of the stent, both before (on the right side) and after (on the left side) expansion, having two types of dots or points on the rings which will rotate through anglesof 45~ and 90~ respectively, upon expansion;
Figure 8 shows a partial section of a pair of radial rings of another embodiment of the stent, before expansion, in which the radial rings have two types of dots or points on the rings which will rotate through angles of 45~ and180~, respectively, upon expansion;
Figure 9 shows two pairs of radial rings of yet another embodiment of the stent, before expansion, in which adjacent rings are constructed with mirror images of each other;
Figure 10 shows four radial rings in which neighboring rings are offset, i.e., have constructions which differ by an angle of rotation from each other. The "z" and "~3" angles are shown on the axis; the "~" axis, corresponds to the angle "~" illustrated in Figure l;
Figure 11 shows a partial section of four rings of yet another embodiment of a stent, before expansion;
Figure 12 shows a graphical depiction of two types of longitll-lin~l connections between neighboring radial rings of a stent, the right side of the Figure being before stent expansion;.
Figure 13 shows a graphical representation of a section of an expanded stent which has been constructed such that some of the radial segments and some of the longitudinal cormections are deliberately omitted during manufacture;
Figure 14 is a perspective view of a stent according to the present invention with the stent in its constricted form, prior to expansion and wherein the connections between adjacent rings of the stent are straight, Figure 15 is ~ perspective view of the stent of Figure 14 with the stent in its expanded form;
Figure 16 is a perspective view of another embodiment of a stent in which the connections between the adjacent rings of the stent are also curved. The stent is shown in the constricted forrn prior to expansion;
Figure 17 is a perspective view of the stent of Figure 16 in its expanded form;
Figure 18 shows an enlarged partial section of another embodiment of a stent in which the stent joints (between the ~ ce~t rings) are circular, and thestent is in its constricted fi~rrn, prior to the expansion. Individual rings are formed with the circular joints, as we}l;
Figure 19 shows the portions of the stent of Figure 18 in its e~p~n-le(l form. Points A, B, C, D, E, F, G, H, I, J and K have been shown on both Pigs.
18 and 19 (opposed, offset U-shapes) to illustrate relative movement and location, a consequence of stent expansion;
., ~. i ...
WO 98/33546 PCT/IB97tO0231 Figure 20A shows a partial enlarged section of another embodiment of a stent with llnd~ ted (opposed, offset U-shapes) rings, strips or segments separating adjacent rings, ,and alternate rings having simple intersections between adjacent points on the same ring and circular joints between adjacent points.
Figure 20A shows the stent in a constricted form; Figure 20B is a schematic representation of the stent of Fig. 20A in an expanded forrn, Figures 21 an(l 22 show partial sections of a stent with undulated (opposed, offset U-shapes) radial strips or segments as in Figure 20A, forrning the rings, yet with the circular connectors being hollow. The rings are connected by longitudinal segments;
Figure 22 shows another embodiment with undulating rings, longitudinal connectors and simple intersections;
Figure 23 is a side elevational schematic view of a film contact im~ging apparatus for stent manufacture;
Figure 24 is a similar schematic view of a laser scanning system for stent manufacture;
Figure 25 is a schematic representation of a Y-tube stent graft in the open position, according to the present invention;
Figure 26 is a schematic representaion of a Y-tube stent graft in the closed configuration.
Figure 27 is an enlarged partial view of t~e stent of the present invention, in an embodiment where all the rings are in phase; and Figure 28 is an enlarged partial view of the stent of the present invention, in an embodiment where adjacent or paired rings are 180 degrees out of phase with one another. Of course, as will be appreciated from the description of the drawings and of the invention, all angles between 0 degrees and 180 degrees can be used for the lateral offset of the "peaks" and "valleys" of the adjacent rows.
Figure 28 shows that the repetitive "peaks" and "valleys" of adjacent rings are offset by about 150 to 160 degrees.
.," . , ",~
CA 02246386 l998-04-l4 wo 98133546 PCT/Is97tOO23 Detailed DescriPtion of 1he Invention The present invention relates to a novel stent construction. The stent geometry allows both longit~l~ins-l flexibility of the stent when the stent is constricted to its initial narrow diameter for threading through the body vessel, and maximum rigidity, after the stent is expanded to its final large diameter, for supporting the body vessel wall. The geometry of the stent is further designed to allow the stent to remain sub~t~nfi~lly the same length before and after expansion and even zero strain on the connection points..
Moreover, as will be described below, the stent geometry allows a substantially homogeneous distribution of strain on the stent material. This allows for less local strain (e.g. on the connection points securing neighboring radial rings of the stent to longitll-lin~l segments and forming the rings themselves), and thus a smaller stent profile is achieved. It aids stent delivery, inside body tubes. Also, the less material used for the stent, the less rejection of the body to the foreign material. This geometry of the stent also allows a further diameter expansion bymaterial stretching such as tantalum which allows up to about 40% elongation.
The stent's further expansion is better achieved by the homogeneous distributionof stress, a result of the new geometry.
Figure l shows a c ylindrical stent with orthogonal cylindrical coordinates (R, fl, Z). Coordinate Z co~ ollds to the }on&itu~lin~l central axis of the stent.
When Z=O, the stent's l<n~itu-lin~l end is described. The stent length, its longitudinal axis, is Z. Radius r refers to the radius of the stent from the longitudinal axis of the stent to the outer circumference of the stent. Radius r, of course, changes with stent dilation during deployment of the balloon or other expansion of the stent radiws by another merh~ni~m (e.g., memory metal). As shown in Figure 147 the stent 30, in its constricted state (i.e. before expansion), is a hollow cylinder, or is tube-like. The hollow cylinder has windings 31 on its surface joined together at points to forrn the radial rings. The stent has longitll~in~l flexibility, wvhen in its constrained diameter, and allows for radial wO 98l33546 PCT/IB97/0023 expansion. As shown in Figure lS, the stent 30, in its expanded state, has the radial rings opened, the windings uncurl from their constricted to their expanded state, providing a larger radius r for the hollow cylinder of the stent construction.
Figure 2 shows adjacent radial rings (1) and (2) of a stent. In the Figure (and in all of Figures 2-11) each ring is shown without the longitudinal connections which are provided between adjacent rings. The longitudinal connections are shown, for example, in Figures 14-16. Radial rings (1) and (2) are each originally7 i.e., before expansion, curved, with the curves of the rings crossing the Z = constam. axis of the ring. ~ach curved ring has dots or points (e.g. dot or point (3~ on ring 1, and dots or points (4), (5) and (6) on ring 2, on its curves During outward expansion of the stent, dots (5) and (6) rotate. During the rotation of the dots, no deformation occurs in the dots. During expansion, dot (5) rotates in a 45'' angle clockwise manner and dot (6) rotates in a 45~ angle counterclockwise manner, thereby resulting in stent geometry shown in Fig. 3.
Figure 3 shows two radial rings 1 and 2 of Figure 2 after m~xim:~l stent diameter expansion. Although the connections on the longitudinal axis are not shown in the Figure, ~he tesulting shape of the connected radial rings, after maximal expansion~ is a cylindrical mesh of rectangular boxes ~sirnilar to screening m~t~.ri~l) A hollow cylinder oi' rectangular boxes is formed. The rectangular mesh can be seen by reference to Figure 15.
As shown in Figures 4, 5 and 6, stents a~e depicted forrned of rings 1 and
BackYround of the Invention and Dc~ tion of the Prior Art Intraluminal endovascular stenting is a method by which a prosthesis is inserted into a body tube and expanded so as to reopen a collapsed vessel wall and prevent the wall from recoll~r~ing into the lu~nen. Endovascular stenting is particularly useful for arteries which are blocked or narrowed and is an alternative to surgical procedures that intend to bypass the occlusion.
Previous structures used as stents or intraluminal vascular grafts have included coiled stainless steel springs; helical wound spring coil made from shape memory alloy; expanding metal stents formed in a zig-zag pattem; diamond shaped, rectangular .shaped, and other mesh and non-mesh clçsign~ Some of the stents currently available employ a self e~p~n(1ing concept, whereby stent expansion is primarily achieved by removing a restraint mech~ni~m holding the stent in a constricted configuration. Other stents in the prior art are delivered to the site by a balloon catheter system, and primarily employ balloon dilation to achieve proper stent expansion.
Problems with this variety of stents is inadequate radial force to m~int~in expansion; inal,propliate scaffolding of tissue to the wall; pre-dilated longitudinal rigidity which negatively impacts on stent delivery; and shortening of the stent as a consequence of radial expansion. Pre-dilation stent longitudinal rigidity is asignificant shortcoming, and prevents the threading of the stent through long . , ~. . .. .
Wo 98133546 PCrlIB97/0023 tortuous vessels and lesions. Shortening of the stent is also a problem, as it is important that the stent cover the entire lesion to minimi7e the risk of post-operative complications. Obviously, therefore, there is a need for a long yet ilexible stent that will provide the appropriate scaffolding effect, will be able to track well in-curved vessels, will not shorten during radial expansion, and yet will have sufficient out~ard radial force to hold the artery open, even in the presence of hard calcified lesions. The stent disclosed herein overcomes these disadvantages. No stent having all of the desired features appears to exist, prior to this invention which achieves most of these properties.
As is well known. a traditional :~lrf~rnz-tive to conventional vascular surgery has been percutaneous transluminal balloon angioplasty (PCTA). In this procedure, the angioplasty balloon is inflated within the stenosed artery to create, through ~hP~ing and mechanical trauma, a larKer inner lumen. This process, while succes.cful in achieving a larger lumen in most cases, can sometimes causelocal tears, dissections ;md p~ ion of plate into the lumen so that vessel blockage is caused rather than the desired vessel opening. In addition, the phenomenon of elastic recoil and intimal growth following arterial dilation often causes late restenosis (within six months) in more than about 30% of the patients undergoing the angloplasty balloon procedure. Because of the fear of the acute complication of sudden occlusion (abrupt closure), a surgical backup is needed in most places where PTCA is performed, This is yet another limitation of the mechanical balloon dilatation procedure.
It has beesl shown that stenting results in excellent acute results with adequate scaffolding of tears to the wall of the artery and wi~ generation of a large inner lumen. This large inner lumen, initially present after stenting~ has a lower restenosis rate after the procedure, as shown in the STRESS (N. Engl. J.
Med. 1994; 331:L 496-5~1) and BENESTENT (N. Engl. J. Med. 1994; 331: 489-95) studies. While the irmer lumen achieved using the self-exp~n-ling stents depends on the sizing of the stents relative to the vessel, the inner }umens that can "". ,~ .~ , . ...
Wo 98133546 PCT/IB97/00231 be achieved with balloon expandable stents depend both on the size and radially exr~nrling pressure of the balloon. The inner lumens achievable with balloon exp~n-l~ble stents can be further increased with further inflation of the balloon.
One of the major complications associated with stent use has been thrombosis. The problem occurs most commonly between day 2 and 6 of the implantation, but may also occur as late as 3 weeks after stenting. This complication is causcd hy clotting of the stent and is associated with high morbidity and mortality. It has been recently shown that the better the stent apposition against the wall and the larger the lumen is, the less likely that this complication will occur. In addition, it is very important that the stent cover the entire lesion since the existence of obstructions before or after the stent may also cause a complication.
The current balloon expandable stents have the significant limitation of relative, longitudinal rigiclity during delivery, and so do not allow for a very long stent to traverse the usual curves in the artery. This longihl-1in~1 rigidity during delivery is sought to be avaided by devices taught in the patents to Wolff (U.S.Patent No. 5,104,404) and to Pinchasik (U.S. Patent No. 5,449,373) in which the rigid Palmaz stent sections are c~-nnected together with flexible connections. For this reason, it is required ~hat the stent be long (to allow treatment of long lesions) and flexible upon insertion to site (to allow passage to and through tortuous locations) but yet have iarge radial force to unblock the vessel and excellent scaffolding so as to be able to hold the atherosclerotic material against the wall, even in bends and in hard calcified lesions. The stent should also allow for further balloon expansion if further lumen enlargement is required at particularlocations.
In U.S. Patent 5,104,404, Pinchasik attempts to address some of the shortcomings of the prior art by te~hing the use of different connectors ~articulation) between the rigid Palmaz stent segments, enabling more flexibility between the rigid parts.
.. " , "
It would be highly desirable, however, to have a stent having few or no longitlldin:~lly rigid parts so that it will be homogeneously flexible along its entire longitudinal axis when delivered on the catheter. Furthermore it would be extremely desirable to eliminzlte the longitudinal shortening of the stent during radial expansion to minimi7P stent misplacement.
Furthermore, in Palmas' stents marketed by Johnson & Johnson, as well as in others, during plastic deformation of the stent (i.e. balloon expansion) the strain is concentrated at small zones. This limits the properties of the m~teri~l that can be used as well as the radial force and the expansion rate. By distributing the strain over large zones, a less thick annealed material can be used to both avoid deterioration of the radial force of the stent when expanded, and to reduce the stent's constricted profile. There are obvious advantages to reduced stent thickness.
According to the prior art method ol manufacturing stents, the material is originally flat. The screen-like m~tP.ri~l is then rolled into a cylinder shape and laser welded or otherwise connected to forrn a tube - - the weld running the length of the longitudinal axis. This is a difficult and expensive manufacturing procedure. It also leads lo a potential lack of uniformity. The present invention, a new method of stent manufacture, as will be explained, results in a more uniformly expandable stent, one not having a weld line forrned after mesh formation.
Patents which relate to the field of stent geometry are as follows: U.S.
Patent Nos.5,354,309; 4,776,337; 5,356,423; 5,383,892; 5,178,618; 5,449,373; and~,104,404.
Summary of the Invention The object of the present invention is to provide a stent which has flexibility sub~n~ y along its lon~it~1~1in~l axis when constrained on a catheter ."" . . .. ..
W 0 98~3546 PCTnBg7/00231 to allow it to easily pass through and along highly curved body vessels and fluid-carrying tubes.
It is further an object of the invention to supply the constricted stent (i.e., before balloon expansion) with a minimum diameter to ease its passage for placement through a minisn~l diameter vascular port as well as to enable it to enter through narrow }umens of constricted body tubes.
It is further an object of the invention to provide a stent geometry which results in a more homogenous distribution of the strain on the stent material, reducing the maximum strain on the stent when expanded so that less material canbe used. Subjecting less material to the same balloon-expanding force can resultin greater radial expansion. This allows both a greater expansion ratio for the stent and smaller stent wall thickness.
It is further an object of this invention to allow a stent geometry and proper material to provide additional stent diameter expansion by elongatinn of the stent material (such aSt~ llm) and not by çll~nging the shape of the stent.
It is further an object of the invention to provide a stent which does not substantially change in length as the stent diameter is expanded during balloon inflation.
A further object of the present invention is to provide a method for fabricating stents and, in particular, the stents disclosed herein.
It is a further object of the invention to supply the stent with a graft material to be a stent graph as well as a stent graft of Y-shape for aortic aneurism.
Brief D~s~ ,tion of the D.~wi ~
Figure 1 is an elevational view of a stent (shown as a cylinder for illustrative purposes) in cylindrical coordinates;
Figure 2 is a parlial section of a stent, showing a pair of radial rings, unconnected in the longitudinal direction (for illustration) and showing a stentbefore expansion, having points or dots on the rings which will rotate 45'' upon WO 98/33S46 PCT~Bg7/00231 expansion due to balloon inflation. (In Figures 2- l 1, the interconnections hetween the adjacent radial rings of the stent are not shown.). A ring of the stent resembles a lock washer an un-hll~ting ring shape;
Figure 3 is a partial section of a stent showing the pair of adjacent radial rings of Figure 2, after expansion of the stent;
Figure 4 is a partial section of a pair of radial rings of a second embodiment of a stent, without longitudinal connection (for ease of illustration) before expansion, having points or dots on the rings which will rotate 90~ upon stent expansion;
Figure 5 is a partial section of another embodiment of a stent showing a pair of radial rings~ before expansion, having points or dots on the rings whichwill rotate 180~ upon expansion;
Figure 6 is a partial section of a pair of radial rings of another embodiment of the stent, again, before expansion, having points or dots on the rings which will rotate 360~ upon expansion;
Figure 7 is a partial section of a pair of radial rings of another embodiment of the stent, both before (on the right side) and after (on the left side) expansion, having two types of dots or points on the rings which will rotate through anglesof 45~ and 90~ respectively, upon expansion;
Figure 8 shows a partial section of a pair of radial rings of another embodiment of the stent, before expansion, in which the radial rings have two types of dots or points on the rings which will rotate through angles of 45~ and180~, respectively, upon expansion;
Figure 9 shows two pairs of radial rings of yet another embodiment of the stent, before expansion, in which adjacent rings are constructed with mirror images of each other;
Figure 10 shows four radial rings in which neighboring rings are offset, i.e., have constructions which differ by an angle of rotation from each other. The "z" and "~3" angles are shown on the axis; the "~" axis, corresponds to the angle "~" illustrated in Figure l;
Figure 11 shows a partial section of four rings of yet another embodiment of a stent, before expansion;
Figure 12 shows a graphical depiction of two types of longitll-lin~l connections between neighboring radial rings of a stent, the right side of the Figure being before stent expansion;.
Figure 13 shows a graphical representation of a section of an expanded stent which has been constructed such that some of the radial segments and some of the longitudinal cormections are deliberately omitted during manufacture;
Figure 14 is a perspective view of a stent according to the present invention with the stent in its constricted form, prior to expansion and wherein the connections between adjacent rings of the stent are straight, Figure 15 is ~ perspective view of the stent of Figure 14 with the stent in its expanded form;
Figure 16 is a perspective view of another embodiment of a stent in which the connections between the adjacent rings of the stent are also curved. The stent is shown in the constricted forrn prior to expansion;
Figure 17 is a perspective view of the stent of Figure 16 in its expanded form;
Figure 18 shows an enlarged partial section of another embodiment of a stent in which the stent joints (between the ~ ce~t rings) are circular, and thestent is in its constricted fi~rrn, prior to the expansion. Individual rings are formed with the circular joints, as we}l;
Figure 19 shows the portions of the stent of Figure 18 in its e~p~n-le(l form. Points A, B, C, D, E, F, G, H, I, J and K have been shown on both Pigs.
18 and 19 (opposed, offset U-shapes) to illustrate relative movement and location, a consequence of stent expansion;
., ~. i ...
WO 98/33546 PCT/IB97tO0231 Figure 20A shows a partial enlarged section of another embodiment of a stent with llnd~ ted (opposed, offset U-shapes) rings, strips or segments separating adjacent rings, ,and alternate rings having simple intersections between adjacent points on the same ring and circular joints between adjacent points.
Figure 20A shows the stent in a constricted form; Figure 20B is a schematic representation of the stent of Fig. 20A in an expanded forrn, Figures 21 an(l 22 show partial sections of a stent with undulated (opposed, offset U-shapes) radial strips or segments as in Figure 20A, forrning the rings, yet with the circular connectors being hollow. The rings are connected by longitudinal segments;
Figure 22 shows another embodiment with undulating rings, longitudinal connectors and simple intersections;
Figure 23 is a side elevational schematic view of a film contact im~ging apparatus for stent manufacture;
Figure 24 is a similar schematic view of a laser scanning system for stent manufacture;
Figure 25 is a schematic representation of a Y-tube stent graft in the open position, according to the present invention;
Figure 26 is a schematic representaion of a Y-tube stent graft in the closed configuration.
Figure 27 is an enlarged partial view of t~e stent of the present invention, in an embodiment where all the rings are in phase; and Figure 28 is an enlarged partial view of the stent of the present invention, in an embodiment where adjacent or paired rings are 180 degrees out of phase with one another. Of course, as will be appreciated from the description of the drawings and of the invention, all angles between 0 degrees and 180 degrees can be used for the lateral offset of the "peaks" and "valleys" of the adjacent rows.
Figure 28 shows that the repetitive "peaks" and "valleys" of adjacent rings are offset by about 150 to 160 degrees.
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CA 02246386 l998-04-l4 wo 98133546 PCT/Is97tOO23 Detailed DescriPtion of 1he Invention The present invention relates to a novel stent construction. The stent geometry allows both longit~l~ins-l flexibility of the stent when the stent is constricted to its initial narrow diameter for threading through the body vessel, and maximum rigidity, after the stent is expanded to its final large diameter, for supporting the body vessel wall. The geometry of the stent is further designed to allow the stent to remain sub~t~nfi~lly the same length before and after expansion and even zero strain on the connection points..
Moreover, as will be described below, the stent geometry allows a substantially homogeneous distribution of strain on the stent material. This allows for less local strain (e.g. on the connection points securing neighboring radial rings of the stent to longitll-lin~l segments and forming the rings themselves), and thus a smaller stent profile is achieved. It aids stent delivery, inside body tubes. Also, the less material used for the stent, the less rejection of the body to the foreign material. This geometry of the stent also allows a further diameter expansion bymaterial stretching such as tantalum which allows up to about 40% elongation.
The stent's further expansion is better achieved by the homogeneous distributionof stress, a result of the new geometry.
Figure l shows a c ylindrical stent with orthogonal cylindrical coordinates (R, fl, Z). Coordinate Z co~ ollds to the }on&itu~lin~l central axis of the stent.
When Z=O, the stent's l<n~itu-lin~l end is described. The stent length, its longitudinal axis, is Z. Radius r refers to the radius of the stent from the longitudinal axis of the stent to the outer circumference of the stent. Radius r, of course, changes with stent dilation during deployment of the balloon or other expansion of the stent radiws by another merh~ni~m (e.g., memory metal). As shown in Figure 147 the stent 30, in its constricted state (i.e. before expansion), is a hollow cylinder, or is tube-like. The hollow cylinder has windings 31 on its surface joined together at points to forrn the radial rings. The stent has longitll~in~l flexibility, wvhen in its constrained diameter, and allows for radial wO 98l33546 PCT/IB97/0023 expansion. As shown in Figure lS, the stent 30, in its expanded state, has the radial rings opened, the windings uncurl from their constricted to their expanded state, providing a larger radius r for the hollow cylinder of the stent construction.
Figure 2 shows adjacent radial rings (1) and (2) of a stent. In the Figure (and in all of Figures 2-11) each ring is shown without the longitudinal connections which are provided between adjacent rings. The longitudinal connections are shown, for example, in Figures 14-16. Radial rings (1) and (2) are each originally7 i.e., before expansion, curved, with the curves of the rings crossing the Z = constam. axis of the ring. ~ach curved ring has dots or points (e.g. dot or point (3~ on ring 1, and dots or points (4), (5) and (6) on ring 2, on its curves During outward expansion of the stent, dots (5) and (6) rotate. During the rotation of the dots, no deformation occurs in the dots. During expansion, dot (5) rotates in a 45'' angle clockwise manner and dot (6) rotates in a 45~ angle counterclockwise manner, thereby resulting in stent geometry shown in Fig. 3.
Figure 3 shows two radial rings 1 and 2 of Figure 2 after m~xim:~l stent diameter expansion. Although the connections on the longitudinal axis are not shown in the Figure, ~he tesulting shape of the connected radial rings, after maximal expansion~ is a cylindrical mesh of rectangular boxes ~sirnilar to screening m~t~.ri~l) A hollow cylinder oi' rectangular boxes is formed. The rectangular mesh can be seen by reference to Figure 15.
As shown in Figures 4, 5 and 6, stents a~e depicted forrned of rings 1 and
2 with dot rotation angles of 90~, 180~, and 360~, respectively, (and by the same principle, any intermediate angle) thereby achieving different levels of radial expansion.
In Figure 7, the angle of rotation of the rotating dots is 45~ clockwise (11) and 90~ counterclockwise (for connecting dot 12).
In Figure 9, it is shown that, in addition to achieving rotation around rotation dots or points at any radial line (Z1, Z2, ...), it is also possible to rotate each ring in the opposite direction of rotation of its neighbor ring, i.e. Iike mirror ~ ~ . . I l W 0 98/33546 PCTnB97100231 images. Dots (14) and (16) will rotate counterclockwise while dots (15) and (17)will rotate clockwise. Again, flexibility of stent design is achieved.
In Figure 10, a stent design is shown (four rings without ring interconnects for ease of illustration), as in Figure 2, but having an angle of rotation or offset between the radial rings along the stent's longitudinal axis Z. Figure 27 shows an embodiment of the invention where adjacent rings have their "peaks" and "valleys"
in phase with one another while Figure 28 shows an alternate embodiment of the invention where the rings are arranged in pairs with each ring of the pair is the mirrow image of the other ring of the pair, i.e., the "peaks" and "valleys" of the rings are 180 degrees out of phase. Of course, according to the present invention, the offset between adjacent of pairs of rings can incrementally vary from a low of 0 degrees, as shown in Figure 27 to a high of 180 degrees, as shown in Figure28.
Figure 11 shows, instead of having close radial loops as in Figure 2 - 10, the present invention can also be practiced with a coil shape on which all rotation dots will be on the line that Z = K x ~.
In Figure 12, ring 20 is circumferentially longer than the distance between two rings Zl and Z2 (distance between adjacent rings), and has shape 21 (left side of Figure 12) after stent expansion, leaving the stent length subst~nti~lly unchanged. Longitudinal connector 22, whose length is equal to the distance between the two rings, does not deform during stent expansion. Connection 24 is a curved shape before stent expansion, and changes to a straight line 25 after stent expansion. The lon~;ihl~lin~l connections can be between two dots (27 and 28) that are not necessarily placed along a line that is parallel to the Z axis.Figure 13 shows that for longitll~lin~l flexibility (important for stent deployment to the site) segments of longitudinal connectors 30 and/or sections of the rings 31, can be selectively omitted for some parts of the stent.
Figures 14 and 16 show two embodiments of the stents, in accordance with the present invention, each in a constricted configuration. As shown, the radial .. , ., . "
rings 33 are connected with longitudinal connectors 35. ~ Figure l 4, the longitudinal connectors are straight (both before and after expansion), while inFigure 16, the longitudinal connectors are curved (before expansion). Figure 15 shows the stent 30 of Figure 14 in an expanded configuration, after inflation by a balloon. Figure 17 (not to scale) similarly depicts the expanded configuration of the stent of Figure 16. As can be seen from the Figures, expansion of the s~ent allows the flexible, constricted configurations to be transformed into a cylinder comprised of substantially rigid rectangular grid geometry. The expanded stent is in the form a hollow tube. Conse~uently, the stent can be threaded through a body vessel in a flexible, constricted state, and subsequently expanded into a subst~nti~lly rigid, expanded state for scaffoldingagainst the body vessel wall.
Figures 18 and 19 show an embodiment of the stent where joints 38 (between adjacent rings and also forrning the rings from straight segments) are circular rather than single connecting dots or points. As shown in the Figures, ring segments 32 (the arrows at the top of the Pigure show the direction of stent expansion) and longitudinal connectors 35 are connected at circle joints 38.
Figure 18 shows the stent in a constricted configuration, prior to expansion, while Figure 19 shows the stent after expansion. Points ~ - K represent connection points at which the radial ring segments 32 and longitufiin~l cormectors 35 meetthe joints 38. COlllpa~ g Pigures 18 and l9; expansion of the stent from a constricted to an expanded configuration causes rotation of the connection points A-K to yield a rectangle-like mesh, in which the corners of the rectangles are occupied by the circular joints. Of course, as discussed, the mesh is in the basic hollow cylinder shape.
Figures 20A and B, 21 and 22 show three embodiments of the stent with n~ te~ or highly curved radially oriented segments 65. In this embodiment, the mdlll~tions are opposed, offset U-shapes. Again, the direction of stent, radial expansion is shown on the Figures. Figures 20A and 20B, as well as 21 show two W O 98/33546 rCT~B97/00231 differing embodiments of circular or extended joints 68 (Figure 21 shows hollow circle joints), while Figure 22 shows a joint 69 which is a point-like intersection of stent ring segments and longitudinal elements. In these embodiments, stent expansion is achieved by rotation of the joints 68 and 69, and by consequent straightening of the nn~ ted or highly curved, radially oriented segments 65.
These embodiments allow excellent radial force and tissue scaffolding with minim~l shortening along the stent's longitudinal axis. They also allow substantially homogeneou, distribution of stress during expansion, with minim~l stress and strain on the joints. Figure 22 shows that every other ring is similar in geometry and thickness to every other ring with adjacent rings having different geometries and material thickness. Of course, the rings of the same geometry andmaterial thickness can either be in phase, with its "peaks" and "valleys" or offset up to about 180 degrees, .IS shown in Figures 27 and 28.
In addition to the improvements provided by the new stent geometry described herein, use oi' a m~teri~l such as tantalum can be particularly advantageous. Elongation of tantalum by applying radial expanding balloon pressure can achieve up l:o a 40% elongation of the stent m:~t~,ri~l. Thus, thiselongation of the stent m~teri~l itself is in addition to the stent radial dilation which can be achieved from expansion of the novel stent by balloon expansion.
As shown in the drawings, the rotation points of the present stents enable large stent expansion, without creating high stress concentration on the connecting points of the stent. This is a significant improvement over both the Palmaz stent and the Pinch~n~ik and Wolff stents of the prior art, in which stress concentration, followed by fatigue and corrosion, at any point, is a potential problem.
Similarly, it is also shown from the descriptions and the Figures that the stent is flexible, longitudinally, when constricted to a small f~ meter, and becomes stiff, only after expansion. This is also an important improvement over the prior art, as the present stent is not composed of ~l~em~ting, rigid and articulated components, joined togeth.er, but rather is integrally constructed as a single flexible WO 98t33546 PCT/IBg7/00231 stent, having a long length, and having the ability to bend, homogeneously, along its longitudinal axis when in its constrained form.
Fabrication of' the stents shown in Figures 1-22 can be accomplished in numerous m~nn~r~. Two new methods and systems for manufacture of the stents are however, shown in Figures 23 and 24.
One current method for fabrication of a patterned etched cylinder is to form a wire mesh from a flat planar surface and then to fuse its two opposite edges to create a cylinder. That method, however, suffers a basic disadvantage in that the presence of t}-e fusing line creates a we~k~ned area along the longitudinal axis of the stent, which is potentially subject to fatigue and breakage. lt would be preferable for the stent to be formed from a more uniform piece of material to avoid this potential problem.
According to the present invention, there is, therefore, provided two novel alternative methods for im~ing the desired pattern i.e., the location of points,lln~ ting connectors, rinK and connecting segments, etc. onto a cylinder, without the need of fusing into a cylinder after forming of the design. Either a film contact imaging method or a laser sc~nning system can be used to accomplish thisobjective.
As shown in Figure 23, a film contact im:~ging method is constructed using an elliptical mirror 100 which reflects ultraviolet light from an ultraviolet light source 110. The ultraviolet light source is located at one focal point of the elliptical mirror 100 and illumin~tes through a slit or narrow aperture 120 (which elimin~tes scattered light) Slit or ap~ e 120 is located at the other focal point of the elliptical mirror to allow for high density power illumination from the ultMviolet source. Rays of ultraviolet light 115 are thus reflected off of elliptical mirror 100 to pass through slit or aperture 120 and onto a moving film 130. Slit120 extends parallel to the Ic)ngitudinal axis of hollow tube or cylinder 140. Film 140 carries the design sought to be provided to the tube or cylinder 140.
",. , ~ , . ..
Film 130 is in contact with hollow cylinder 140. Figure 22 shows a drawing of the photoetching film for the stent production, according to the method of the present invention. Hollow cylinder 140 is material which is fabricated into the stent of the present invention. Film 130 serves as a mask or template, beingtransparent to ultraviolet light in some areas and opaque to ultraviolet in others in the predefined stent pattern. Cylinder 140 is coated with an appropriate material (a photoresist) for a photo-etching process. As ultraviolet light 115 is tr~m~mi~ted onto film 130 through slit 120, film 130 moves past cylinder 140 while the cylinder 140 rotates. Th~ rotation of the cylinder 140 is correlated with the movement of the filnl 130 to appropriately image the pattern on the film around and onto the cylinder 140. As a result, ultraviolet light 115 passing through UV-transparent portions of the film template will strike the cylinder 140 in the desired pattem to photoetch the al~ol~iate configuration onto cylinder 140. An acid treatment is then used to remove the areas which were struck by tne UV light. Ingeneral, the chemical aspects of the system are similar to that used in the manufacture of computer chips i.e., photoresist, m~sking, acid, etc.
It should be pointed out that variations on this design can, of course, be accomplished by those of ordinary skill in the art. For example, in the presenceof a sufficiently high powered light source, usage of an elliptical mirror is not e~enti~l, As shown in Figure 24, a second method which can be used for the fabrication of stents is a laser scanning system. The system consists of a cylinder or tube 160 to be etched, a laser 170, the laser optics 180 (cont~inin~ beam components and modulator), and a dynamic deflector 190 (such as a rotating mirror, a polygon, or any other known s~nnin~ deflector). The system is based upon a well-known flat bed sc~nnin~ system. Cylinder 160 is coated with a photoresist, or material suitable for photoetching. A laser 170 is selected of the applvpliate power and wavelength suitable for stim~ t;ng the photoresist in use.For example, for an ablation method, the laser can be a high powered IR laser , .
diode; for a photoresist sensitive to visible light, the laser can be a laser in the visible range or for a conventional UV photoresist, an Eximer laser or third (orhigher) harmonic generation Nd:YAG/Nd:YLF laser can be used. The laser beam is shaped by an appr~ ;ate optical system, and modulated by direct modulation in the case of an IR laser diode, with AOM (an Acoustic Optical Modulator) in the case of a CW laser in the visible, or by a vibrating mirror in the case of a UV
laser.
The laser beam from laser 170 hits a deflector device 190 which can be a rotating mirror, a polygon mirror, or other known sc~nning device. The beam emerges from the deflector, passing through a scan lens 195 and focussed on the cylinder 160. The cylinder, coated with a photoresist, rotates about its longitudinal axis 200 at a constant angular velocity, while the beam scans back and forth. The modulation of the laser beam allows writing a computer im:~ging file directly onthe cylinder without the need of intermediate media (e.g. film). The laser sc~nning velocity is correlated to the cylinder angular velocity, and is determined by the energy required for exposure of the photoresist.
Figures 25 and 26 relate to use of the present invention as a stent graft.
This is a stent over which a cloth sleeve is positioned to prevent blood from going through the stent wall or for having better support of the vessel wall. As a particular embodiment, the stent graft is in a Y-shape for the treatment of aortic aneurysm, near the aortic birulc~lion. In such cases, simple tube stent grafts tend to migrate downwardly. In the Y-shape of the present invention, however, the stent is supported on the bifulcation and thus it cannot migrate from the site. A
method of percutaneous insertion of this Y-stent graft is shown in the drawing.
As shown in the drawings, the main tube integral with a right and a left tube, thereby fonning the Y-shape stent graft. A first balloon passes from the left tube into the main tube whi]e a second balloon passes into the right tube. During deployment, the right tube moves flexibly to the right. The second step of deployment contemplates the pulling of the entirety of the stent graft so that it is ", . . ~
wo 98/33S46 PCT/IB97l00231 located and fixed to the aortic bifulcaton. Then inflation of balloon No. 1 for the main tube is accomplished. Then balloon No. 2 is inflaated in the right tube.
Then balloon No. 1 is pulled and reinfl~ted followed by a withdrawal of balloons.
Figure 25 shows the Y-shaped tube stent graft in its open or expanded configuration. Balloon No. 1 is shown inflated and located in the main graft tube.
Balloon No. 2 is shown in the right graft tube. Pulling balloon No. 1 and reinflating the same expands the left graft tube.
Having described this invention with regard to specific embodiments, it is to be understood that the description is not meant as a limitation since furthervariations or modifications may be apparcl t or may suggest themselves to those skilled in the art. It is intended that the present application cover such variations and modifications as fall within the scope of the appended claims.
In Figure 7, the angle of rotation of the rotating dots is 45~ clockwise (11) and 90~ counterclockwise (for connecting dot 12).
In Figure 9, it is shown that, in addition to achieving rotation around rotation dots or points at any radial line (Z1, Z2, ...), it is also possible to rotate each ring in the opposite direction of rotation of its neighbor ring, i.e. Iike mirror ~ ~ . . I l W 0 98/33546 PCTnB97100231 images. Dots (14) and (16) will rotate counterclockwise while dots (15) and (17)will rotate clockwise. Again, flexibility of stent design is achieved.
In Figure 10, a stent design is shown (four rings without ring interconnects for ease of illustration), as in Figure 2, but having an angle of rotation or offset between the radial rings along the stent's longitudinal axis Z. Figure 27 shows an embodiment of the invention where adjacent rings have their "peaks" and "valleys"
in phase with one another while Figure 28 shows an alternate embodiment of the invention where the rings are arranged in pairs with each ring of the pair is the mirrow image of the other ring of the pair, i.e., the "peaks" and "valleys" of the rings are 180 degrees out of phase. Of course, according to the present invention, the offset between adjacent of pairs of rings can incrementally vary from a low of 0 degrees, as shown in Figure 27 to a high of 180 degrees, as shown in Figure28.
Figure 11 shows, instead of having close radial loops as in Figure 2 - 10, the present invention can also be practiced with a coil shape on which all rotation dots will be on the line that Z = K x ~.
In Figure 12, ring 20 is circumferentially longer than the distance between two rings Zl and Z2 (distance between adjacent rings), and has shape 21 (left side of Figure 12) after stent expansion, leaving the stent length subst~nti~lly unchanged. Longitudinal connector 22, whose length is equal to the distance between the two rings, does not deform during stent expansion. Connection 24 is a curved shape before stent expansion, and changes to a straight line 25 after stent expansion. The lon~;ihl~lin~l connections can be between two dots (27 and 28) that are not necessarily placed along a line that is parallel to the Z axis.Figure 13 shows that for longitll~lin~l flexibility (important for stent deployment to the site) segments of longitudinal connectors 30 and/or sections of the rings 31, can be selectively omitted for some parts of the stent.
Figures 14 and 16 show two embodiments of the stents, in accordance with the present invention, each in a constricted configuration. As shown, the radial .. , ., . "
rings 33 are connected with longitudinal connectors 35. ~ Figure l 4, the longitudinal connectors are straight (both before and after expansion), while inFigure 16, the longitudinal connectors are curved (before expansion). Figure 15 shows the stent 30 of Figure 14 in an expanded configuration, after inflation by a balloon. Figure 17 (not to scale) similarly depicts the expanded configuration of the stent of Figure 16. As can be seen from the Figures, expansion of the s~ent allows the flexible, constricted configurations to be transformed into a cylinder comprised of substantially rigid rectangular grid geometry. The expanded stent is in the form a hollow tube. Conse~uently, the stent can be threaded through a body vessel in a flexible, constricted state, and subsequently expanded into a subst~nti~lly rigid, expanded state for scaffoldingagainst the body vessel wall.
Figures 18 and 19 show an embodiment of the stent where joints 38 (between adjacent rings and also forrning the rings from straight segments) are circular rather than single connecting dots or points. As shown in the Figures, ring segments 32 (the arrows at the top of the Pigure show the direction of stent expansion) and longitudinal connectors 35 are connected at circle joints 38.
Figure 18 shows the stent in a constricted configuration, prior to expansion, while Figure 19 shows the stent after expansion. Points ~ - K represent connection points at which the radial ring segments 32 and longitufiin~l cormectors 35 meetthe joints 38. COlllpa~ g Pigures 18 and l9; expansion of the stent from a constricted to an expanded configuration causes rotation of the connection points A-K to yield a rectangle-like mesh, in which the corners of the rectangles are occupied by the circular joints. Of course, as discussed, the mesh is in the basic hollow cylinder shape.
Figures 20A and B, 21 and 22 show three embodiments of the stent with n~ te~ or highly curved radially oriented segments 65. In this embodiment, the mdlll~tions are opposed, offset U-shapes. Again, the direction of stent, radial expansion is shown on the Figures. Figures 20A and 20B, as well as 21 show two W O 98/33546 rCT~B97/00231 differing embodiments of circular or extended joints 68 (Figure 21 shows hollow circle joints), while Figure 22 shows a joint 69 which is a point-like intersection of stent ring segments and longitudinal elements. In these embodiments, stent expansion is achieved by rotation of the joints 68 and 69, and by consequent straightening of the nn~ ted or highly curved, radially oriented segments 65.
These embodiments allow excellent radial force and tissue scaffolding with minim~l shortening along the stent's longitudinal axis. They also allow substantially homogeneou, distribution of stress during expansion, with minim~l stress and strain on the joints. Figure 22 shows that every other ring is similar in geometry and thickness to every other ring with adjacent rings having different geometries and material thickness. Of course, the rings of the same geometry andmaterial thickness can either be in phase, with its "peaks" and "valleys" or offset up to about 180 degrees, .IS shown in Figures 27 and 28.
In addition to the improvements provided by the new stent geometry described herein, use oi' a m~teri~l such as tantalum can be particularly advantageous. Elongation of tantalum by applying radial expanding balloon pressure can achieve up l:o a 40% elongation of the stent m:~t~,ri~l. Thus, thiselongation of the stent m~teri~l itself is in addition to the stent radial dilation which can be achieved from expansion of the novel stent by balloon expansion.
As shown in the drawings, the rotation points of the present stents enable large stent expansion, without creating high stress concentration on the connecting points of the stent. This is a significant improvement over both the Palmaz stent and the Pinch~n~ik and Wolff stents of the prior art, in which stress concentration, followed by fatigue and corrosion, at any point, is a potential problem.
Similarly, it is also shown from the descriptions and the Figures that the stent is flexible, longitudinally, when constricted to a small f~ meter, and becomes stiff, only after expansion. This is also an important improvement over the prior art, as the present stent is not composed of ~l~em~ting, rigid and articulated components, joined togeth.er, but rather is integrally constructed as a single flexible WO 98t33546 PCT/IBg7/00231 stent, having a long length, and having the ability to bend, homogeneously, along its longitudinal axis when in its constrained form.
Fabrication of' the stents shown in Figures 1-22 can be accomplished in numerous m~nn~r~. Two new methods and systems for manufacture of the stents are however, shown in Figures 23 and 24.
One current method for fabrication of a patterned etched cylinder is to form a wire mesh from a flat planar surface and then to fuse its two opposite edges to create a cylinder. That method, however, suffers a basic disadvantage in that the presence of t}-e fusing line creates a we~k~ned area along the longitudinal axis of the stent, which is potentially subject to fatigue and breakage. lt would be preferable for the stent to be formed from a more uniform piece of material to avoid this potential problem.
According to the present invention, there is, therefore, provided two novel alternative methods for im~ing the desired pattern i.e., the location of points,lln~ ting connectors, rinK and connecting segments, etc. onto a cylinder, without the need of fusing into a cylinder after forming of the design. Either a film contact imaging method or a laser sc~nning system can be used to accomplish thisobjective.
As shown in Figure 23, a film contact im:~ging method is constructed using an elliptical mirror 100 which reflects ultraviolet light from an ultraviolet light source 110. The ultraviolet light source is located at one focal point of the elliptical mirror 100 and illumin~tes through a slit or narrow aperture 120 (which elimin~tes scattered light) Slit or ap~ e 120 is located at the other focal point of the elliptical mirror to allow for high density power illumination from the ultMviolet source. Rays of ultraviolet light 115 are thus reflected off of elliptical mirror 100 to pass through slit or aperture 120 and onto a moving film 130. Slit120 extends parallel to the Ic)ngitudinal axis of hollow tube or cylinder 140. Film 140 carries the design sought to be provided to the tube or cylinder 140.
",. , ~ , . ..
Film 130 is in contact with hollow cylinder 140. Figure 22 shows a drawing of the photoetching film for the stent production, according to the method of the present invention. Hollow cylinder 140 is material which is fabricated into the stent of the present invention. Film 130 serves as a mask or template, beingtransparent to ultraviolet light in some areas and opaque to ultraviolet in others in the predefined stent pattern. Cylinder 140 is coated with an appropriate material (a photoresist) for a photo-etching process. As ultraviolet light 115 is tr~m~mi~ted onto film 130 through slit 120, film 130 moves past cylinder 140 while the cylinder 140 rotates. Th~ rotation of the cylinder 140 is correlated with the movement of the filnl 130 to appropriately image the pattern on the film around and onto the cylinder 140. As a result, ultraviolet light 115 passing through UV-transparent portions of the film template will strike the cylinder 140 in the desired pattem to photoetch the al~ol~iate configuration onto cylinder 140. An acid treatment is then used to remove the areas which were struck by tne UV light. Ingeneral, the chemical aspects of the system are similar to that used in the manufacture of computer chips i.e., photoresist, m~sking, acid, etc.
It should be pointed out that variations on this design can, of course, be accomplished by those of ordinary skill in the art. For example, in the presenceof a sufficiently high powered light source, usage of an elliptical mirror is not e~enti~l, As shown in Figure 24, a second method which can be used for the fabrication of stents is a laser scanning system. The system consists of a cylinder or tube 160 to be etched, a laser 170, the laser optics 180 (cont~inin~ beam components and modulator), and a dynamic deflector 190 (such as a rotating mirror, a polygon, or any other known s~nnin~ deflector). The system is based upon a well-known flat bed sc~nnin~ system. Cylinder 160 is coated with a photoresist, or material suitable for photoetching. A laser 170 is selected of the applvpliate power and wavelength suitable for stim~ t;ng the photoresist in use.For example, for an ablation method, the laser can be a high powered IR laser , .
diode; for a photoresist sensitive to visible light, the laser can be a laser in the visible range or for a conventional UV photoresist, an Eximer laser or third (orhigher) harmonic generation Nd:YAG/Nd:YLF laser can be used. The laser beam is shaped by an appr~ ;ate optical system, and modulated by direct modulation in the case of an IR laser diode, with AOM (an Acoustic Optical Modulator) in the case of a CW laser in the visible, or by a vibrating mirror in the case of a UV
laser.
The laser beam from laser 170 hits a deflector device 190 which can be a rotating mirror, a polygon mirror, or other known sc~nning device. The beam emerges from the deflector, passing through a scan lens 195 and focussed on the cylinder 160. The cylinder, coated with a photoresist, rotates about its longitudinal axis 200 at a constant angular velocity, while the beam scans back and forth. The modulation of the laser beam allows writing a computer im:~ging file directly onthe cylinder without the need of intermediate media (e.g. film). The laser sc~nning velocity is correlated to the cylinder angular velocity, and is determined by the energy required for exposure of the photoresist.
Figures 25 and 26 relate to use of the present invention as a stent graft.
This is a stent over which a cloth sleeve is positioned to prevent blood from going through the stent wall or for having better support of the vessel wall. As a particular embodiment, the stent graft is in a Y-shape for the treatment of aortic aneurysm, near the aortic birulc~lion. In such cases, simple tube stent grafts tend to migrate downwardly. In the Y-shape of the present invention, however, the stent is supported on the bifulcation and thus it cannot migrate from the site. A
method of percutaneous insertion of this Y-stent graft is shown in the drawing.
As shown in the drawings, the main tube integral with a right and a left tube, thereby fonning the Y-shape stent graft. A first balloon passes from the left tube into the main tube whi]e a second balloon passes into the right tube. During deployment, the right tube moves flexibly to the right. The second step of deployment contemplates the pulling of the entirety of the stent graft so that it is ", . . ~
wo 98/33S46 PCT/IB97l00231 located and fixed to the aortic bifulcaton. Then inflation of balloon No. 1 for the main tube is accomplished. Then balloon No. 2 is inflaated in the right tube.
Then balloon No. 1 is pulled and reinfl~ted followed by a withdrawal of balloons.
Figure 25 shows the Y-shaped tube stent graft in its open or expanded configuration. Balloon No. 1 is shown inflated and located in the main graft tube.
Balloon No. 2 is shown in the right graft tube. Pulling balloon No. 1 and reinflating the same expands the left graft tube.
Having described this invention with regard to specific embodiments, it is to be understood that the description is not meant as a limitation since furthervariations or modifications may be apparcl t or may suggest themselves to those skilled in the art. It is intended that the present application cover such variations and modifications as fall within the scope of the appended claims.
Claims (31)
1. A medical stent, comprising:
at least two radial rings, each of said radial rings having windings, each of said rings having both a constricted state and an expanded state corresponding to the constricted and expanded state of said windings of said stent, said constricted state being a state of said rings in which said windings are curled in shape, said expanded state being a state of said rings in which said windings are uncurled in shape such that each of said rings becomes substantially circular and of greaterdiameter than said ring in said constricted state; and, longitudinal connectors, said longitudinal connectors connecting said radial rings to form said stent in a cylindrical shape, said constricted state of said stent allowing delivery of said stent on a catheter into a patient, and said expanded state of said stent causing said rings to rest against the walls of a body vessel intowhich said stent is placed, said rings being selectively expandable from said constricted state to said expanded state, said stent being flexible along substantially its entire longitudinal axis when said stent is in said constricted state, said stent being substantially rigid when said stent is expanded to said expanded state, and said stent being substantially the same length independent said of whether said rings or said stent are in said constricted or said expanded states.
at least two radial rings, each of said radial rings having windings, each of said rings having both a constricted state and an expanded state corresponding to the constricted and expanded state of said windings of said stent, said constricted state being a state of said rings in which said windings are curled in shape, said expanded state being a state of said rings in which said windings are uncurled in shape such that each of said rings becomes substantially circular and of greaterdiameter than said ring in said constricted state; and, longitudinal connectors, said longitudinal connectors connecting said radial rings to form said stent in a cylindrical shape, said constricted state of said stent allowing delivery of said stent on a catheter into a patient, and said expanded state of said stent causing said rings to rest against the walls of a body vessel intowhich said stent is placed, said rings being selectively expandable from said constricted state to said expanded state, said stent being flexible along substantially its entire longitudinal axis when said stent is in said constricted state, said stent being substantially rigid when said stent is expanded to said expanded state, and said stent being substantially the same length independent said of whether said rings or said stent are in said constricted or said expanded states.
2. A medical stent as claimed in Claim 1 wherein said stent is expandable by a balloon catheter.
3. A medical stent as claimed in Claim 1, wherein said rings have points on said windings, said points rotating forty-five (45) degrees upon expansion of said rings from said constricted state to said expanded state.
4. A medical stent as claimed in Claim 1, wherein said rings have points on said windings, said points rotating ninety (90) degrees upon expansion of said rings from said constricted state to said expanded state.
5. A medical stent as claimed in Claim 1, wherein said rings have points on said windings, said points rotating one hundred and eighty (180) degrees upon expansion of said rings from said constricted state to said expanded state.
6. A medical stent as claimed in Claim 1, wherein said rings have points on said windings, said points rotating three hundred and sixty (360) degrees upon expansion of said rings from said constricted state to said expanded state.
7. A medical stent as claimed in Claim 1, wherein said rings have at least two points on said windings, at least one of said points rotating forty-five (45) degrees in a first direction and at least one of said points on said same ring rotating ninety (90) degrees in a direction opposite to said first direction.
8. A medical stent as claimed in Claim 1, wherein at least two of adjacent rings are paired, the winding of a said second ring of said pair being the mirror image of the winding of said first ring of said pair.
9. A medical stent as claimed in Claim 1, wherein said longitudinal connectors are substantially straight when said stent is in said constricted state.
10. A medical stent as claimed in Claim 1, wherein said longitudinal connectors are substantially straight both when said stent is in said constricted state and when said stent is in said expanded state.
11. A medical stent as claimed in Claim 1, wherein said longitudinal connectors are curved when said stent is in said constricted state, and become straight when said stent expands into said expanded state.
12. A medical stent as claimed in Claim 1. wherein at least one of said longitudinal connectors between adjacent of said rings is omitted.
13. A medical stent as claimed in Claim 1, wherein at least one segment of at least one of said rings is omitted.
14. A medical stent as claimed in Claim 1, wherein the shape of said stent in said expanded state is a hollow cylinder of substantially rigid rectangular mesh.
15. A medical stent as claimed in Claim 1, further comprising rotatable joints on at least one of said rings.
16. A medical stent as claimed in Claim 15, wherein said rotatable joints are circular.
17. A medical stent as claimed in Claim 15, wherein said rotatable joints are points of connection between said rings and said longitudinal connectors..
18. A medical stent as claimed in Claim 15, wherein said rotatable joints are circular and hollow.
19. A medical stent as claimed in Claim 1, wherein at least some of either said rings or said longitudinal connectors comprise undulating segments.
20. A medical stent as claimed in Claim 19 wherein said undulating segments are opposed and offset U-shapes.
21. A medical stent as claimed in Claim 15 wherein said adjacent of said rings are paired, said rings comprise peaks and valleys and and said peaks and valleys are offset with respect to one another by about 0 to 180 degrees.
22. A medical stent as claimed in Claim 21 wherein said undulating segments are opposed and offset U-shapes.
23. A medical stent as claimed in Claim 1, in which at least part of said stent is comprised of tantalum.
24. A medical balloon-expandable stent as claimed in Claim 3, wherein said windings also will rotate one hundred and eighty (180) degrees opposite to said rotation of forty-five (45) degrees upon expansion of said stent from said constricted state to said expanded state.
25. A medical stent as claimed in Claim 1, wherein said expanded state is a hollow cylinder of substantially rigid rectangular mesh, the connections between said rings and said longitudinal connectors being circular and rotatable joints at the corners of the rectangles of said mesh.
26. A medical stent as claimed in Claim 1, wherein the radial expansion of said rings is enhanced, at least in part, by strain of said stent material.
27. A medical stent as claimed in Claim 1 wherein said rings are expanded by both uncurling of said windings and strain of said stent material.
28. A medical stent as claimed in Claim 27 wherein said stent is made, at least in part, from tantalum.
29. A method of manufacturing a medical stent comprising the steps of:
(a) first forming a cylinder;
(b) relative rotation of said cylinder adjacent to a moving film having a pattern to be provided to said cylinder;
(c) directing concentrated light through said said film and toward said cylinder;
(d) exposing to light those portions of said cylinder not blocked by said pattern of said film, to form masked portions of said cylinder;
and (e) removing the material of said cylinder not masked.
(a) first forming a cylinder;
(b) relative rotation of said cylinder adjacent to a moving film having a pattern to be provided to said cylinder;
(c) directing concentrated light through said said film and toward said cylinder;
(d) exposing to light those portions of said cylinder not blocked by said pattern of said film, to form masked portions of said cylinder;
and (e) removing the material of said cylinder not masked.
30. A method of manufacturing a medical stent comprising the steps of:
(a) first forming a cylinder;
(b) creating a pattern to be provided to said cylinder;
(c) relative rotating of said cylinder about its longitudinal axis in the vicinity of a laser scanning along the cylinder's longitudinal axis;
and (d) proving said pattern to said cylinder by coordination of said scanning laser and relative rotation of said cylinder.
(a) first forming a cylinder;
(b) creating a pattern to be provided to said cylinder;
(c) relative rotating of said cylinder about its longitudinal axis in the vicinity of a laser scanning along the cylinder's longitudinal axis;
and (d) proving said pattern to said cylinder by coordination of said scanning laser and relative rotation of said cylinder.
31. A medical stent as claimed in claim 1 comprising a Y-shaped stent graft.
Priority Applications (12)
Application Number | Priority Date | Filing Date | Title |
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US08/543,337 US5776161A (en) | 1995-10-16 | 1995-10-16 | Medical stents, apparatus and method for making same |
EP06000217A EP1649830A1 (en) | 1995-10-16 | 1997-02-03 | Medical stents |
DE29723905U DE29723905U1 (en) | 1995-10-16 | 1997-02-03 | Medical stents and device for making the same |
EP97903559A EP0909198B1 (en) | 1995-10-16 | 1997-02-03 | Medical stents |
CA002246386A CA2246386A1 (en) | 1995-10-16 | 1997-02-03 | Medical stents, apparatus and method for making same |
PCT/IB1997/000231 WO1998033546A1 (en) | 1995-10-16 | 1997-02-03 | Medical stents, apparatus and method for making same |
JP09519200A JP2001501488A (en) | 1995-10-16 | 1997-02-03 | Medical stent, manufacturing apparatus and manufacturing method thereof |
AU18081/97A AU1808197A (en) | 1995-10-16 | 1997-02-03 | Medical stents, apparatus and method for making same |
DE69736228T DE69736228T2 (en) | 1995-10-16 | 1997-02-03 | MEDICAL STENTS |
US08/942,648 US6090127A (en) | 1995-10-16 | 1997-10-02 | Medical stents, apparatus and method for making same |
US09/533,879 US6428570B1 (en) | 1995-10-16 | 2000-03-22 | Medical stents, apparatus and method for making same |
US10/192,072 US6641609B2 (en) | 1995-10-16 | 2002-07-09 | Medical stents, apparatus and method for making same |
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
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US08/543,337 US5776161A (en) | 1995-10-16 | 1995-10-16 | Medical stents, apparatus and method for making same |
CA002246386A CA2246386A1 (en) | 1995-10-16 | 1997-02-03 | Medical stents, apparatus and method for making same |
PCT/IB1997/000231 WO1998033546A1 (en) | 1995-10-16 | 1997-02-03 | Medical stents, apparatus and method for making same |
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CA2246386A1 true CA2246386A1 (en) | 1998-08-06 |
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CA002246386A Abandoned CA2246386A1 (en) | 1995-10-16 | 1997-02-03 | Medical stents, apparatus and method for making same |
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EP (2) | EP1649830A1 (en) |
JP (1) | JP2001501488A (en) |
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CA (1) | CA2246386A1 (en) |
DE (2) | DE69736228T2 (en) |
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Families Citing this family (492)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6039749A (en) | 1994-02-10 | 2000-03-21 | Endovascular Systems, Inc. | Method and apparatus for deploying non-circular stents and graftstent complexes |
DE4424242A1 (en) * | 1994-07-09 | 1996-01-11 | Ernst Peter Prof Dr M Strecker | Endoprosthesis implantable percutaneously in a patient's body |
US20020156523A1 (en) * | 1994-08-31 | 2002-10-24 | Lilip Lau | Exterior supported self-expanding stent-graft |
DE69622231T2 (en) * | 1995-03-01 | 2002-12-05 | Scimed Life Systems Inc | LENGTHFLEXIBLE AND EXPANDABLE STENT |
US6896696B2 (en) | 1998-11-20 | 2005-05-24 | Scimed Life Systems, Inc. | Flexible and expandable stent |
US7204848B1 (en) * | 1995-03-01 | 2007-04-17 | Boston Scientific Scimed, Inc. | Longitudinally flexible expandable stent |
US6451047B2 (en) | 1995-03-10 | 2002-09-17 | Impra, Inc. | Encapsulated intraluminal stent-graft and methods of making same |
US6579314B1 (en) * | 1995-03-10 | 2003-06-17 | C.R. Bard, Inc. | Covered stent with encapsulated ends |
US6264684B1 (en) | 1995-03-10 | 2001-07-24 | Impra, Inc., A Subsidiary Of C.R. Bard, Inc. | Helically supported graft |
US6602281B1 (en) * | 1995-06-05 | 2003-08-05 | Avantec Vascular Corporation | Radially expansible vessel scaffold having beams and expansion joints |
RU2157146C2 (en) * | 1995-06-13 | 2000-10-10 | ВИЛЬЯМ КУК Европа, A/S | Device for performing implantation in blood vessels and hollow organs |
US6287336B1 (en) | 1995-10-16 | 2001-09-11 | Medtronic, Inc. | Variable flexibility stent |
US5776161A (en) | 1995-10-16 | 1998-07-07 | Instent, Inc. | Medical stents, apparatus and method for making same |
US6991614B2 (en) | 1995-11-07 | 2006-01-31 | Boston Scientific Scimed, Inc. | Ureteral stent for improved patient comfort |
US6042605A (en) * | 1995-12-14 | 2000-03-28 | Gore Enterprose Holdings, Inc. | Kink resistant stent-graft |
US6203569B1 (en) * | 1996-01-04 | 2001-03-20 | Bandula Wijay | Flexible stent |
US20040193248A1 (en) * | 1996-01-26 | 2004-09-30 | Gray Larry B. | Axially flexible stent |
US6258116B1 (en) | 1996-01-26 | 2001-07-10 | Cordis Corporation | Bifurcated axially flexible stent |
US6436104B2 (en) * | 1996-01-26 | 2002-08-20 | Cordis Corporation | Bifurcated axially flexible stent |
WO1997027959A1 (en) | 1996-01-30 | 1997-08-07 | Medtronic, Inc. | Articles for and methods of making stents |
CA2192520A1 (en) * | 1996-03-05 | 1997-09-05 | Ian M. Penn | Expandable stent and method for delivery of same |
EP1477133B9 (en) * | 1996-03-05 | 2007-11-21 | Evysio Medical Devices Ulc | Expandable stent |
US6796997B1 (en) | 1996-03-05 | 2004-09-28 | Evysio Medical Devices Ulc | Expandable stent |
NZ331269A (en) * | 1996-04-10 | 2000-01-28 | Advanced Cardiovascular System | Expandable stent, its structural strength varying along its length |
US6039756A (en) * | 1996-04-26 | 2000-03-21 | Jang; G. David | Intravascular stent |
JP4636634B2 (en) | 1996-04-26 | 2011-02-23 | ボストン サイエンティフィック サイムド,インコーポレイテッド | Intravascular stent |
US20040106985A1 (en) | 1996-04-26 | 2004-06-03 | Jang G. David | Intravascular stent |
US6241760B1 (en) | 1996-04-26 | 2001-06-05 | G. David Jang | Intravascular stent |
US5922021A (en) * | 1996-04-26 | 1999-07-13 | Jang; G. David | Intravascular stent |
US6235053B1 (en) | 1998-02-02 | 2001-05-22 | G. David Jang | Tubular stent consists of chevron-shape expansion struts and contralaterally attached diagonal connectors |
US5807404A (en) * | 1996-09-19 | 1998-09-15 | Medinol Ltd. | Stent with variable features to optimize support and method of making such stent |
US20060173531A1 (en) * | 1996-09-19 | 2006-08-03 | Jacob Richter | Stent with variable features to optimize support and method of making such stent |
US6432127B1 (en) | 1996-10-11 | 2002-08-13 | Transvascular, Inc. | Devices for forming and/or maintaining connections between adjacent anatomical conduits |
US8211167B2 (en) | 1999-12-06 | 2012-07-03 | Boston Scientific Scimed, Inc. | Method of using a catheter with attached flexible side sheath |
US6599316B2 (en) | 1996-11-04 | 2003-07-29 | Advanced Stent Technologies, Inc. | Extendible stent apparatus |
US6692483B2 (en) | 1996-11-04 | 2004-02-17 | Advanced Stent Technologies, Inc. | Catheter with attached flexible side sheath |
US7591846B2 (en) | 1996-11-04 | 2009-09-22 | Boston Scientific Scimed, Inc. | Methods for deploying stents in bifurcations |
US6835203B1 (en) | 1996-11-04 | 2004-12-28 | Advanced Stent Technologies, Inc. | Extendible stent apparatus |
US6325826B1 (en) * | 1998-01-14 | 2001-12-04 | Advanced Stent Technologies, Inc. | Extendible stent apparatus |
WO1998020810A1 (en) * | 1996-11-12 | 1998-05-22 | Medtronic, Inc. | Flexible, radially expansible luminal prostheses |
US6027527A (en) * | 1996-12-06 | 2000-02-22 | Piolax Inc. | 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 |
US7959664B2 (en) * | 1996-12-26 | 2011-06-14 | Medinol, Ltd. | Flat process of drug coating for stents |
US5906759A (en) * | 1996-12-26 | 1999-05-25 | Medinol Ltd. | Stent forming apparatus with stent deforming blades |
US20040267350A1 (en) * | 2002-10-30 | 2004-12-30 | Roubin Gary S. | Non-foreshortening intraluminal prosthesis |
US5827321A (en) * | 1997-02-07 | 1998-10-27 | Cornerstone Devices, Inc. | Non-Foreshortening intraluminal prosthesis |
DE29702671U1 (en) * | 1997-02-17 | 1997-04-10 | Jomed Implantate Gmbh | Stent |
US6033433A (en) † | 1997-04-25 | 2000-03-07 | Scimed Life Systems, Inc. | Stent configurations including spirals |
IT1292295B1 (en) * | 1997-04-29 | 1999-01-29 | Sorin Biomedica Cardio Spa | ANGIOPLASTIC STENT |
US6451049B2 (en) | 1998-04-29 | 2002-09-17 | Sorin Biomedica Cardio, S.P.A. | Stents for angioplasty |
US5855597A (en) * | 1997-05-07 | 1999-01-05 | Iowa-India Investments Co. Limited | Stent valve and stent graft for percutaneous surgery |
EP0884029B1 (en) | 1997-06-13 | 2004-12-22 | Gary J. Becker | Expandable intraluminal endoprosthesis |
US6635080B1 (en) * | 1997-06-19 | 2003-10-21 | Vascutek Limited | Prosthesis for repair of body passages |
ES2214600T3 (en) | 1997-06-30 | 2004-09-16 | Medex Holding Gmbh | INTRALUMINAL IMPLANT. |
KR19990010304A (en) * | 1997-07-16 | 1999-02-18 | 장양수 | Blood vessel stent |
US6070589A (en) | 1997-08-01 | 2000-06-06 | Teramed, Inc. | Methods for deploying bypass graft stents |
ES2290995T3 (en) | 1997-09-24 | 2008-02-16 | Med Institute, Inc. | RADIALLY EXPANDABLE ENDOPROTESIS. |
US5948016A (en) * | 1997-09-25 | 1999-09-07 | Jang; G. David | Intravascular stent with non-parallel slots |
US6013091A (en) * | 1997-10-09 | 2000-01-11 | Scimed Life Systems, Inc. | Stent configurations |
US6309414B1 (en) * | 1997-11-04 | 2001-10-30 | Sorin Biomedica Cardio S.P.A. | Angioplasty stents |
US6330884B1 (en) | 1997-11-14 | 2001-12-18 | Transvascular, Inc. | Deformable scaffolding multicellular stent |
US6190406B1 (en) * | 1998-01-09 | 2001-02-20 | Nitinal Development Corporation | Intravascular stent having tapered struts |
US6533807B2 (en) * | 1998-02-05 | 2003-03-18 | Medtronic, Inc. | Radially-expandable stent and delivery system |
WO1999040876A2 (en) * | 1998-02-17 | 1999-08-19 | Jang G David | Tubular stent consists of chevron-shape expansion struts and ipsilaterally attached m-frame connectors |
US5931866A (en) * | 1998-02-24 | 1999-08-03 | Frantzen; John J. | Radially expandable stent featuring accordion stops |
DK174814B1 (en) * | 1998-02-25 | 2003-12-01 | Cook William Europ | stent device |
ATE471132T1 (en) * | 1998-03-04 | 2010-07-15 | Boston Scient Ltd | STENT WITH IMPROVED CELL CONFIGURATION |
US5935162A (en) * | 1998-03-16 | 1999-08-10 | Medtronic, Inc. | Wire-tubular hybrid stent |
US6129756A (en) | 1998-03-16 | 2000-10-10 | Teramed, Inc. | Biluminal endovascular graft system |
US6290731B1 (en) | 1998-03-30 | 2001-09-18 | Cordis Corporation | Aortic graft having a precursor gasket for repairing an abdominal aortic aneurysm |
US6626938B1 (en) | 2000-11-16 | 2003-09-30 | Cordis Corporation | Stent graft having a pleated graft member |
WO1999066863A2 (en) * | 1998-06-24 | 1999-12-29 | Sulzer Carbomedics Inc. | Altering heart valve leaflet attachment geometry to influence the location and magnitude of maximum loaded stress on the leaflet |
US6261319B1 (en) | 1998-07-08 | 2001-07-17 | Scimed Life Systems, Inc. | Stent |
US6656218B1 (en) | 1998-07-24 | 2003-12-02 | Micrus Corporation | Intravascular flow modifier and reinforcement device |
US5911754A (en) * | 1998-07-24 | 1999-06-15 | Uni-Cath Inc. | Flexible stent with effective strut and connector patterns |
US6461380B1 (en) * | 1998-07-28 | 2002-10-08 | Advanced Cardiovascular Systems, Inc. | Stent configuration |
CN1183881C (en) * | 1998-07-31 | 2005-01-12 | 诺维公司 | Small vessel expandable stent and method for prodn. of same |
US6500149B2 (en) | 1998-08-31 | 2002-12-31 | Deepak Gandhi | Apparatus for deployment of micro-coil using a catheter |
DE19840645A1 (en) | 1998-09-05 | 2000-03-09 | Jomed Implantate Gmbh | Stent |
US20020019660A1 (en) * | 1998-09-05 | 2002-02-14 | Marc Gianotti | Methods and apparatus for a curved stent |
US6682554B2 (en) | 1998-09-05 | 2004-01-27 | Jomed Gmbh | Methods and apparatus for a stent having an expandable web structure |
US7815763B2 (en) * | 2001-09-28 | 2010-10-19 | Abbott Laboratories Vascular Enterprises Limited | Porous membranes for medical implants and methods of manufacture |
US6755856B2 (en) | 1998-09-05 | 2004-06-29 | Abbott Laboratories Vascular Enterprises Limited | Methods and apparatus for stenting comprising enhanced embolic protection, coupled with improved protection against restenosis and thrombus formation |
US7887578B2 (en) | 1998-09-05 | 2011-02-15 | Abbott Laboratories Vascular Enterprises Limited | Stent having an expandable web structure |
US6193744B1 (en) * | 1998-09-10 | 2001-02-27 | Scimed Life Systems, Inc. | Stent configurations |
US6071307A (en) * | 1998-09-30 | 2000-06-06 | Baxter International Inc. | Endoluminal grafts having continuously curvilinear wireforms |
US6273909B1 (en) * | 1998-10-05 | 2001-08-14 | Teramed Inc. | Endovascular graft system |
US6494879B2 (en) | 1998-10-15 | 2002-12-17 | Scimed Life Systems, Inc. | Treating urinary retention |
US6042597A (en) | 1998-10-23 | 2000-03-28 | Scimed Life Systems, Inc. | Helical stent design |
US6214036B1 (en) * | 1998-11-09 | 2001-04-10 | Cordis Corporation | Stent which is easily recaptured and repositioned within the body |
US6336937B1 (en) * | 1998-12-09 | 2002-01-08 | Gore Enterprise Holdings, Inc. | Multi-stage expandable stent-graft |
US6743252B1 (en) | 1998-12-18 | 2004-06-01 | Cook Incorporated | Cannula stent |
US7655030B2 (en) | 2003-07-18 | 2010-02-02 | Boston Scientific Scimed, Inc. | Catheter balloon systems and methods |
CA2358453A1 (en) * | 1999-01-22 | 2000-07-27 | Khalid Al-Saadon | Expandable endovascular medical tubular stent |
US6096072A (en) * | 1999-01-26 | 2000-08-01 | Uni-Cath Inc. | Self-exchange stent with effective supporting ability |
US6398803B1 (en) | 1999-02-02 | 2002-06-04 | Impra, Inc., A Subsidiary Of C.R. Bard, Inc. | Partial encapsulation of stents |
US6332892B1 (en) | 1999-03-02 | 2001-12-25 | Scimed Life Systems, Inc. | Medical device with one or more helical coils |
US6325825B1 (en) * | 1999-04-08 | 2001-12-04 | Cordis Corporation | Stent with variable wall thickness |
US6730116B1 (en) * | 1999-04-16 | 2004-05-04 | Medtronic, Inc. | Medical device for intraluminal endovascular stenting |
US6273911B1 (en) | 1999-04-22 | 2001-08-14 | Advanced Cardiovascular Systems, Inc. | Variable strength stent |
US6245101B1 (en) | 1999-05-03 | 2001-06-12 | William J. Drasler | Intravascular hinge stent |
US8016873B1 (en) | 1999-05-03 | 2011-09-13 | Drasler William J | Intravascular hinge stent |
US6540774B1 (en) | 1999-08-31 | 2003-04-01 | Advanced Cardiovascular Systems, Inc. | Stent design with end rings having enhanced strength and radiopacity |
US6293968B1 (en) | 1999-09-02 | 2001-09-25 | Syde A. Taheri | Inflatable intraluminal vascular stent |
US6302907B1 (en) * | 1999-10-05 | 2001-10-16 | Scimed Life Systems, Inc. | Flexible endoluminal stent and process of manufacture |
US6331189B1 (en) | 1999-10-18 | 2001-12-18 | Medtronic, Inc. | Flexible medical stent |
DE19952295A1 (en) * | 1999-10-29 | 2001-05-23 | Angiomed Ag | Method of making a stent |
US6733513B2 (en) | 1999-11-04 | 2004-05-11 | Advanced Bioprosthetic Surfaces, Ltd. | Balloon catheter having metal balloon and method of making same |
US7195641B2 (en) | 1999-11-19 | 2007-03-27 | Advanced Bio Prosthetic Surfaces, Ltd. | Valvular prostheses having metal or pseudometallic construction and methods of manufacture |
US6849085B2 (en) | 1999-11-19 | 2005-02-01 | Advanced Bio Prosthetic Surfaces, Ltd. | Self-supporting laminated films, structural materials and medical devices manufactured therefrom and method of making same |
US7235092B2 (en) * | 1999-11-19 | 2007-06-26 | Advanced Bio Prosthetic Surfaces, Ltd. | Guidewires and thin film catheter-sheaths and method of making same |
US8458879B2 (en) * | 2001-07-03 | 2013-06-11 | Advanced Bio Prosthetic Surfaces, Ltd., A Wholly Owned Subsidiary Of Palmaz Scientific, Inc. | Method of fabricating an implantable medical device |
US6936066B2 (en) * | 1999-11-19 | 2005-08-30 | Advanced Bio Prosthetic Surfaces, Ltd. | Complaint implantable medical devices and methods of making same |
US7300457B2 (en) | 1999-11-19 | 2007-11-27 | Advanced Bio Prosthetic Surfaces, Ltd. | Self-supporting metallic implantable grafts, compliant implantable medical devices and methods of making same |
US7736687B2 (en) | 2006-01-31 | 2010-06-15 | Advance Bio Prosthetic Surfaces, Ltd. | Methods of making medical devices |
US10172730B2 (en) * | 1999-11-19 | 2019-01-08 | Vactronix Scientific, Llc | Stents with metallic covers and methods of making same |
US6379383B1 (en) | 1999-11-19 | 2002-04-30 | Advanced Bio Prosthetic Surfaces, Ltd. | Endoluminal device exhibiting improved endothelialization and method of manufacture thereof |
US6537310B1 (en) | 1999-11-19 | 2003-03-25 | Advanced Bio Prosthetic Surfaces, Ltd. | Endoluminal implantable devices and method of making same |
US6280466B1 (en) | 1999-12-03 | 2001-08-28 | Teramed Inc. | Endovascular graft system |
US7044980B2 (en) * | 2000-02-03 | 2006-05-16 | Boston Scientific Scimed, Inc. | Facilitating drainage |
EP1132058A1 (en) | 2000-03-06 | 2001-09-12 | Advanced Laser Applications Holding S.A. | Intravascular prothesis |
US6695865B2 (en) | 2000-03-20 | 2004-02-24 | Advanced Bio Prosthetic Surfaces, Ltd. | Embolic protection device |
US6616689B1 (en) | 2000-05-03 | 2003-09-09 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US6602282B1 (en) * | 2000-05-04 | 2003-08-05 | Avantec Vascular Corporation | Flexible stent structure |
US9566148B2 (en) | 2000-05-12 | 2017-02-14 | Vactronix Scientific, Inc. | Self-supporting laminated films, structural materials and medical devices manufactured therefrom and methods of making same |
ATE519454T1 (en) | 2000-05-22 | 2011-08-15 | Orbusneich Medical Inc | SELF-EXPANDABLE STENT |
US6652579B1 (en) | 2000-06-22 | 2003-11-25 | Advanced Cardiovascular Systems, Inc. | Radiopaque stent |
US6805704B1 (en) * | 2000-06-26 | 2004-10-19 | C. R. Bard, Inc. | Intraluminal stents |
US8070792B2 (en) | 2000-09-22 | 2011-12-06 | Boston Scientific Scimed, Inc. | Stent |
US7766956B2 (en) | 2000-09-22 | 2010-08-03 | Boston Scientific Scimed, Inc. | Intravascular stent and assembly |
US20020116049A1 (en) * | 2000-09-22 | 2002-08-22 | Scimed Life Systems, Inc. | Stent |
US6695833B1 (en) * | 2000-09-27 | 2004-02-24 | Nellix, Inc. | Vascular stent-graft apparatus and forming method |
DE10050971A1 (en) * | 2000-10-10 | 2002-04-11 | Biotronik Mess & Therapieg | stent |
US6485508B1 (en) | 2000-10-13 | 2002-11-26 | Mcguinness Colm P. | Low profile stent |
WO2002038080A2 (en) * | 2000-11-07 | 2002-05-16 | Advanced Bio Prosthetic Surfaces, Ltd. | Endoluminal stent, self-fupporting endoluminal graft and methods of making same |
US6929660B1 (en) | 2000-12-22 | 2005-08-16 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US20040073294A1 (en) | 2002-09-20 | 2004-04-15 | Conor Medsystems, Inc. | Method and apparatus for loading a beneficial agent into an expandable medical device |
US7266687B2 (en) * | 2001-02-16 | 2007-09-04 | Motorola, Inc. | Method and apparatus for storing and distributing encryption keys |
US6942689B2 (en) * | 2001-03-01 | 2005-09-13 | Cordis Corporation | Flexible stent |
US6790227B2 (en) * | 2001-03-01 | 2004-09-14 | Cordis Corporation | Flexible stent |
US6998060B2 (en) * | 2001-03-01 | 2006-02-14 | Cordis Corporation | Flexible stent and method of manufacture |
US6679911B2 (en) * | 2001-03-01 | 2004-01-20 | Cordis Corporation | Flexible stent |
US20030069630A1 (en) * | 2001-03-02 | 2003-04-10 | Robert Burgermeister | Stent with radiopaque markers incorporated thereon |
AU784552B2 (en) * | 2001-03-02 | 2006-05-04 | Cardinal Health 529, Llc | Flexible stent |
US6585753B2 (en) * | 2001-03-28 | 2003-07-01 | Scimed Life Systems, Inc. | Expandable coil stent |
US6719804B2 (en) | 2001-04-02 | 2004-04-13 | Scimed Life Systems, Inc. | Medical stent and related methods |
DE10118944B4 (en) | 2001-04-18 | 2013-01-31 | Merit Medical Systems, Inc. | Removable, essentially cylindrical implants |
US20050021123A1 (en) | 2001-04-30 | 2005-01-27 | Jurgen Dorn | Variable speed self-expanding stent delivery system and luer locking connector |
US6685745B2 (en) * | 2001-05-15 | 2004-02-03 | Scimed Life Systems, Inc. | Delivering an agent to a patient's body |
US6494855B2 (en) * | 2001-05-16 | 2002-12-17 | Scimed Life Systems, Inc. | Draining bodily fluid |
BR0103255A (en) * | 2001-05-16 | 2003-05-20 | Christiane Dias Maues | Cylindrical tubular prosthetic device; and prosthetic device with biological cover for drug release; and its intraluminal splitting system |
US8617231B2 (en) | 2001-05-18 | 2013-12-31 | Boston Scientific Scimed, Inc. | Dual guidewire exchange catheter system |
US6981964B2 (en) * | 2001-05-22 | 2006-01-03 | Boston Scientific Scimed, Inc. | Draining bodily fluids with a stent |
US6939373B2 (en) * | 2003-08-20 | 2005-09-06 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US6629994B2 (en) | 2001-06-11 | 2003-10-07 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US6635083B1 (en) | 2001-06-25 | 2003-10-21 | Advanced Cardiovascular Systems, Inc. | Stent with non-linear links and method of use |
US6749629B1 (en) | 2001-06-27 | 2004-06-15 | Advanced Cardiovascular Systems, Inc. | Stent pattern with figure-eights |
US6605110B2 (en) | 2001-06-29 | 2003-08-12 | Advanced Cardiovascular Systems, Inc. | Stent with enhanced bendability and flexibility |
US6607554B2 (en) * | 2001-06-29 | 2003-08-19 | Advanced Cardiovascular Systems, Inc. | Universal stent link design |
WO2003009773A2 (en) | 2001-07-26 | 2003-02-06 | Alveolus Inc. | Removable stent and method of using the same |
US20030032999A1 (en) | 2001-08-07 | 2003-02-13 | Medtronic Ave, Inc. | Balloon stent assembly system and method |
US7708712B2 (en) * | 2001-09-04 | 2010-05-04 | Broncus Technologies, Inc. | Methods and devices for maintaining patency of surgically created channels in a body organ |
IES20010828A2 (en) * | 2001-09-12 | 2003-03-19 | Medtronic Inc | Medical device for intraluminal endovascular stenting |
US6620202B2 (en) | 2001-10-16 | 2003-09-16 | Scimed Life Systems, Inc. | Medical stent with variable coil and related methods |
US7147661B2 (en) | 2001-12-20 | 2006-12-12 | Boston Scientific Santa Rosa Corp. | Radially expandable stent |
US20030135256A1 (en) | 2002-01-14 | 2003-07-17 | Gallagher Brendan P. | Stent delivery system |
US7473273B2 (en) * | 2002-01-22 | 2009-01-06 | Medtronic Vascular, Inc. | Stent assembly with therapeutic agent exterior banding |
US7326245B2 (en) * | 2002-01-31 | 2008-02-05 | Boston Scientific Scimed, Inc. | Medical device for delivering biologically active material |
US7445629B2 (en) * | 2002-01-31 | 2008-11-04 | Boston Scientific Scimed, Inc. | Medical device for delivering biologically active material |
US8506647B2 (en) | 2002-02-14 | 2013-08-13 | Boston Scientific Scimed, Inc. | System for maintaining body canal patency |
US8328877B2 (en) | 2002-03-19 | 2012-12-11 | Boston Scientific Scimed, Inc. | Stent retention element and related methods |
US8260967B2 (en) * | 2002-04-02 | 2012-09-04 | Verizon Business Global Llc | Billing system for communications services involving telephony and instant communications |
US7083822B2 (en) * | 2002-04-26 | 2006-08-01 | Medtronic Vascular, Inc. | Overlapping coated stents |
US7470281B2 (en) * | 2002-04-26 | 2008-12-30 | Medtronic Vascular, Inc. | Coated stent with crimpable coating |
WO2003092549A2 (en) * | 2002-05-06 | 2003-11-13 | Abbott Laboratories | Endoprosthesis for controlled contraction and expansion |
JP2005524488A (en) * | 2002-05-08 | 2005-08-18 | アボット・ラボラトリーズ | Endoprosthesis with extended foot |
US6656220B1 (en) | 2002-06-17 | 2003-12-02 | Advanced Cardiovascular Systems, Inc. | Intravascular stent |
US9561123B2 (en) | 2002-08-30 | 2017-02-07 | C.R. Bard, Inc. | Highly flexible stent and method of manufacture |
US6878162B2 (en) * | 2002-08-30 | 2005-04-12 | Edwards Lifesciences Ag | Helical stent having improved flexibility and expandability |
EP1542616B1 (en) | 2002-09-20 | 2015-04-22 | Endologix, Inc. | Stent-graft with positioning anchor |
AU2003270817B2 (en) * | 2002-09-26 | 2009-09-17 | Vactronix Scientific, Llc | High strength vacuum deposited nitionol alloy films, medical thin film graft materials and method of making same |
EP1569762B1 (en) * | 2002-10-22 | 2007-10-03 | Medtronic Vascular, Inc. | Stent with intermittent coating |
US20060149365A1 (en) * | 2002-10-22 | 2006-07-06 | Medtronic Vascular, Inc. | Stent with eccentric coating |
EP1413261A1 (en) | 2002-10-23 | 2004-04-28 | Medtronic Vascular, Inc. | Stent with detachable ends |
US20040093056A1 (en) | 2002-10-26 | 2004-05-13 | Johnson Lianw M. | Medical appliance delivery apparatus and method of use |
US7527644B2 (en) | 2002-11-05 | 2009-05-05 | Alveolus Inc. | Stent with geometry determinated functionality and method of making the same |
US7959671B2 (en) | 2002-11-05 | 2011-06-14 | Merit Medical Systems, Inc. | Differential covering and coating methods |
US7637942B2 (en) | 2002-11-05 | 2009-12-29 | Merit Medical Systems, Inc. | Coated stent with geometry determinated functionality and method of making the same |
US7875068B2 (en) | 2002-11-05 | 2011-01-25 | Merit Medical Systems, Inc. | Removable biliary stent |
DE10261822A1 (en) * | 2002-12-20 | 2004-07-01 | Biotronik Meß- und Therapiegeräte GmbH & Co. Ingenieurbüro Berlin | Helix bridge connection |
US20040147998A1 (en) * | 2003-01-24 | 2004-07-29 | Nolting John E. | Differentially coated stent |
US20040148001A1 (en) * | 2003-01-24 | 2004-07-29 | Nolting John E. | Solvent-bonded stent-graft assembly |
US7354519B1 (en) | 2003-02-03 | 2008-04-08 | Hutchinson Technology Incorporated | Method and apparatus for fabricating a stent |
US7179286B2 (en) * | 2003-02-21 | 2007-02-20 | Boston Scientific Scimed, Inc. | Stent with stepped connectors |
US7367989B2 (en) * | 2003-02-27 | 2008-05-06 | Scimed Life Systems, Inc. | Rotating balloon expandable sheath bifurcation delivery |
US7314480B2 (en) * | 2003-02-27 | 2008-01-01 | Boston Scientific Scimed, Inc. | Rotating balloon expandable sheath bifurcation delivery |
US20040180131A1 (en) * | 2003-03-14 | 2004-09-16 | Medtronic Ave. | Stent coating method |
ATE492246T1 (en) * | 2003-03-19 | 2011-01-15 | Advanced Bio Prosthetic Surfac | ENDOLUMINAL STENT WITH CENTER CONNECTING LINKS |
US6929663B2 (en) * | 2003-03-26 | 2005-08-16 | Boston Scientific Scimed, Inc. | Longitudinally expanding medical device |
US7637934B2 (en) | 2003-03-31 | 2009-12-29 | Merit Medical Systems, Inc. | Medical appliance optical delivery and deployment apparatus and method |
EP1608294B1 (en) * | 2003-04-02 | 2007-12-26 | Boston Scientific Limited | Detachable and retrievable stent assembly |
US20040199246A1 (en) * | 2003-04-02 | 2004-10-07 | Scimed Life Systems, Inc. | Expandable stent |
US7731747B2 (en) | 2003-04-14 | 2010-06-08 | Tryton Medical, Inc. | Vascular bifurcation prosthesis with multiple thin fronds |
US8109987B2 (en) | 2003-04-14 | 2012-02-07 | Tryton Medical, Inc. | Method of treating a lumenal bifurcation |
US8083791B2 (en) | 2003-04-14 | 2011-12-27 | Tryton Medical, Inc. | Method of treating a lumenal bifurcation |
US7972372B2 (en) | 2003-04-14 | 2011-07-05 | Tryton Medical, Inc. | Kit for treating vascular bifurcations |
US7481834B2 (en) * | 2003-04-14 | 2009-01-27 | Tryton Medical, Inc. | Stent for placement at luminal os |
US7758630B2 (en) | 2003-04-14 | 2010-07-20 | Tryton Medical, Inc. | Helical ostium support for treating vascular bifurcations |
US7717953B2 (en) | 2004-10-13 | 2010-05-18 | Tryton Medical, Inc. | Delivery system for placement of prosthesis at luminal OS |
US6777647B1 (en) | 2003-04-16 | 2004-08-17 | Scimed Life Systems, Inc. | Combination laser cutter and cleaner |
US6958073B2 (en) * | 2003-04-21 | 2005-10-25 | Medtronic Vascular, Inc. | Method and system for stent retention using an adhesive |
US7198637B2 (en) * | 2003-04-21 | 2007-04-03 | Medtronic Vascular, Inc. | Method and system for stent retention using an adhesive |
US20040215313A1 (en) * | 2003-04-22 | 2004-10-28 | Peiwen Cheng | Stent with sandwich type coating |
US6945992B2 (en) * | 2003-04-22 | 2005-09-20 | Medtronic Vascular, Inc. | Single-piece crown stent |
US7377937B2 (en) * | 2003-04-22 | 2008-05-27 | Medtronic Vascular, Inc. | Stent-graft assembly with elution openings |
US20040236399A1 (en) * | 2003-04-22 | 2004-11-25 | Medtronic Vascular, Inc. | Stent with improved surface adhesion |
US20040230176A1 (en) * | 2003-04-23 | 2004-11-18 | Medtronic Vascular, Inc. | System for treating a vascular condition that inhibits restenosis at stent ends |
US20040215323A1 (en) * | 2003-04-24 | 2004-10-28 | Medtronic Ave, Inc. | Membrane eyelet |
US20040215328A1 (en) * | 2003-04-25 | 2004-10-28 | Ronan Thornton | Bifurcated stent with concentric body portions |
US20040215311A1 (en) * | 2003-04-28 | 2004-10-28 | Kantor John D. | Method and system for improving stent retention using stent openings |
US7604660B2 (en) | 2003-05-01 | 2009-10-20 | Merit Medical Systems, Inc. | Bifurcated medical appliance delivery apparatus and method |
US7625398B2 (en) * | 2003-05-06 | 2009-12-01 | Abbott Laboratories | Endoprosthesis having foot extensions |
US7625401B2 (en) * | 2003-05-06 | 2009-12-01 | Abbott Laboratories | Endoprosthesis having foot extensions |
US7651529B2 (en) | 2003-05-09 | 2010-01-26 | Boston Scientific Scimed, Inc. | Stricture retractor |
US7105015B2 (en) * | 2003-06-17 | 2006-09-12 | Medtronic Vascular, Inc. | Method and system for treating an ostium of a side-branch vessel |
US20060210600A1 (en) * | 2003-07-07 | 2006-09-21 | Medtronic Vascular, Inc. | Coated stent with timed release of multiple therapeutic agents to inhibit restenosis adjacent to the stent ends |
US8784472B2 (en) * | 2003-08-15 | 2014-07-22 | Boston Scientific Scimed, Inc. | Clutch driven stent delivery system |
US8298280B2 (en) | 2003-08-21 | 2012-10-30 | Boston Scientific Scimed, Inc. | Stent with protruding branch portion for bifurcated vessels |
US20050055078A1 (en) * | 2003-09-04 | 2005-03-10 | Medtronic Vascular, Inc. | Stent with outer slough coating |
US7785653B2 (en) | 2003-09-22 | 2010-08-31 | Innovational Holdings Llc | Method and apparatus for loading a beneficial agent into an expandable medical device |
US8801692B2 (en) * | 2003-09-24 | 2014-08-12 | Medtronic Vascular, Inc. | Gradient coated stent and method of fabrication |
US20050080479A1 (en) * | 2003-09-29 | 2005-04-14 | Feng James Q. | Expandable endovascular stent |
US7055237B2 (en) * | 2003-09-29 | 2006-06-06 | Medtronic Vascular, Inc. | Method of forming a drug eluting stent |
US8043357B2 (en) * | 2003-10-10 | 2011-10-25 | Cook Medical Technologies Llc | Ring stent |
US20050085889A1 (en) * | 2003-10-17 | 2005-04-21 | Rangarajan Sundar | Stent with detachable ends |
US7344557B2 (en) | 2003-11-12 | 2008-03-18 | Advanced Stent Technologies, Inc. | Catheter balloon systems and methods |
US20050131530A1 (en) * | 2003-12-15 | 2005-06-16 | Darack Ed E. | Endoluminal stent |
US7686841B2 (en) * | 2003-12-29 | 2010-03-30 | Boston Scientific Scimed, Inc. | Rotating balloon expandable sheath bifurcation delivery system |
US7922753B2 (en) * | 2004-01-13 | 2011-04-12 | Boston Scientific Scimed, Inc. | Bifurcated stent delivery system |
US8012192B2 (en) * | 2004-02-18 | 2011-09-06 | Boston Scientific Scimed, Inc. | Multi-stent delivery system |
US7225518B2 (en) | 2004-02-23 | 2007-06-05 | Boston Scientific Scimed, Inc. | Apparatus for crimping a stent assembly |
US7922740B2 (en) | 2004-02-24 | 2011-04-12 | Boston Scientific Scimed, Inc. | Rotatable catheter assembly |
US7744619B2 (en) | 2004-02-24 | 2010-06-29 | Boston Scientific Scimed, Inc. | Rotatable catheter assembly |
EP1737391A2 (en) * | 2004-04-13 | 2007-01-03 | Cook Incorporated | Implantable frame with variable compliance |
US7955371B2 (en) * | 2004-05-12 | 2011-06-07 | Medtronic Vascular, Inc. | System and method for stent deployment and infusion of a therapeutic agent into tissue adjacent to the stent ends |
US20050273151A1 (en) * | 2004-06-04 | 2005-12-08 | John Fulkerson | Stent delivery system |
US20050273149A1 (en) * | 2004-06-08 | 2005-12-08 | Tran Thomas T | Bifurcated stent delivery system |
US20060015170A1 (en) * | 2004-07-16 | 2006-01-19 | Jones Ryan A | Contrast coated stent and method of fabrication |
US8048145B2 (en) | 2004-07-22 | 2011-11-01 | Endologix, Inc. | Graft systems having filling structures supported by scaffolds and methods for their use |
US20060036308A1 (en) * | 2004-08-12 | 2006-02-16 | Medtronic Vascular, Inc. | Stent with extruded covering |
US7763067B2 (en) | 2004-09-01 | 2010-07-27 | C. R. Bard, Inc. | Stent and method for manufacturing the stent |
US20060064155A1 (en) * | 2004-09-01 | 2006-03-23 | Pst, Llc | Stent and method for manufacturing the stent |
GB0419954D0 (en) | 2004-09-08 | 2004-10-13 | Advotek Medical Devices Ltd | System for directing therapy |
US20060058869A1 (en) * | 2004-09-14 | 2006-03-16 | Vascular Architects, Inc., A Delaware Corporation | Coiled ladder stent |
US7393181B2 (en) | 2004-09-17 | 2008-07-01 | The Penn State Research Foundation | Expandable impeller pump |
US20060074396A1 (en) * | 2004-09-28 | 2006-04-06 | Medtronic Vascular, Inc. | Stent delivery system |
US7887579B2 (en) | 2004-09-29 | 2011-02-15 | Merit Medical Systems, Inc. | Active stent |
US20060079951A1 (en) * | 2004-10-08 | 2006-04-13 | Medtronic Vascular, Inc. | Guide catheter with attached stent delivery system |
AR054656A1 (en) * | 2005-04-03 | 2007-07-11 | Liliana Rosa Grinfeld | STENT FOR OSTIAL INJURIES AND VASCULAR FORKS |
CN101484089B (en) | 2005-04-04 | 2015-11-25 | 可挠支架装置公司 | Flexible stent |
US20060276882A1 (en) * | 2005-04-11 | 2006-12-07 | Cook Incorporated | Medical device including remodelable material attached to frame |
US7947207B2 (en) | 2005-04-12 | 2011-05-24 | Abbott Cardiovascular Systems Inc. | Method for retaining a vascular stent on a catheter |
US7763198B2 (en) | 2005-04-12 | 2010-07-27 | Abbott Cardiovascular Systems Inc. | Method for retaining a vascular stent on a catheter |
US8628565B2 (en) * | 2005-04-13 | 2014-01-14 | Abbott Cardiovascular Systems Inc. | Intravascular stent |
US20060248698A1 (en) * | 2005-05-05 | 2006-11-09 | Hanson Brian J | Tubular stent and methods of making the same |
US7731654B2 (en) | 2005-05-13 | 2010-06-08 | Merit Medical Systems, Inc. | Delivery device with viewing window and associated method |
WO2007005800A1 (en) * | 2005-06-30 | 2007-01-11 | Abbott Laboratories | Endoprosthesis having foot extensions |
EP1903985A4 (en) | 2005-07-07 | 2010-04-28 | Nellix Inc | Systems and methods for endovascular aneurysm treatment |
JP2009504345A (en) * | 2005-08-17 | 2009-02-05 | シー・アール・バード・インコーポレーテッド | Variable speed stent delivery system |
US7682304B2 (en) * | 2005-09-21 | 2010-03-23 | Medtronic, Inc. | Composite heart valve apparatus manufactured using techniques involving laser machining of tissue |
US7404823B2 (en) * | 2005-10-31 | 2008-07-29 | Boston Scientific Scimed, Inc. | Stent configurations |
US20070112418A1 (en) | 2005-11-14 | 2007-05-17 | Boston Scientific Scimed, Inc. | Stent with spiral side-branch support designs |
US7381217B2 (en) * | 2005-12-23 | 2008-06-03 | Boston Scientific Scimed, Inc. | Serpentine stent pattern |
WO2007081530A2 (en) * | 2006-01-03 | 2007-07-19 | Med Institute, Inc. | Endoluminal medical device for local delivery of cathepsin inhibitors |
US20080286325A1 (en) * | 2006-01-05 | 2008-11-20 | Med Institute, Inc. | Cyclodextrin elution media for medical device coatings comprising a taxane therapeutic agent |
US7919108B2 (en) * | 2006-03-10 | 2011-04-05 | Cook Incorporated | Taxane coatings for implantable medical devices |
US9078781B2 (en) | 2006-01-11 | 2015-07-14 | Medtronic, Inc. | Sterile cover for compressible stents used in percutaneous device delivery systems |
US11026822B2 (en) | 2006-01-13 | 2021-06-08 | C. R. Bard, Inc. | Stent delivery system |
WO2007084370A1 (en) | 2006-01-13 | 2007-07-26 | C.R. Bard, Inc. | Stent delivery system |
US20070173925A1 (en) * | 2006-01-25 | 2007-07-26 | Cornova, Inc. | Flexible expandable stent |
US8092819B2 (en) * | 2006-01-27 | 2012-01-10 | Cook Medical Technologies LLC. | Implantable medical device coated with a bioactive agent |
CA2948428C (en) | 2006-02-14 | 2020-06-30 | Angiomed Gmbh & Co. Medizintechnik Kg | Highly flexible stent and method of manufacture |
US20070191926A1 (en) * | 2006-02-14 | 2007-08-16 | Advanced Cardiovascular Systems, Inc. | Stent pattern for high stent retention |
US8821561B2 (en) | 2006-02-22 | 2014-09-02 | Boston Scientific Scimed, Inc. | Marker arrangement for bifurcation catheter |
US7875284B2 (en) * | 2006-03-10 | 2011-01-25 | Cook Incorporated | Methods of manufacturing and modifying taxane coatings for implantable medical devices |
US8828077B2 (en) | 2006-03-15 | 2014-09-09 | Medinol Ltd. | Flat process of preparing drug eluting stents |
AU2007230945B2 (en) | 2006-03-23 | 2013-05-02 | The Penn State Research Foundation | Heart assist device with expandable impeller pump |
US8043358B2 (en) * | 2006-03-29 | 2011-10-25 | Boston Scientific Scimed, Inc. | Stent with overlap and high extension |
US8348991B2 (en) * | 2006-03-29 | 2013-01-08 | Boston Scientific Scimed, Inc. | Stent with overlap and high expansion |
US7318837B2 (en) * | 2006-03-30 | 2008-01-15 | Medtronic Vascular, Inc. | Customized alloys for stents |
US7955383B2 (en) * | 2006-04-25 | 2011-06-07 | Medtronics Vascular, Inc. | Laminated implantable medical device having a metallic coating |
US9101505B2 (en) * | 2006-04-27 | 2015-08-11 | Brs Holdings, Llc | Composite stent |
US9155646B2 (en) | 2006-04-27 | 2015-10-13 | Brs Holdings, Llc | Composite stent with bioremovable ceramic flakes |
US7744643B2 (en) * | 2006-05-04 | 2010-06-29 | Boston Scientific Scimed, Inc. | Displaceable stent side branch structure |
US7691400B2 (en) * | 2006-05-05 | 2010-04-06 | Medtronic Vascular, Inc. | Medical device having coating with zeolite drug reservoirs |
CA2652871C (en) * | 2006-05-12 | 2016-01-12 | Cordis Corporation | Balloon expandable bioabsorbable drug eluting flexible stent |
US20070283969A1 (en) * | 2006-06-12 | 2007-12-13 | Medtronic Vascular, Inc. | Method of Diagnosing and Treating Erectile Dysfunction |
WO2008005284A2 (en) | 2006-06-30 | 2008-01-10 | Cook Incorporated | Methods of manufacturing and modifying taxane coatings for implantable medical devices |
US8613698B2 (en) | 2006-07-10 | 2013-12-24 | Mcneil-Ppc, Inc. | Resilient device |
US10004584B2 (en) | 2006-07-10 | 2018-06-26 | First Quality Hygienic, Inc. | Resilient intravaginal device |
US8047980B2 (en) | 2006-07-10 | 2011-11-01 | Mcneil-Ppc, Inc. | Method of treating urinary incontinence |
CN104257450B (en) | 2006-07-10 | 2017-05-10 | 第一次质量卫生公司 | Resilient Device |
US10219884B2 (en) | 2006-07-10 | 2019-03-05 | First Quality Hygienic, Inc. | Resilient device |
US7833260B2 (en) * | 2006-07-20 | 2010-11-16 | Orbusneich Medical, Inc. | Bioabsorbable polymeric medical device |
EP3009477B1 (en) | 2006-07-20 | 2024-01-24 | Orbusneich Medical Pte. Ltd | Bioabsorbable polymeric composition for a medical device |
WO2008011612A2 (en) * | 2006-07-20 | 2008-01-24 | Orbusneich Medical, Inc. | Bioabsorbable polymeric medical device |
CN101516291B (en) * | 2006-07-20 | 2013-08-21 | 奥巴斯尼茨医学公司 | Bioabsorbable polymeric medical device |
GB0615658D0 (en) | 2006-08-07 | 2006-09-13 | Angiomed Ag | Hand-held actuator device |
EP2056746A2 (en) * | 2006-08-17 | 2009-05-13 | NFOCUS Neuromedical Inc. | Aneurysm covering devices and delivery devices |
US20080177371A1 (en) * | 2006-08-28 | 2008-07-24 | Cornova, Inc. | Implantable devices and methods of forming the same |
US8414637B2 (en) * | 2006-09-08 | 2013-04-09 | Boston Scientific Scimed, Inc. | Stent |
US7988720B2 (en) | 2006-09-12 | 2011-08-02 | Boston Scientific Scimed, Inc. | Longitudinally flexible expandable stent |
US20080082038A1 (en) * | 2006-09-28 | 2008-04-03 | Vance Products Incorporated, D/B/A/ Cook Urological Incorporated | Medical Device including a Bioactive in a Non-ionic and an Ionic Form and Methods of Preparation Thereof |
US20080108824A1 (en) * | 2006-09-28 | 2008-05-08 | Med Institute, Inc | Medical Devices Incorporating a Bioactive and Methods of Preparing Such Devices |
US20080081829A1 (en) * | 2006-09-28 | 2008-04-03 | Med Institute, Inc | Medical Device Including an Anesthetic and Method of Preparation Thereof |
US8778009B2 (en) * | 2006-10-06 | 2014-07-15 | Abbott Cardiovascular Systems Inc. | Intravascular stent |
US7854957B2 (en) | 2006-10-18 | 2010-12-21 | Innovational Holdings, Llc | Systems and methods for producing a medical device |
CN101631513B (en) * | 2006-10-20 | 2013-06-05 | 奥巴斯尼茨医学公司 | Bioabsorbable polymeric composition and medical device |
US7959942B2 (en) * | 2006-10-20 | 2011-06-14 | Orbusneich Medical, Inc. | Bioabsorbable medical device with coating |
US20080119927A1 (en) * | 2006-11-17 | 2008-05-22 | Medtronic Vascular, Inc. | Stent Coating Including Therapeutic Biodegradable Glass, and Method of Making |
US20080133000A1 (en) * | 2006-12-01 | 2008-06-05 | Medtronic Vascular, Inc. | Bifurcated Stent With Variable Length Branches |
US7651527B2 (en) | 2006-12-15 | 2010-01-26 | Medtronic Vascular, Inc. | Bioresorbable stent |
US9510943B2 (en) | 2007-01-19 | 2016-12-06 | Medtronic, Inc. | Stented heart valve devices and methods for atrioventricular valve replacement |
US8052740B2 (en) * | 2007-02-09 | 2011-11-08 | Piolax Medical Devices, Inc. | Stent including a marker fitted to a frame portion |
US8333799B2 (en) | 2007-02-12 | 2012-12-18 | C. R. Bard, Inc. | Highly flexible stent and method of manufacture |
EP4005537A1 (en) * | 2007-02-12 | 2022-06-01 | C.R. Bard Inc. | Highly flexible stent and method of manufacture |
US20080208352A1 (en) * | 2007-02-27 | 2008-08-28 | Medtronic Vascular, Inc. | Stent Having Controlled Porosity for Improved Ductility |
US20080206441A1 (en) * | 2007-02-27 | 2008-08-28 | Medtronic Vascular, Inc. | Ion Beam Etching a Surface of an Implantable Medical Device |
US8974514B2 (en) * | 2007-03-13 | 2015-03-10 | Abbott Cardiovascular Systems Inc. | Intravascular stent with integrated link and ring strut |
US20080234800A1 (en) * | 2007-03-20 | 2008-09-25 | Medtronic Vascular, Inc. | Stent Including a Toggle Lock |
US20080249458A1 (en) * | 2007-04-09 | 2008-10-09 | Medtronic Vascular, Inc. | Intraventricular Shunt and Methods of Use Therefor |
US8128679B2 (en) | 2007-05-23 | 2012-03-06 | Abbott Laboratories Vascular Enterprises Limited | Flexible stent with torque-absorbing connectors |
US8016874B2 (en) | 2007-05-23 | 2011-09-13 | Abbott Laboratories Vascular Enterprises Limited | Flexible stent with elevated scaffolding properties |
US8007470B2 (en) | 2007-07-10 | 2011-08-30 | Cook Medical Technologies Llc | Minimally invasive medical device and method for delivery of therapeutic or diagnostic agents into a vessel wall |
GB0713497D0 (en) | 2007-07-11 | 2007-08-22 | Angiomed Ag | Device for catheter sheath retraction |
US20110130822A1 (en) * | 2007-07-20 | 2011-06-02 | Orbusneich Medical, Inc. | Bioabsorbable Polymeric Compositions and Medical Devices |
US20100094405A1 (en) * | 2008-10-10 | 2010-04-15 | Orbusneich Medical, Inc. | Bioabsorbable Polymeric Medical Device |
US8486134B2 (en) | 2007-08-01 | 2013-07-16 | Boston Scientific Scimed, Inc. | Bifurcation treatment system and methods |
US8092864B2 (en) * | 2007-08-28 | 2012-01-10 | Cook Medical Technologies Llc | Mandrel and method for coating open-cell implantable endovascular structures |
US8066755B2 (en) | 2007-09-26 | 2011-11-29 | Trivascular, Inc. | System and method of pivoted stent deployment |
US8663309B2 (en) | 2007-09-26 | 2014-03-04 | Trivascular, Inc. | Asymmetric stent apparatus and method |
US8226701B2 (en) | 2007-09-26 | 2012-07-24 | Trivascular, Inc. | Stent and delivery system for deployment thereof |
CN101917929A (en) | 2007-10-04 | 2010-12-15 | 特里瓦斯库拉尔公司 | Modular vascular graft for low profile percutaneous delivery |
US20090118811A1 (en) * | 2007-11-05 | 2009-05-07 | Medtronic Vascular, Inc. | Globe Stent |
US7828840B2 (en) * | 2007-11-15 | 2010-11-09 | Med Institute, Inc. | Medical devices and methods for local delivery of angiotensin II type 2 receptor antagonists |
US8328861B2 (en) | 2007-11-16 | 2012-12-11 | Trivascular, Inc. | Delivery system and method for bifurcated graft |
US8083789B2 (en) | 2007-11-16 | 2011-12-27 | Trivascular, Inc. | Securement assembly and method for expandable endovascular device |
US8397666B2 (en) * | 2007-12-06 | 2013-03-19 | Cook Medical Technologies Llc | Mandrel coating assembly |
US8128677B2 (en) | 2007-12-12 | 2012-03-06 | Intact Vascular LLC | Device and method for tacking plaque to a blood vessel wall |
US9603730B2 (en) | 2007-12-12 | 2017-03-28 | Intact Vascular, Inc. | Endoluminal device and method |
US9375327B2 (en) | 2007-12-12 | 2016-06-28 | Intact Vascular, Inc. | Endovascular implant |
US10166127B2 (en) | 2007-12-12 | 2019-01-01 | Intact Vascular, Inc. | Endoluminal device and method |
US10022250B2 (en) | 2007-12-12 | 2018-07-17 | Intact Vascular, Inc. | Deployment device for placement of multiple intraluminal surgical staples |
US7896911B2 (en) | 2007-12-12 | 2011-03-01 | Innovasc Llc | Device and method for tacking plaque to blood vessel wall |
US8157751B2 (en) * | 2007-12-13 | 2012-04-17 | Boston Scientific Scimed, Inc. | Coil member for a medical device |
US7815687B2 (en) * | 2007-12-18 | 2010-10-19 | Med Institute, Inc. | Method of promoting cell proliferation and ingrowth by injury to the native tissue |
US7972373B2 (en) * | 2007-12-19 | 2011-07-05 | Advanced Technologies And Regenerative Medicine, Llc | Balloon expandable bioabsorbable stent with a single stress concentration region interconnecting adjacent struts |
US20090163998A1 (en) * | 2007-12-20 | 2009-06-25 | Abbott Laboratories Vascular Enterprises Limited | Endoprosthesis having rings linked by foot extensions |
US7850726B2 (en) | 2007-12-20 | 2010-12-14 | Abbott Laboratories Vascular Enterprises Limited | Endoprosthesis having struts linked by foot extensions |
US8337544B2 (en) | 2007-12-20 | 2012-12-25 | Abbott Laboratories Vascular Enterprises Limited | Endoprosthesis having flexible connectors |
US8920488B2 (en) | 2007-12-20 | 2014-12-30 | Abbott Laboratories Vascular Enterprises Limited | Endoprosthesis having a stable architecture |
WO2009088953A2 (en) | 2007-12-31 | 2009-07-16 | Boston Scientific Scimed Inc. | Bifurcation stent delivery system and methods |
US8196279B2 (en) | 2008-02-27 | 2012-06-12 | C. R. Bard, Inc. | Stent-graft covering process |
US20090248034A1 (en) * | 2008-03-28 | 2009-10-01 | Medtronic Vascular, Inc. | Method of Diagnosing and Treating Benign Prostatic Hyperplasia |
JP5391407B2 (en) * | 2008-04-03 | 2014-01-15 | クック・メディカル・テクノロジーズ・リミテッド・ライアビリティ・カンパニー | Self-cleaning device, system and method of use thereof |
US7806923B2 (en) * | 2008-04-11 | 2010-10-05 | Medtronic Vascular, Inc. | Side branch stent having a proximal split ring |
US20090259299A1 (en) * | 2008-04-14 | 2009-10-15 | Medtronic Vascular, Inc. | Side Branch Stent Having a Proximal Flexible Material Section |
AU2009240419A1 (en) | 2008-04-25 | 2009-10-29 | Nellix, Inc. | Stent graft delivery system |
US8136218B2 (en) | 2008-04-29 | 2012-03-20 | Medtronic, Inc. | Prosthetic heart valve, prosthetic heart valve assembly and method for making same |
US8333003B2 (en) | 2008-05-19 | 2012-12-18 | Boston Scientific Scimed, Inc. | Bifurcation stent crimping systems and methods |
US8377108B2 (en) | 2008-06-02 | 2013-02-19 | Boston Scientific Scimed, Inc. | Staggered two balloon bifurcation catheter assembly and methods |
CA2726596A1 (en) | 2008-06-04 | 2009-12-10 | Nellix, Inc. | Sealing apparatus and methods of use |
US8827954B2 (en) | 2008-06-05 | 2014-09-09 | Boston Scientific Scimed, Inc. | Deflatable bifurcated device |
WO2009149405A1 (en) | 2008-06-05 | 2009-12-10 | Boston Scientific Scimed, Inc. | Balloon bifurcated lumen treatment |
US8147898B2 (en) * | 2008-07-25 | 2012-04-03 | Medtronic Vascular, Inc. | Low temperature drug deposition |
US20100036471A1 (en) * | 2008-08-05 | 2010-02-11 | Medtronic Vascular, Inc. | Method of Diagnosing and Treating Lower Urinary Tract Symptoms |
US8133199B2 (en) | 2008-08-27 | 2012-03-13 | Boston Scientific Scimed, Inc. | Electroactive polymer activation system for a medical device |
US20100145433A1 (en) * | 2008-09-30 | 2010-06-10 | Abbott Cardiovascular Systems, Inc. | Endoprostheses for deployment in a body lumen |
WO2010042952A1 (en) * | 2008-10-11 | 2010-04-15 | Orbusneich Medical, Inc. | Bioabsorbable polymeric compositions and medical devices |
US20100125323A1 (en) * | 2008-11-14 | 2010-05-20 | Medtronic Vascular, Inc. | Coil Stent Delivery System and Method of Use |
US20100125326A1 (en) * | 2008-11-20 | 2010-05-20 | Medtronic Vascular, Inc. | Braided Stent With a Shortenable Tether |
US20100125325A1 (en) * | 2008-11-20 | 2010-05-20 | Medtronic Vascular, Inc. | Stent With Cathodic Protection and Stent Delivery System |
US20100204770A1 (en) * | 2009-02-10 | 2010-08-12 | Medtronic Vascular, Inc. | Stent Delivery System Permitting in Vivo Stent Repositioning |
US8021420B2 (en) * | 2009-03-12 | 2011-09-20 | Medtronic Vascular, Inc. | Prosthetic valve delivery system |
US20100241069A1 (en) | 2009-03-19 | 2010-09-23 | Abbott Cardiovascular Systems Inc. | Ostial lesion stent delivery system |
US8052741B2 (en) * | 2009-03-23 | 2011-11-08 | Medtronic Vascular, Inc. | Branch vessel prosthesis with a roll-up sealing assembly |
US20100256723A1 (en) * | 2009-04-03 | 2010-10-07 | Medtronic Vascular, Inc. | Prosthetic Valve With Device for Restricting Expansion |
US9066785B2 (en) | 2009-04-06 | 2015-06-30 | Medtronic Vascular, Inc. | Packaging systems for percutaneously deliverable bioprosthetic valves |
US20100261737A1 (en) * | 2009-04-10 | 2010-10-14 | Medtronic Vascular, Inc. | Method of Treating Erectile Dysfunction |
US20100268320A1 (en) | 2009-04-17 | 2010-10-21 | Medtronic Vascular, Inc. | Endovascular Implant Having an Integral Graft Component and Method of Manufacture |
US8052737B2 (en) * | 2009-05-05 | 2011-11-08 | Medtronic Vascular, Inc. | Implantable temporary flow restrictor device |
US8366763B2 (en) | 2009-07-02 | 2013-02-05 | Tryton Medical, Inc. | Ostium support for treating vascular bifurcations |
US20110070358A1 (en) | 2009-09-20 | 2011-03-24 | Medtronic Vascular, Inc. | Method of forming hollow tubular drug eluting medical devices |
US8298279B2 (en) * | 2009-09-24 | 2012-10-30 | Medtronic Vascular, Inc. | Stent including a toggle lock strut |
US8114149B2 (en) * | 2009-10-20 | 2012-02-14 | Svelte Medical Systems, Inc. | Hybrid stent with helical connectors |
US20110098799A1 (en) | 2009-10-27 | 2011-04-28 | Medtronic Vascular, Inc. | Stent Combined with a Biological Scaffold Seeded With Endothelial Cells |
BR112012011466B1 (en) * | 2009-10-30 | 2020-10-27 | Cordis Corporation | stent for insertion into a patient's vessel |
EP2496189A4 (en) | 2009-11-04 | 2016-05-11 | Nitinol Devices And Components Inc | Alternating circumferential bridge stent design and methods for use thereof |
US20110276078A1 (en) | 2009-12-30 | 2011-11-10 | Nellix, Inc. | Filling structure for a graft system and methods of use |
US8512393B2 (en) | 2010-02-26 | 2013-08-20 | ProMed, Inc. | Apparatus for vessel access closure |
EP3042616A1 (en) | 2010-02-26 | 2016-07-13 | Promed, Inc. | System and method for vessel access closure |
US8636811B2 (en) | 2010-04-07 | 2014-01-28 | Medtronic Vascular, Inc. | Drug eluting rolled stent and stent delivery system |
US8882824B2 (en) * | 2010-04-20 | 2014-11-11 | Cg Bio Co., Ltd. | Expanding vascular stent |
US9237961B2 (en) | 2010-04-23 | 2016-01-19 | Medtronic Vascular, Inc. | Stent delivery system for detecting wall apposition of the stent during deployment |
US9615948B2 (en) | 2010-04-26 | 2017-04-11 | Medtronic Vascular, Inc. | Drug eluting folded stent and stent delivery system |
US8377365B2 (en) | 2010-04-29 | 2013-02-19 | Medtronic Vascular, Inc. | System and method for stent manufacture |
US8858615B2 (en) * | 2010-05-19 | 2014-10-14 | National Taiwan University | Preventing vascular stenosis of cardiovascular stent |
US9301864B2 (en) | 2010-06-08 | 2016-04-05 | Veniti, Inc. | Bi-directional stent delivery system |
US20120010691A1 (en) | 2010-07-06 | 2012-01-12 | Medtronic Vascular, Inc. | Particle Embedded Polymer Stent and Method of Manufacture |
US8268382B2 (en) | 2010-07-12 | 2012-09-18 | Medtronic Vascular, Inc. | Method of making a stent with hollow struts |
US9233014B2 (en) | 2010-09-24 | 2016-01-12 | Veniti, Inc. | Stent with support braces |
EP2624791B1 (en) | 2010-10-08 | 2017-06-21 | Confluent Medical Technologies, Inc. | Alternating circumferential bridge stent design |
GB201017834D0 (en) | 2010-10-21 | 2010-12-01 | Angiomed Ag | System to deliver a bodily implant |
US9788933B2 (en) * | 2010-10-29 | 2017-10-17 | Cook Medical Technologies Llc | Medical device delivery system and deployment method |
WO2012071542A2 (en) | 2010-11-24 | 2012-05-31 | Tryton Medical, Inc. | Support for treating vascular bifurcations |
EP2658484A1 (en) | 2010-12-30 | 2013-11-06 | Boston Scientific Scimed, Inc. | Multi stage opening stent designs |
US9138518B2 (en) | 2011-01-06 | 2015-09-22 | Thoratec Corporation | Percutaneous heart pump |
US8801768B2 (en) | 2011-01-21 | 2014-08-12 | Endologix, Inc. | Graft systems having semi-permeable filling structures and methods for their use |
US8790388B2 (en) | 2011-03-03 | 2014-07-29 | Boston Scientific Scimed, Inc. | Stent with reduced profile |
EP2680797B1 (en) | 2011-03-03 | 2016-10-26 | Boston Scientific Scimed, Inc. | Low strain high strength stent |
CN103648437B (en) | 2011-04-06 | 2016-05-04 | 恩朵罗杰克斯国际控股有限公司 | For the method and system of vascular aneurysms treatment |
WO2012149205A1 (en) | 2011-04-27 | 2012-11-01 | Dolan Mark J | Nerve impingement systems including an intravascular prosthesis and an extravascular prosthesis and associated systems and methods |
US10271973B2 (en) | 2011-06-03 | 2019-04-30 | Intact Vascular, Inc. | Endovascular implant |
EP3733134A1 (en) | 2012-01-25 | 2020-11-04 | Intact Vascular, Inc. | Endoluminal device |
WO2013120082A1 (en) | 2012-02-10 | 2013-08-15 | Kassab Ghassan S | Methods and uses of biological tissues for various stent and other medical applications |
US8934988B2 (en) * | 2012-03-16 | 2015-01-13 | St. Jude Medical Ab | Ablation stent with meander structure |
US8992595B2 (en) | 2012-04-04 | 2015-03-31 | Trivascular, Inc. | Durable stent graft with tapered struts and stable delivery methods and devices |
US9498363B2 (en) | 2012-04-06 | 2016-11-22 | Trivascular, Inc. | Delivery catheter for endovascular device |
WO2013162724A1 (en) | 2012-04-26 | 2013-10-31 | Tryton Medical, Inc. | Support for treating vascular bifurcations |
US9872947B2 (en) | 2012-05-14 | 2018-01-23 | Tc1 Llc | Sheath system for catheter pump |
US8721517B2 (en) | 2012-05-14 | 2014-05-13 | Thoratec Corporation | Impeller for catheter pump |
US9446179B2 (en) | 2012-05-14 | 2016-09-20 | Thoratec Corporation | Distal bearing support |
DE102013008168A1 (en) | 2012-05-14 | 2013-11-14 | Thoratec Corporation | Impeller for catheter pump |
US9421311B2 (en) | 2012-07-03 | 2016-08-23 | Thoratec Corporation | Motor assembly for catheter pump |
EP4186557A1 (en) | 2012-07-03 | 2023-05-31 | Tc1 Llc | Motor assembly for catheter pump |
US9358329B2 (en) | 2012-07-03 | 2016-06-07 | Thoratec Corporation | Catheter pump |
US20140031917A1 (en) | 2012-07-25 | 2014-01-30 | Medtronic Vascular, Inc. | Matched End Stiffness Stent and Method of Manufacture |
US9072619B2 (en) | 2012-12-05 | 2015-07-07 | Medtronic Vascular, Inc. | Preferentially electropolished stent system and method of manufacture |
EP2953580A2 (en) | 2013-02-11 | 2015-12-16 | Cook Medical Technologies LLC | Expandable support frame and medical device |
EP4122520A1 (en) | 2013-03-13 | 2023-01-25 | Tc1 Llc | Fluid handling system |
US11033728B2 (en) | 2013-03-13 | 2021-06-15 | Tc1 Llc | Fluid handling system |
US11077294B2 (en) | 2013-03-13 | 2021-08-03 | Tc1 Llc | Sheath assembly for catheter pump |
US10561509B2 (en) | 2013-03-13 | 2020-02-18 | DePuy Synthes Products, Inc. | Braided stent with expansion ring and method of delivery |
WO2014159093A1 (en) | 2013-03-14 | 2014-10-02 | Endologix, Inc. | Method for forming materials in situ within a medical device |
US9308302B2 (en) | 2013-03-15 | 2016-04-12 | Thoratec Corporation | Catheter pump assembly including a stator |
US10271975B2 (en) * | 2013-03-15 | 2019-04-30 | Atrium Medical Corporation | Stent device having reduced foreshortening and recoil and method of making same |
US20160030649A1 (en) | 2013-03-15 | 2016-02-04 | Thoratec Corporation | Catheter pump assembly including a stator |
US9398966B2 (en) | 2013-03-15 | 2016-07-26 | Medtronic Vascular, Inc. | Welded stent and stent delivery system |
DE102013104550B4 (en) | 2013-05-03 | 2021-07-01 | Acandis Gmbh | Medical device for insertion into a hollow organ in the body |
CA2913110A1 (en) | 2013-06-11 | 2014-12-18 | ProMed, Inc. | Systems and methods for improved vessel access closure |
EP3010451B1 (en) | 2013-06-21 | 2021-11-24 | Boston Scientific Scimed, Inc. | Stent with deflecting connector |
JP6081948B2 (en) * | 2014-03-25 | 2017-02-15 | 株式会社World Medish Technology | Flexible stent |
EP3791920A1 (en) | 2014-04-15 | 2021-03-17 | Tc1 Llc | Catheter pump introducer systems and methods |
WO2015160979A1 (en) | 2014-04-15 | 2015-10-22 | Thoratec Corporation | Catheter pump with access ports |
EP3131615B1 (en) | 2014-04-15 | 2021-06-09 | Tc1 Llc | Sensors for catheter pumps |
WO2015160942A1 (en) | 2014-04-15 | 2015-10-22 | Thoratec Corporation | Catheter pump with off-set motor position |
US9545263B2 (en) | 2014-06-19 | 2017-01-17 | Limflow Gmbh | Devices and methods for treating lower extremity vasculature |
EP3183024B1 (en) | 2014-08-18 | 2019-09-18 | Tc1 Llc | Guide features for percutaneous catheter pump |
US10206796B2 (en) | 2014-08-27 | 2019-02-19 | DePuy Synthes Products, Inc. | Multi-strand implant with enhanced radiopacity |
EP3598986B1 (en) | 2015-01-22 | 2021-02-17 | Tc1 Llc | Motor assembly with heat exchanger for catheter pump |
WO2016118784A1 (en) | 2015-01-22 | 2016-07-28 | Thoratec Corporation | Attachment mechanisms for motor of catheter pump |
US9770543B2 (en) | 2015-01-22 | 2017-09-26 | Tc1 Llc | Reduced rotational mass motor assembly for catheter pump |
US9433520B2 (en) | 2015-01-29 | 2016-09-06 | Intact Vascular, Inc. | Delivery device and method of delivery |
US9375336B1 (en) | 2015-01-29 | 2016-06-28 | Intact Vascular, Inc. | Delivery device and method of delivery |
US9907890B2 (en) | 2015-04-16 | 2018-03-06 | Tc1 Llc | Catheter pump with positioning brace |
EP3324884A1 (en) * | 2015-07-19 | 2018-05-30 | Sanford Health | Bridging stent graft with combination balloon expandable and self-expandable stents and methods for use |
US10993824B2 (en) | 2016-01-01 | 2021-05-04 | Intact Vascular, Inc. | Delivery device and method of delivery |
WO2017172823A1 (en) | 2016-03-31 | 2017-10-05 | Vesper Medical, Inc. | Intravascular implants |
EP3808403A1 (en) | 2016-07-21 | 2021-04-21 | Tc1 Llc | Fluid seals for catheter pump motor assembly |
EP3808401A1 (en) | 2016-07-21 | 2021-04-21 | Tc1 Llc | Gas-filled chamber for catheter pump motor assembly |
US10076428B2 (en) | 2016-08-25 | 2018-09-18 | DePuy Synthes Products, Inc. | Expansion ring for a braided stent |
US10292851B2 (en) | 2016-09-30 | 2019-05-21 | DePuy Synthes Products, Inc. | Self-expanding device delivery apparatus with dual function bump |
US10182927B2 (en) * | 2016-10-21 | 2019-01-22 | DePuy Synthes Products, Inc. | Expansion ring for a braided stent |
AU2018214780B2 (en) * | 2017-02-01 | 2022-02-03 | Japan Medical Device Technology Co., Ltd. | Bioabsorbable stent |
US11523920B2 (en) * | 2017-03-16 | 2022-12-13 | Keyvon Rashidi | Stent with a smooth surface in its expanded configuration |
EP4299086A2 (en) | 2017-04-10 | 2024-01-03 | LimFlow GmbH | Devices for treating lower extremity vasculature |
US10238513B2 (en) | 2017-07-19 | 2019-03-26 | Abbott Cardiovascular Systems Inc. | Intravascular stent |
US11660218B2 (en) | 2017-07-26 | 2023-05-30 | Intact Vascular, Inc. | Delivery device and method of delivery |
US10849769B2 (en) | 2017-08-23 | 2020-12-01 | Vesper Medical, Inc. | Non-foreshortening stent |
US11628076B2 (en) | 2017-09-08 | 2023-04-18 | Vesper Medical, Inc. | Hybrid stent |
US10271977B2 (en) | 2017-09-08 | 2019-04-30 | Vesper Medical, Inc. | Hybrid stent |
US11357650B2 (en) | 2019-02-28 | 2022-06-14 | Vesper Medical, Inc. | Hybrid stent |
US11364134B2 (en) | 2018-02-15 | 2022-06-21 | Vesper Medical, Inc. | Tapering stent |
US10500078B2 (en) | 2018-03-09 | 2019-12-10 | Vesper Medical, Inc. | Implantable stent |
US10575973B2 (en) | 2018-04-11 | 2020-03-03 | Abbott Cardiovascular Systems Inc. | Intravascular stent having high fatigue performance |
AU2019204522A1 (en) | 2018-07-30 | 2020-02-13 | DePuy Synthes Products, Inc. | Systems and methods of manufacturing and using an expansion ring |
US10456280B1 (en) | 2018-08-06 | 2019-10-29 | DePuy Synthes Products, Inc. | Systems and methods of using a braided implant |
US10278848B1 (en) | 2018-08-06 | 2019-05-07 | DePuy Synthes Products, Inc. | Stent delivery with expansion assisting delivery wire |
WO2020076833A1 (en) | 2018-10-09 | 2020-04-16 | Limflow Gmbh | Devices and methods for catheter alignment |
US11039944B2 (en) | 2018-12-27 | 2021-06-22 | DePuy Synthes Products, Inc. | Braided stent system with one or more expansion rings |
EP4051174A4 (en) | 2019-11-01 | 2023-11-22 | LimFlow GmbH | Devices and methods for increasing blood perfusion to a distal extremity |
Family Cites Families (56)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4733665C2 (en) * | 1985-11-07 | 2002-01-29 | Expandable Grafts Partnership | Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft |
US4893623A (en) * | 1986-12-09 | 1990-01-16 | Advanced Surgical Intervention, Inc. | Method and apparatus for treating hypertrophy of the prostate gland |
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 |
US5133732A (en) * | 1987-10-19 | 1992-07-28 | 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 |
US4856516A (en) * | 1989-01-09 | 1989-08-15 | Cordis Corporation | Endovascular stent apparatus and method |
US4994071A (en) * | 1989-05-22 | 1991-02-19 | Cordis Corporation | Bifurcating stent apparatus and method |
CA2026604A1 (en) * | 1989-10-02 | 1991-04-03 | Rodney G. Wolff | Articulated stent |
CA2052981C (en) * | 1990-10-09 | 1995-08-01 | Cesare Gianturco | Percutaneous stent assembly |
US5356423A (en) | 1991-01-04 | 1994-10-18 | American Medical Systems, Inc. | Resectable self-expanding stent |
US5178618A (en) * | 1991-01-16 | 1993-01-12 | Brigham And Womens Hospital | Method and device for recanalization of a body passageway |
US5135536A (en) * | 1991-02-05 | 1992-08-04 | Cordis Corporation | Endovascular stent and method |
US5116365A (en) * | 1991-02-22 | 1992-05-26 | Cordis Corporation | Stent apparatus and method for making |
US5527354A (en) * | 1991-06-28 | 1996-06-18 | Cook Incorporated | Stent formed of half-round wire |
US5314472A (en) * | 1991-10-01 | 1994-05-24 | Cook Incorporated | Vascular stent |
US5293879A (en) * | 1991-09-23 | 1994-03-15 | Vitatron Medical, B.V. | System an method for detecting tremors such as those which result from parkinson's disease |
US5366504A (en) | 1992-05-20 | 1994-11-22 | Boston Scientific Corporation | Tubular medical prosthesis |
US5234457A (en) * | 1991-10-09 | 1993-08-10 | Boston Scientific Corporation | Impregnated stent |
US5354309A (en) * | 1991-10-11 | 1994-10-11 | Angiomed Ag | Apparatus for widening a stenosis in a body cavity |
CA2380683C (en) * | 1991-10-28 | 2006-08-08 | Advanced Cardiovascular Systems, Inc. | Expandable stents and method for making same |
FR2683449A1 (en) * | 1991-11-08 | 1993-05-14 | Cardon Alain | ENDOPROTHESIS FOR TRANSLUMINAL IMPLANTATION. |
US5507767A (en) * | 1992-01-15 | 1996-04-16 | Cook Incorporated | Spiral stent |
US5282823A (en) * | 1992-03-19 | 1994-02-01 | Medtronic, Inc. | Intravascular radially expandable stent |
US5540712A (en) * | 1992-05-01 | 1996-07-30 | Nitinol Medical Technologies, Inc. | Stent and method and apparatus for forming and delivering the same |
US5342387A (en) * | 1992-06-18 | 1994-08-30 | American Biomed, Inc. | Artificial support for a blood vessel |
US5366473A (en) * | 1992-08-18 | 1994-11-22 | Ultrasonic Sensing And Monitoring Systems, Inc. | Method and apparatus for applying vascular grafts |
US5389106A (en) * | 1993-10-29 | 1995-02-14 | Numed, Inc. | Impermeable expandable intravascular stent |
US5643312A (en) * | 1994-02-25 | 1997-07-01 | Fischell Robert | Stent having a multiplicity of closed circular structures |
US5549663A (en) * | 1994-03-09 | 1996-08-27 | Cordis Corporation | Endoprosthesis having graft member and exposed welded end junctions, method and procedure |
US5733303A (en) | 1994-03-17 | 1998-03-31 | Medinol Ltd. | Flexible expandable stent |
US5449373A (en) * | 1994-03-17 | 1995-09-12 | Medinol Ltd. | Articulated stent |
JP2825452B2 (en) * | 1994-04-25 | 1998-11-18 | アドヴァンスド カーディオヴァスキュラー システムズ インコーポレーテッド | Radiopak stent marker |
US5554181A (en) * | 1994-05-04 | 1996-09-10 | Regents Of The University Of Minnesota | Stent |
DE4424242A1 (en) * | 1994-07-09 | 1996-01-11 | Ernst Peter Prof Dr M Strecker | Endoprosthesis implantable percutaneously in a patient's body |
US5636641A (en) * | 1994-07-25 | 1997-06-10 | Advanced Cardiovascular Systems, Inc. | High strength member for intracorporeal use |
US5549662A (en) * | 1994-11-07 | 1996-08-27 | Scimed Life Systems, Inc. | Expandable stent using sliding members |
EP0790810B1 (en) * | 1994-11-09 | 2004-04-28 | Endotex Interventional Systems, Inc. | Kit of delivery catheter and graft for aneurysm repair |
CA2163824C (en) * | 1994-11-28 | 2000-06-20 | Richard J. Saunders | Method and apparatus for direct laser cutting of metal stents |
US5630829A (en) * | 1994-12-09 | 1997-05-20 | Intervascular, Inc. | High hoop strength intraluminal stent |
DE19505393A1 (en) * | 1995-02-17 | 1996-08-22 | Byk Sangtec Diagnostica | Starter kit |
DE69622231T2 (en) * | 1995-03-01 | 2002-12-05 | Scimed Life Systems Inc | LENGTHFLEXIBLE AND EXPANDABLE STENT |
US5591197A (en) * | 1995-03-14 | 1997-01-07 | Advanced Cardiovascular Systems, Inc. | Expandable stent forming projecting barbs and method for deploying |
ES2119527T5 (en) * | 1995-04-01 | 2006-11-16 | Variomed Ag | STENT DEVICE FOR TRANSLUMINAL IMPLEMENTATION IN HOLLOW ORGANS. |
US5613981A (en) * | 1995-04-21 | 1997-03-25 | Medtronic, Inc. | Bidirectional dual sinusoidal helix stent |
US5591198A (en) * | 1995-04-27 | 1997-01-07 | Medtronic, Inc. | Multiple sinusoidal wave configuration stent |
RU2157146C2 (en) * | 1995-06-13 | 2000-10-10 | ВИЛЬЯМ КУК Европа, A/S | Device for performing implantation in blood vessels and hollow organs |
US5776161A (en) * | 1995-10-16 | 1998-07-07 | Instent, Inc. | Medical stents, apparatus and method for making same |
WO1997014375A1 (en) * | 1995-10-20 | 1997-04-24 | Bandula Wijay | Vascular stent |
US5607442A (en) * | 1995-11-13 | 1997-03-04 | Isostent, Inc. | Stent with improved radiopacity and appearance characteristics |
US5697971A (en) * | 1996-06-11 | 1997-12-16 | Fischell; Robert E. | Multi-cell stent with cells having differing characteristics |
US5755776A (en) * | 1996-10-04 | 1998-05-26 | Al-Saadon; Khalid | Permanent expandable intraluminal tubular stent |
US5827321A (en) * | 1997-02-07 | 1998-10-27 | Cornerstone Devices, Inc. | Non-Foreshortening intraluminal prosthesis |
US6033433A (en) * | 1997-04-25 | 2000-03-07 | Scimed Life Systems, Inc. | Stent configurations including spirals |
US5741327A (en) * | 1997-05-06 | 1998-04-21 | Global Therapeutics, Inc. | Surgical stent featuring radiopaque markers |
US5911754A (en) * | 1998-07-24 | 1999-06-15 | Uni-Cath Inc. | Flexible stent with effective strut and connector patterns |
-
1995
- 1995-10-16 US US08/543,337 patent/US5776161A/en not_active Expired - Lifetime
-
1997
- 1997-02-03 JP JP09519200A patent/JP2001501488A/en not_active Ceased
- 1997-02-03 CA CA002246386A patent/CA2246386A1/en not_active Abandoned
- 1997-02-03 EP EP06000217A patent/EP1649830A1/en not_active Withdrawn
- 1997-02-03 DE DE69736228T patent/DE69736228T2/en not_active Expired - Lifetime
- 1997-02-03 EP EP97903559A patent/EP0909198B1/en not_active Expired - Lifetime
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- 1997-02-03 AU AU18081/97A patent/AU1808197A/en not_active Abandoned
- 1997-02-03 DE DE29723905U patent/DE29723905U1/en not_active Expired - Lifetime
- 1997-10-02 US US08/942,648 patent/US6090127A/en not_active Expired - Lifetime
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2000
- 2000-03-22 US US09/533,879 patent/US6428570B1/en not_active Expired - Lifetime
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2002
- 2002-07-09 US US10/192,072 patent/US6641609B2/en not_active Expired - Fee Related
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