WO2002022049A2 - Implantable prosthesis for intravascular applications - Google Patents
Implantable prosthesis for intravascular applications Download PDFInfo
- Publication number
- WO2002022049A2 WO2002022049A2 PCT/DE2001/003528 DE0103528W WO0222049A2 WO 2002022049 A2 WO2002022049 A2 WO 2002022049A2 DE 0103528 W DE0103528 W DE 0103528W WO 0222049 A2 WO0222049 A2 WO 0222049A2
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- prosthesis
- strand
- prosthesis according
- prostheses
- section
- Prior art date
Links
Classifications
-
- 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
- A61F2/88—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure the wire-like elements formed as helical or spiral coils
-
- 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
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0002—Two-dimensional shapes, e.g. cross-sections
- A61F2230/0028—Shapes in the form of latin or greek characters
- A61F2230/0054—V-shaped
Definitions
- the invention relates to an implantable prosthesis for intravascular applications.
- High-pressure expandable stents are inserted into the vessels with the help of balloon dilators and expanded by internal overpressure. In doing so, their structure deforms. After removing the dilator, the stent remains dimensionally stable. In so-called self-expanding prostheses, the stent opens due to existing restoring forces or due to the prevailing environmental conditions, such as flow and temperature.
- the delivery systems required for this category of stents must be designed accordingly.
- the stent is to be designed in such a way that it only assumes its desired shape after being introduced into the vessels.
- the hollow organ, such as the vessel is expanded by the stent and supported on the other. Any existing stenosis is removed.
- sloted tube prostheses are predominantly made from a cut tube (sloted tube prostheses).
- sloted tube prostheses are subject to the well-known mechanical laws of buckling under external pressure and buckling under axial loading, as well as fatigue under permanent transverse loading.
- the so-called collapse or bulge pressure is decisive for the design and the design of such prostheses, since it reflects the actual resistance of the structure in the vessel after the implantation and thus determines the durability of the implant.
- Due to the cylindrical initial shape of the prosthesis the level of the dent pressure is physically limited and is usually below 0.8 bar. Medically reasonable and desirable higher collapse limits cannot be achieved with such cylinder structures.
- tubular, sloted tube prostheses are also largely determined by the design.
- cylindrical prostheses can only be crimped up to a certain diameter, since they also assume the contour of a tube in the crimped state and, as a result, cannot fall below a minimum achievable outer diameter.
- a low stone insertion diameter (possibly less than 1 mm) required by medical professionals cannot be achieved with sloted tubes prostheses, or only to a limited extent with clear reductions in the case of achievable collapse pressures.
- sloted tube prostheses are rigid both in the radial and in the longitudinal direction. They therefore represent an unnatural barrier to any vascular movement. In addition to allergic reactions, this often triggers mechanical actions in the body and a. the phenomenon of restenosis is greatly favored.
- Sloted tube prostheses made from a tube often have sharp-edged corners and edges, so that during implantation and dilation there is a risk of cutting open and injuring vascular areas (intima). From a fluidic point of view, these areas represent considerable resistance, which often - due to the resulting roughness - lead to turbulence.
- the consequences are thrombosis or similar complications.
- a move has been made to electropolishing it.
- the charge polarization of the prosthesis during electropolishing creates electromagnetic fields that have a corresponding magnetic influence on the blood flowing through. The consequences can also be thrombosis and coagulation symptoms.
- mesh prostheses have been manufactured using textile techniques, such as weaving, knitting, braiding, etc.
- textile techniques such as weaving, knitting, braiding, etc.
- wall stent and the reheatr stent are also known examples of this.
- These mesh prostheses are flexible. They are made from wire material and have a number of advantages. Nevertheless, these prostheses have proven to be of little use in normal day-to-day operations.
- the textile techniques used result in a close-knit structure with a round structure.
- the prosthesis design determined in this way thus shows a considerable accumulation of material.
- the consequences of this are often allergic reactions, turbulence and similar fluid mechanical phenomena that lead to thrombosis.
- mesh prostheses are mainly used only for larger vessels, where turbulence plays a subordinate role and is accepted.
- the ends of the mesh prosthesis are usually not post-treated either. As a result, they sometimes cause serious intimate traumas. Since there is a build-up of material at these ends due to the manufacturing process, this is a constructive solution
- DE 197 22 857 A1 shows a stent which consists of at least one thin-walled, tubular body, the lateral surface of which is divided into web-like elements which extend in the longitudinal direction of the stent and are expandable in the circumferential direction of the stent. These elements are each connected to the two expandable elements adjacent in the circumferential direction of the stent via at least one connecting web and to the end face of an expandable element adjacent in the longitudinal direction of the stent via an end stop.
- this stent which is provided in particular as a coronary stent, lacks the required flexibility.
- the stent is associated with a complicated and costly manufacture.
- DE 1 766 921 describes a surgical dilator which consists of a grid-like tube, the grid elements of which are designed and / or run in such a way that the wall of the tube contracts diametrically and expands axially when an axial tensile force acts and when the tensile force ceases in the essentially returns to its normal form.
- DE 41 37 857 A1 discloses a device with a prosthesis which can be implanted in the body of a patient and which is designed as a hollow body.
- the hollow body is compressed against the action of resilient spring forces to a cross-section which is reduced in relation to the expanded position of use and is held in this position by means of an expandable covering.
- This sheathing which can be a mesh, for example in the form of a crochet, extends over the entire length of the prosthesis and consists of at least one continuous thread and at least one pulling line. By pulling on the covering, the prosthesis expands automatically to a cross section corresponding to the position of use.
- it has proven to be problematic in its application, particularly with regard to the application of the covering.
- a blood vessel support device which has an elongated metal wire mesh which is expandable in the radial direction, the metal wire mesh having at least one axial end having a plurality of individually projecting elements.
- WO 94/01056 A1 describes a tubular prosthesis with greater flexibility, which consists of loosely interlocking knitting loops of a metal wire that forms the tubular shape and second, also loosely interlocking knitting loops formed of metal wire, which is provided with predetermined, selected substances , whereby both knitted fabrics are joined together to form a co-knitted fabric.
- the disadvantages already mentioned are also associated with this stent.
- the object of the invention is therefore to provide a longitudinally and radially highly flexible implantable prosthesis of the type mentioned at the outset, which is smaller Material intensity has a more favorable stress distribution, is damage-tolerant against lateral load, insofar as it can withstand greater loads and can be crimped to a very small diameter.
- the object is achieved by an implantable prosthesis with the features of claim 1.
- Advantageous configurations of the prosthesis according to the invention result from the features of claims 2 to 11.
- the invention provides an implantable prosthesis which, compared to the prior art, has the advantage of better crimping and dilating behavior with less material intensity. It also has a more favorable stress distribution in the stent system. This considerably reduces the risk of stent venogeny during implantations.
- the advantages of the sloted tube prostheses and the mesh prostheses are brought about by the invention in a medically meaningful manner.
- the implants according to the invention have a particularly high flexibility both longitudinally and radially and a high fatigue strength in the event of collapse pressures.
- stents in areas subject to high shear forces, such as in the peripheral area and in ureters (urological stents) and in highly branched labyrinth-like vessels (such as in the area of neurology) is significantly promoted by the present invention or made possible for the first time.
- the prosthesis according to the invention with its polygonal cross-section, can also be manufactured inexpensively and in high quality using known textile technologies, for example by knitting and knitting.
- the prosthesis can be made with 3, 4, 5, 6, 7 and 8 needles as required. Depending on the needle arrangement and number of needles, the prosthesis is given a polygonal initial cross-sectional shape. This makes it possible for the first time to implement only as much material as necessary in a prosthesis strand. Furthermore, prostheses with significant areas of a certain material concentration can be manufactured. Immediate advantages are:
- the prostheses according to the invention with their prismatic cross section are manufactured close to the final contour.
- the loose structure ends are processed and fixed, for example by welding. This possibility of permanent end fixation is only made possible by the minimal use of materials and the present prosthesis design. In this respect, the prostheses have no significantly protruding ends. This prevents intimate trauma when expanding. Controlled, laminar to convex expansion behavior without twisting also largely prevents intimate irritation.
- the prostheses assume a largely round structure due to the crimping and due to the high pressure dilator.
- the advantages directly associated with this are a very low recoil during crimping and very low circumferential tensions after expansion.
- the prosthesis has a very high resistance to radial pressures (collapse pressures) with the least possible use of material, since the material is trained through this manufacturing process.
- the prosthesis is also characterized by a very high longitudinal and radial flexibility, even with very short lengths.
- the prosthesis is made from semi-finished wire (flat wire, round wire). The manufacturing procedure for wire drawing creates smooth surfaces. Further processing of the wire materials does not significantly damage the surface, making subsequent electropolishing unnecessary. A high bio- and hemocompatibility is given with low thrombogenicity and clot tendency.
- Fig. 1 shows the top view and side view of a prosthesis according to the invention in the expanded state with different profile options and with ends fixed by welding.
- Fig. 2 shows a prosthesis with widening and narrowing in areas.
- Fig. 3 shows the top view of two prostheses according to the invention with different coating or coating options.
- FIG. 1 shows the top view and side view of a prosthesis according to the invention in the expanded state and with ends 3a fixed by welding. It can optionally be designed with the profile cross sections 5a, 5b, 5c, 5d, 5e, 5f and 5g. Depending on the number of needles used in the manufacture of the prosthesis and depending on the mold used, the different cross-sectional profiles can be created.
- the cross-sectional profiles 5a and 5b are rectangular and very well suited for use in cardiology.
- the edge lengths of the profiles depend both on the number of needles actually used and on the possible number of needles of the knitting head used and the diameter of the knitting tool.
- the edges A, B, C, D, E, F and G of the respective prismatic cross section can be of the same length or can be produced in different lengths.
- the shape of the prismatic cross-section as well as the change in the geometry of the prosthesis and its surface quality can be chosen freely depending on the specific implantation requirements, for example whether the implantation affects large arteries in the coronary or peripheral area or ureter or highly branched labyrinth-like vessels or refers to bypass and / or abdominal aortic aneurysm operations.
- prosthesis profiles can be coupled together for branched vessels. If the desired properties of the preferred implant cannot be produced from a starting material 1, 8, 16, then corresponding composite constructions made from several wires and from several suitable materials (e.g. through the incorporation of plastic and / or tantalum). If a reduction in the restenosis rate, which is particularly interesting for patients of so-called risk groups, is also pursued, the prosthesis can be coated or surface-treated with all means known in the art. Both the semi-finished product itself (wires, filaments, yarns, etc.) and the finished prosthesis can be subjected to a suitable coating.
- the strand formed from interconnected meshes is made from materials 1, 8, 16 which meet the requirements for crimpability and dimensional stability after expansion as well as X-ray opacity.
- the stretch and bendability of the prosthesis which can be adjusted depending on the construction and type of material 1, 8, 16 and the stress-resistant design of the structure, prevents both lateral load and compression of the structure from causing malfunctions and failure of the prosthesis .
- the meshes themselves are mechanically / kinematically connected to one another by means of joints 2, 9, 11. They reduce stress and give the prosthesis a particularly high degree of flexibility.
- a special embodiment of the invention provides that the prosthesis is formed with additional stiffeners of a known type.
- a particular advantage of the invention can be seen when the prosthesis is applied to a balloon catheter for the purpose of implantation by high pressure dilation using a suitable crimping device.
- the prosthesis back 6 takes on the task of stabilizing the structure during crimping in such a way that the process-related deformations predominantly from the prosthesis webs 7 be included. They therefore act as a stiffener.
- the deformation of the prosthesis webs 7 compensates for the structural elevations of the back of the prosthesis 6, so that the finished implant has no unevenness in its crimped shape.
- the prosthesis webs 7 and the prosthesis back 6 completely adapt to the structure of the conditions of the vessel, since the provision of the implant is different in some areas.
- the back area 6 of the implant assumes the function of improving the X-ray visualization, since it is inherently more material-intensive than other areas of the implant.
- the material concentration required by X-ray analysis is only present in the back area, which means that the rest of the structure is loaded with less material. This significantly improves biocompatibility.
- FIG. 2 shows a prosthesis made by knitting with widenings 12a and constrictions 12b.
- This advantageous embodiment of the prosthesis allows the implant to be expanded when it is positioned by a balloon catheter, first in the middle and then at its ends (convex, laminar-convex expansion behavior). Any residues are pushed outwards from the center. This is also achieved within certain limits by treating the prosthesis ends 10, for example by welding.
- the connecting joints 2, 9, 11 of the meshes and their free spaces allow the ingrowth of body tissue, so that the implant is firmly anchored in the vessel after a healing period and its surface is covered with endothelium.
- the body tissue can only penetrate to a small extent, so that restenosis cannot occur.
- the geometry of the implant according to the invention is largely determined by the areas of use and the type of vessels to be treated. If high radial and transverse force loads are expected, the required flexibility can be set by the type of mesh material, the choice of the type of profile cross section of the strand, the mesh density and the type of its articulated connection 2, 9, 11.
- the stress and / or strain-induced stresses in the prosthesis according to the invention are due to the structural design of the mechanical / kinematic joints 2, 9, 11 below the permissible values and adapt to the ideal stress-free state even under normal loads.
- the ends 3, 3a, 10 of the highly flexible prosthesis are fixed by means of a suitable welding process, whereby implants can also be designed with a fixed or movable fixation (material, form and force fit) by means of clips and / or knotting or the like of the end wires 4.
- a preferred embodiment of the prosthesis according to the invention shown in FIG. 3 relates to two prostheses according to the invention with different coating or coating options 1a, 13.
- Such a preferred embodiment of the prosthesis according to the invention is specifically intended for bypass (SVG) or for so-called abdominal aortic aneurysm (AAA) operations.
- the prosthesis according to the invention is manufactured to a sufficient length or individually and is provided with a casing 1a, 13 made of biocompatible materials, such as polyethylene terephthalate (PEFT), Dacron or Gore-Tex, PU elastomer or Teflon in a monolithic or sandwich construction.
- the casing 1a, 13 can be fastened with the aid of welding 14.
- the prosthesis can also be immersed in liquid plastic or overmolded with plastic 1a.
- the jacket can also be formed from one or more metallic layers which are attached mechanically, for example by means of clips, to the mesh-like strand in a form-fitting and non-positive manner.
- the jacket 1a, 13 prevents liquids from flowing in or out.
- this version of the implant can be manufactured in long lengths. The end customer can still order the device almost by the meter and cut out the desired lengths depending on the application. This makes this product extremely suitable as an "artificial artery".
- the material of the casing can also be provided with a coating consisting of one or more layers, including a metallic coating 15.
- the jacket 1a, 13 and the coating of the stitch-forming material is furthermore excellently suitable as a carrier material for the storage of medicines.
- medication treatment such as with immunomodulators, immunosuppressants (e.g. sirolimus), antiproliferatives or statins and heparins, etc. ⁇ ., to accelerate healing and to combat restenosis ("to prevent") directly carried out with the introduction of the prosthesis system.
- Coatings 15 and jacket 1a, 13 and also the material of the meshes 1, 8, 16 can consist of a single-layer or multi-layer biodegradable or resorbable material which is broken down in the body after a certain length of time and the components of which are removed.
- the materials 1, 8, 16 must consist of materials that have very good biocompatibility and biocompatibility and that are highly corrosion-resistant. This is solved by using appropriate materials, whereby steel or tantalum materials that are currently common in medicine are used in the construction of the high pressure dilatation.
- the prosthesis can also be used as a so-called “self-expandable” implant.
- suitable shape memory alloys are used as the starting material.
- the functioning of the mechanical / kinematic joints 2, 9, 11 is determined in particular by the manufacturing process of the prosthesis.
- the mesh-like strand can be manufactured using known textile technologies, such as knitting, knitting, winding or braiding processes. These processes are particularly suitable for shaping into a prismatic cross section of the strand and for forming stitches which are connected to one another in an articulated manner from wires, fibers, filaments, yarns or similar starting materials 1, 8, 16.
- Metallic and textile materials or also plastics or composite materials can also be used as starting materials 1, 8, 16.
- mesh-like strands can be produced from these materials, which can then be processed into highly flexible prostheses of the type mentioned at the beginning, which can be used as implants.
- the prosthesis according to the invention thus represents a medically desired new development for holistic support and therapy of vessels in stenoses with surprising positive effects.
- the prosthesis according to the invention replaces previous prostheses and, in a modified form, fulfills the additional function of a artificial artery.
- it has a particularly high degree of flexibility with medically useful improved biocompatibility and cost-reducing purchase.
- it enables the medical professional to treat vascular areas that are inaccessible with the previously known systems.
- the invention opens up a new dimension in the treatment of vascular diseases.
Abstract
Description
Claims
Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
EP01978143A EP1318773A2 (en) | 2000-09-12 | 2001-09-12 | Implantable prosthesis for intravascular applications |
AU2002210360A AU2002210360A1 (en) | 2000-09-12 | 2001-09-12 | Implantable prosthesis for intravascular applications |
DE10193800T DE10193800D2 (en) | 2000-09-12 | 2001-09-12 | Implantable prosthesis for intravascular applications |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE10045325.2 | 2000-09-12 | ||
DE2000145325 DE10045325A1 (en) | 2000-09-12 | 2000-09-12 | Highly flexible implant for intra- or endovascular applications (stent) and manufacturing processes |
Publications (2)
Publication Number | Publication Date |
---|---|
WO2002022049A2 true WO2002022049A2 (en) | 2002-03-21 |
WO2002022049A3 WO2002022049A3 (en) | 2002-08-08 |
Family
ID=7656092
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/DE2001/003528 WO2002022049A2 (en) | 2000-09-12 | 2001-09-12 | Implantable prosthesis for intravascular applications |
Country Status (4)
Country | Link |
---|---|
EP (1) | EP1318773A2 (en) |
AU (1) | AU2002210360A1 (en) |
DE (2) | DE10045325A1 (en) |
WO (1) | WO2002022049A2 (en) |
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7011676B2 (en) | 2002-09-05 | 2006-03-14 | Scimed Life Systems, Inc. | Flat knitted stent and method of making the same |
CN109978781A (en) * | 2019-03-14 | 2019-07-05 | 北京工业大学 | A kind of intravascular ultrasound image segmentation method based on extremal region detection |
US10888414B2 (en) | 2019-03-20 | 2021-01-12 | inQB8 Medical Technologies, LLC | Aortic dissection implant |
Families Citing this family (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE10351220A1 (en) | 2003-10-28 | 2005-06-02 | Deutsche Institute für Textil- und Faserforschung Stuttgart - Stiftung des öffentlichen Rechts | Tubular implant |
DE102004008459A1 (en) * | 2004-02-17 | 2005-09-01 | Aesculap Ag & Co. Kg | Implant, useful as stents, comprises a fabric and at least a radiopaque marker, which passes in a direction along the implant |
Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE1766921B1 (en) | 1966-07-15 | 1970-01-15 | Nat Res Dev | Surgical dilator |
US4580568A (en) | 1984-10-01 | 1986-04-08 | Cook, Incorporated | Percutaneous endovascular stent and method for insertion thereof |
US4655771A (en) | 1982-04-30 | 1987-04-07 | Shepherd Patents S.A. | Prosthesis comprising an expansible or contractile tubular body |
US4830003A (en) | 1988-06-17 | 1989-05-16 | Wolff Rodney G | Compressive stent and delivery system |
DE4137857A1 (en) | 1990-11-26 | 1992-05-27 | Ernst Peter Prof Dr M Strecker | DEVICE WITH A PROSTHESIS IMPLANTABLE IN THE BODY OF A PATIENT |
WO1994001056A1 (en) | 1992-07-13 | 1994-01-20 | Boston Scientific Corporation | Tubular medical prosthesis |
DE19722857A1 (en) | 1997-05-23 | 1998-11-26 | Biotronik Mess & Therapieg | Stent |
DE29904817U1 (en) | 1999-03-16 | 1999-05-27 | Amg Handelsgesellschaft Fuer A | Blood vessel support device |
Family Cites Families (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5957974A (en) * | 1997-01-23 | 1999-09-28 | Schneider (Usa) Inc | Stent graft with braided polymeric sleeve |
-
2000
- 2000-09-12 DE DE2000145325 patent/DE10045325A1/en not_active Withdrawn
-
2001
- 2001-09-12 WO PCT/DE2001/003528 patent/WO2002022049A2/en not_active Application Discontinuation
- 2001-09-12 DE DE10193800T patent/DE10193800D2/en not_active Expired - Fee Related
- 2001-09-12 AU AU2002210360A patent/AU2002210360A1/en not_active Abandoned
- 2001-09-12 EP EP01978143A patent/EP1318773A2/en not_active Withdrawn
Patent Citations (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE1766921B1 (en) | 1966-07-15 | 1970-01-15 | Nat Res Dev | Surgical dilator |
US4655771A (en) | 1982-04-30 | 1987-04-07 | Shepherd Patents S.A. | Prosthesis comprising an expansible or contractile tubular body |
US4655771B1 (en) | 1982-04-30 | 1996-09-10 | Medinvent Ams Sa | Prosthesis comprising an expansible or contractile tubular body |
US4580568A (en) | 1984-10-01 | 1986-04-08 | Cook, Incorporated | Percutaneous endovascular stent and method for insertion thereof |
US4830003A (en) | 1988-06-17 | 1989-05-16 | Wolff Rodney G | Compressive stent and delivery system |
DE4137857A1 (en) | 1990-11-26 | 1992-05-27 | Ernst Peter Prof Dr M Strecker | DEVICE WITH A PROSTHESIS IMPLANTABLE IN THE BODY OF A PATIENT |
WO1994001056A1 (en) | 1992-07-13 | 1994-01-20 | Boston Scientific Corporation | Tubular medical prosthesis |
DE19722857A1 (en) | 1997-05-23 | 1998-11-26 | Biotronik Mess & Therapieg | Stent |
DE29904817U1 (en) | 1999-03-16 | 1999-05-27 | Amg Handelsgesellschaft Fuer A | Blood vessel support device |
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7011676B2 (en) | 2002-09-05 | 2006-03-14 | Scimed Life Systems, Inc. | Flat knitted stent and method of making the same |
CN109978781A (en) * | 2019-03-14 | 2019-07-05 | 北京工业大学 | A kind of intravascular ultrasound image segmentation method based on extremal region detection |
US10888414B2 (en) | 2019-03-20 | 2021-01-12 | inQB8 Medical Technologies, LLC | Aortic dissection implant |
Also Published As
Publication number | Publication date |
---|---|
AU2002210360A1 (en) | 2002-03-26 |
EP1318773A2 (en) | 2003-06-18 |
DE10045325A1 (en) | 2002-04-04 |
DE10193800D2 (en) | 2004-01-22 |
WO2002022049A3 (en) | 2002-08-08 |
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