WO2012061992A1 - 一种滑扣生物可吸收支架及其应用 - Google Patents
一种滑扣生物可吸收支架及其应用 Download PDFInfo
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- WO2012061992A1 WO2012061992A1 PCT/CN2010/078664 CN2010078664W WO2012061992A1 WO 2012061992 A1 WO2012061992 A1 WO 2012061992A1 CN 2010078664 W CN2010078664 W CN 2010078664W WO 2012061992 A1 WO2012061992 A1 WO 2012061992A1
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- Prior art keywords
- stent
- bracket
- lumen
- stenosis
- buckle
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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
- A61F2/02—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
-
- 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
- A61F2/852—Two or more distinct overlapping stents
-
- 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
- A61F2/92—Stents in the form of a rolled-up sheet expanding after insertion into the vessel, e.g. with a spiral shape in cross-section
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/04—Macromolecular materials
- A61L31/06—Macromolecular materials obtained otherwise than by reactions only involving carbon-to-carbon unsaturated bonds
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
- A61L31/14—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
- A61L31/148—Materials at least partially resorbable by the body
-
- 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/848—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents having means for fixation to the vessel wall, e.g. barbs
- A61F2002/8483—Barbs
-
- 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
- A61F2210/00—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2210/0004—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof bioabsorbable
-
- 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
- A61F2210/00—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2210/0076—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof multilayered, e.g. laminated structures
-
- 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
- A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2220/0008—Fixation appliances for connecting prostheses to the body
- A61F2220/0016—Fixation appliances for connecting prostheses to the body with sharp anchoring protrusions, e.g. barbs, pins, spikes
-
- 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
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0058—Additional features; Implant or prostheses properties not otherwise provided for
- A61F2250/0082—Additional features; Implant or prostheses properties not otherwise provided for specially designed for children, e.g. having means for adjusting to their growth
Definitions
- the present invention relates to a medical device, and more particularly to a novel slider bioresorbable stent and use thereof. Background technique
- Congenital heart disease (hereinafter referred to as congenital heart disease) is the most common cardiovascular disease in childhood, the incidence rate is 0.678% of live births, congenital pulmonary artery and pulmonary vein stenosis, body vein in infants with congenital heart disease
- the stenosis of the aorta and its branches accounted for 7%-15% of all congenital heart disease, and the right ventricle-pulmonary artery artificial conduit (RV-PA tubing) stenosis, restenosis after pulmonary and pulmonary veins, and the body vein and
- RV-PA tubing right ventricle-pulmonary artery artificial conduit
- stent effectiveness means that the stent supports the blood vessel and should have sufficient radial strength. Because the blood vessels of infants and young children are in the stage of growth and development, the stents are required to be degradable to facilitate further growth and development of blood vessels. At the same time, the blood vessels of infants and young children are small, and the initial diameter of the stent is required to be small; the transportability and impermeability of X can make the stent easy to be transported to the stenotic lesion.
- the stent After the stent is implanted, it supports the blood vessel wall in the early stage to prevent retraction. With the endothelialization of the stent and the reconstruction of the blood vessel wall in the later stage, the stent only needs temporary support.
- Currently used blood vessel stents and the like are all made of metal. However, the size of the metal stent after implantation is not changed with the growth of the blood vessel, and it is easy to cause artificial stenosis due to the mismatch of the blood vessel size, and is particularly unsuitable for the pediatric vascular stent of a child having growth characteristics.
- Metal stents also have the following defects: (1) long-term antiplatelet therapy is easy to form thrombus; (2) lifelong retention in the human body, affecting subsequent possible surgical treatment; (3) pseudo-presence during nuclear magnetic resonance and CT examination (4) It may change the geometry of the blood vessel to block the branch; (5) hinder the subsequent reconstruction and expansion of the lumen; (6) If the metal stent is not in close contact with the tube wall, a small gap remains after implantation. Therefore, if a biodegradable stent that is similar in performance to a metal stent and completely absorbed after its mission is completed, it can overcome the above weakness of the metal stent and open up a new world for the intervention of congenital heart disease.
- bioresorbable stents in cardiovascular diseases has been studied at home and abroad.
- the current research is mainly poly-L-lactic acid, poly-p-cyclohexanone and polycaprolactone. These materials have passed.
- Igaki-Tamai stent, REVA in the design of bioresorbable stents Brackets and four-leaf structure brackets the common feature of these brackets is a complete cylindrical type before expansion, but there are problems, that is, the support force of all the brackets is insufficient, and the elastic contraction of the brackets is easy to occur, and the manufacturing process of the brackets is complicated.
- the cost is high, and it is limited by support and the like, and cannot be widely applied to other stenosis diseases other than blood vessels.
- Cispheral Patent Publication No. CN 101484195A discloses a "composite stent", which discloses a biodegradable or bioabsorbable multilayer or composite stent comprising a biocoated bioreactor Absorbable ceramic material.
- composite stent discloses a biodegradable or bioabsorbable multilayer or composite stent comprising a biocoated bioreactor Absorbable ceramic material.
- slider bioresorbable stent with strong support and ease of manufacture, and its use as a cardiovascular stent or lumen stent in cardiovascular or luminal stenosis has not been reported.
- a new type of slider bioresorbable stent is used as a cardiovascular system stent or a lumen stent in cardiovascular or luminal stenosis.
- the cardiovascular stenosis disease refers to coronary artery stenosis, carotid stenosis, renal artery stenosis, pulmonary artery and its branch stenosis, aortic and its branch stenosis or stenosis of the pulmonary vein.
- the stenosis of the lumen refers to a disease of the trachea, esophagus, biliary tract, urethra or intestinal stenosis.
- the bracket includes:
- a flat stent body having a mesh structure
- bracket head located at one end of the bracket body, the bracket head being integrally formed with the bracket body, the size of which is adapted to the bracket body, and the bracket head functions as a sliding buckle during the curling process of the bracket;
- a bracket buckle is also integrally formed with the bracket body for fixing the bracket into a tubular bracket buckle during crimping of the bracket.
- the scaffold material is polydioxanone (PD0), polylactic acid (PLA), polydioxanone (PD0), polycaprolactone (PCL), polyglycolic acid (PGA) or poly Hydroxybutyric acid (PHB) high molecular polymer.
- the scaffold material is polydioxanone (PD0).
- the stent further includes a delivery device, the delivery device comprising:
- An outer cannula having a proximal end, a distal end, and a lumen extending between the ends;
- An inner sheath having a proximal end, a distal end, and an inner lumen extending between the ends, the outer diameter of the inner sheath tube being adapted to be slidably inserted into the lumen of the outer cannula;
- a balloon catheter having a proximal end, a distal end, and an inner lumen extending between the ends, the outer diameter of the balloon catheter Suitable for slidingly inserting into the lumen of the inner sheath tube, the distal end of the balloon catheter has a balloon, and a flaky integrated slider bracket can be placed on the balloon and delivered through the catheter into the narrow lumen .
- a novel bio-absorbable stent comprising: a snap type, an edge slide type, an intermediate slide type and a double buckle type bracket, wherein
- Double button brackets include:
- a flat stent body having a mesh structure
- bracket head located at one end of the bracket body, the bracket head being integrally formed with the bracket body, the size of which is adapted to the bracket body, and the bracket head functions as a sliding buckle during the curling process of the bracket;
- bracket buckle also being integrally formed with the bracket body, comprising a tooth structure on both sides of the bracket body and a buckle of the bracket head of the bracket head, for fixing the bracket into the curling process of the bracket Tubular bracket buckle.
- the new slider bioresorbable stent has good degradability and biocompatibility, and is more suitable for pediatric vascular stents. After implantation, there is no late stent thrombosis, so it is not necessary to take antiplatelet drugs for a long time. Affecting possible subsequent surgical procedures;
- the stent is equipped with a delivery system, which reduces the difficulty of surgical operation;
- FIG. 1 is a schematic view of a snap-type bracket of a novel slider bioresorbable stent of the present invention.
- FIG. 2 is a schematic view of an edge slider type bracket of a novel slider bioresorbable stent of the present invention.
- FIG 3 is a schematic view of an intermediate slider type bracket of a novel slider bioresorbable stent of the present invention.
- FIG. 4 is a schematic view of a double buckle type bracket of a novel slider bioresorbable stent of the present invention.
- Figure 5 is a schematic illustration of a delivery system of a novel slider bioresorbable stent of the present invention.
- bracket body 1.
- bracket head 2.
- the mesh tube bracket is obtained by using a stainless steel cylindrical mold.
- the diameter of the mold is the same as the diameter of the required bracket, and a hole is evenly circled on the circumference of both ends of the mold, and the steel needle is inserted, and the number of the upper and lower steel needles is uniform and aligned with each other.
- the PD0 fiber is woven back and forth on the mold. It is necessary to pay attention to the weaving order, and a cylinder which is interlaced and mutually constrained between the fibers and the fibers can be directly woven, and then heat set (90 ° C, 4 hours) to keep the same. The shape, braid density and fiber angle can be adjusted at will.
- the Zigzag stent is obtained by heat-fixing a polymer fiber. On a piece of 3 hidden thick steel plate, use a wire cutting method to make a small hole, then insert a steel needle, fix the PD0 fiber into a sine wave shape with a steel needle, and then place it under suitable setting conditions, so that the fiber has Zigzag The shape has a shape memory effect. A plurality of fibers are bonded together according to the diameter of the stent to obtain a cylindrical stent.
- the slide-type bracket is made of PD0 pellets by three-dimensional micro-jet free-formation technology.
- the bracket is a sheet-like shape before implantation, and the shape includes a bracket body of the mesh structure and a bracket for lifting the buckle.
- the head and the bracket buckle are composed.
- the stent is crimped onto the balloon, and one end is inserted into the other end of the specially designed lock (similar to the "belt buckle") to form a cylindrical stent.
- the stent expands as the balloon expands, and the stent is then buckled after the balloon is removed. , can no longer slide inward to maintain support.
- an X-ray-proof metal mark is loaded in the middle of the mesh structure of the slide-type bracket.
- the slider type bracket is divided into four types: a snap type, an edge slide type, an intermediate slide type and a double buckle type.
- a bioabsorbable slider bracket As shown in Fig. 1, a bioabsorbable slider bracket according to an embodiment of the present invention is shown.
- the bracket comprises: a flat bracket body 1 and a bracket head 2 at one end of the body, the bracket head 2 includes a bracket buckle 22 and an outer frame 21, and a row of mesh holes 11 are arranged on the bracket body portion, and the mesh holes 11
- the sizes can be the same or different. 5-3mmo ⁇
- the size of the mesh 11 is 0. 5-3mmo
- the mesh 11 can be any shape including a circle, an ellipse, a square, a rectangle, a triangle, a polygon, and the like. In one embodiment of the invention, the mesh 11 is circular.
- the bracket buckle 22 is located near the head portion 2 of the bracket and includes 2-4 protruding buckles which together with the outer frame 21 constitute the slider device of the present invention. There may also be more raised buckles depending on the size of the desired bracket and the desired application.
- the length of the protruding buckle is 0. 5-1 at an angle with respect to the plane of the bracket, usually 20-40 degrees. However, it should be understood by those skilled in the art that it can be any other angle.
- the size of the outer frame 21 is adapted to the size of the bracket body 1, so that the inner protruding buckle can be strictly slid along the length of the sheet during the curling of the bracket to avoid misalignment.
- the tabs of the protrusions can be arbitrarily inserted into any of the rows of meshes 11 during sliding, so that the sheets can be fixed into a tubular shape.
- the bracket includes a flat bracket body 1 and a bracket head 2 at one end of the body.
- the bracket head 2 includes an outer frame 21 sized to fit the bracket body 1 with a plurality of teeth 12 on either side of the bracket body 1.
- the bracket includes a longitudinal axis Z extending parallel to the stent head 2 and a transverse axis X extending perpendicular to the stent head 2, as shown in FIG.
- a row of mesh holes 11 are arranged on the bracket body 1 , and the mesh sizes may be the same or different.
- the size of the mesh 11 is evenly distributed, for example, the size of the mesh 11 is 0. 5_3mm.
- the mesh 11 can be any shape including a circle, an ellipse, a square, a rectangle, a triangle, a polygon, and the like. In one embodiment of the invention, the mesh 11 is circular.
- the bracket buckles are represented as teeth 12 on both sides of the bracket body 1.
- the bracket body 1 can pass through the outer frame 21 during the curling of the bracket, and the teeth 12 on both sides can be configured along Both edges of the outer frame 21 slide. During the sliding process, the teeth 12 engage the outer frame 21 to enable the sheet to be fixed into a tubular shape.
- the teeth 12 have a size of 0.1. All of the teeth 12 extend away from the head of the stent at an angle relative to the transverse axis of the stent, such as 30-60 degrees. In one embodiment of the invention, the teeth 12 are at an angle of 30 degrees with respect to the transverse axis of the stent.
- a bioabsorbable slider bracket As shown in Fig. 3, a bioabsorbable slider bracket according to still another embodiment of the present invention is shown.
- the bracket includes a flat bracket body 1 and a bracket head 2 at one end of the body.
- the bracket head 2 includes an outer frame 21 and a buckle structure 23 between the outer frames. Both ends of the buckle structure 23 are connected to the outer frame 21,
- the bracket body 1 includes teeth 12 corresponding to the buckle structure 23, the teeth 12 extending away from the bracket head 2.
- the bracket includes a longitudinal axis Z extending parallel to the bracket head 2 and a transverse axis X extending perpendicular to the bracket head 2.
- a row of mesh holes 11 are arranged on the portion of the bracket body 1, and the sizes of the mesh holes 11 may be the same or different.
- the size of the mesh 11 is 0. 5_3mm.
- the mesh 11 can be any shape including a circle, an ellipse, a square, a rectangle, a triangle, a polygon, and the like. In one embodiment of the invention, the mesh 11 is circular.
- Lmmo The tooth 12 is relative to the transverse axis of the bracket. In one embodiment, the length of the tooth 12 on the bracket body 1 is 0. lmmo. a certain angle Degree, for example, at an angle of 30-60 degrees. In one embodiment of the invention, the teeth 12 are at an angle of 30 degrees with respect to the transverse axis of the stent.
- the teeth 12 are slid along the two sides of the buckle structure 23 in the outer frame 21 of the bracket head. During the sliding process, the teeth 12 are fastened to the buckle structure 23 in the outer frame 21, The sheet can be fixed into a tubular shape.
- the bracket comprises: a flat bracket body 1 and a bracket head 2 at one end of the body, the bracket head 2 includes a bracket buckle 22 and an outer frame 21, and a row of mesh holes 11 are distributed on the bracket body 1 portion, and each mesh hole The size of the 11 can be the same or different, and the bracket body 1 has a plurality of teeth 12 on both sides.
- the bracket buckle 22 is located near the head 2 of the bracket and includes 2-4 protruding buckles. These raised buckles and the teeth 12 on the bracket body together with the outer frame 21 constitute the slider device of the present invention.
- the length of the protruding buckle is 0. 5-lmm, at an angle relative to the plane of the bracket, usually 20-40 degrees. However, those skilled in the art will appreciate that it can be any other angle.
- the size of the outer frame 21 is adapted to the size of the bracket body 1, so that the inner protruding buckle can be strictly slid along the length of the sheet during the curling process of the bracket to avoid misalignment.
- the tabs of the projections can be arbitrarily inserted into any of the rows of meshes 11 during sliding, so that the sheets can be fixed into a tubular shape.
- the teeth 12 on both sides of the bracket body 1 can pass through the outer frame 21 during the curling of the bracket, and the teeth 12 structure on both sides can slide along both edges of the outer frame 21. During the sliding process, the teeth 12 engage the outer frame 21 to enable the sheet to be fixed into a tubular shape.
- the size of the teeth 12 is 0. All of the teeth 12 of the lmmo extend away from the head of the stent at an angle relative to the transverse axis X of the stent, for example 30-60 degrees. In one embodiment of the invention, the teeth 12 are at an angle of 30 degrees with respect to the transverse axis of the stent.
- the double-buckle type bracket has both a buckle and an edge slider, which makes the bracket more supportive during use and ensures the bracket is buckled.
- the bracket cannot be retracted after being fastened.
- the stent is tightly rolled up and attached to the delivery device balloon. After reaching the designated site, the balloon expands to expand the stent sliding diameter, and the balloon is sucked back, and the pressure bracket is buckled by the blood vessel wall. Live, support the blood vessel wall.
- test contents include: radial strength, stent surface coverage, stent axial shrinkage, and stent expansion rate.
- the test results of the mechanical properties of the stent are shown in Table 1.
- the radial strength of the self-expanding mesh tube stent and the Zigzag stent can not meet the clinical needs (generally 80-120Kpa), so it is not suitable for experiment.
- the radial strength of the four balloon-expandable slide-type brackets is above 80Kpa, and the edge-slip-type bracket has reached the radial strength of the metal bracket; at the same time, the slider bracket has no axial contraction rate, which is superior to the metal bracket (5 %); but the expansion rate (29%) is slightly inferior to the metal stent (25%); surface coverage Significantly higher than metal brackets (20%)
- the simulated artificial blood vessel was selected to have a diameter of 6 mm, and the ratio of the stent to the blood vessel was 1.3:1.
- the balloon of the delivery system is sucked into a negative pressure by a pressure pump, the outer sheath tube is withdrawn, the four kinds of slider brackets are respectively wound and wound around the delivery system balloon, and then the outer sheath tube is pushed forward to the cone to wrap.
- Stent insert the delivery system into the hose, 10atm*30 seconds to expand the release stent.
- the evaluation criteria for successful deduction rate are: Success: After the balloon is removed, the stent buckle is stuck and supports the blood vessel; Failure: After the balloon is removed, the stent is not buckled, and the stent tip is curled inward. Failed to support the blood vessels.
- the in vitro simulation results of four different slide-type stents are shown in Table 3.
- the middle slide type, the edge slide type and the double buckle type bracket can be successfully buckled to support the blood vessel wall; however, the buckle type has one failure.
- the four types of slide-type brackets have a very small acute elastic retraction rate (0.40 ⁇ 0.10%).
- Vessel lumen diameter After the balloon is removed, the diameter of the vessel lumen at the stent is measured.
- Acute elastic retraction rate of the stent (diameter when the stent is fully expanded - stent diameter after balloon removal) / diameter when the stent is fully expanded.
- PDO snap-on brackets can be released under normal release pressure (10-14atm), the stent can be successfully buckled, no stent curls into the lumen; the stent basically maintains a preset lumen diameter, with very low acute Elastic retraction rate (0.5%). Prove that this bracket design operation is feasible.
- PDO edge slide-type brackets can be released under normal release pressure (10-14atm), the stent can be successfully buckled, no stent curls into the lumen; the stent basically maintains the preset lumen diameter, which has extremely low Acute elastic retraction rate (0.3%). Prove that this bracket design operation is feasible.
- PDO intermediate slide type brackets can be released under normal release pressure (10-16atm), the brackets can be successfully buckled, no brackets are curled into the lumen; the stent basically maintains the preset lumen diameter, which has extremely low Acute elastic retraction rate (0.43 %). Prove that this bracket design operation is feasible.
- PDO double-buckle brackets can be released under normal release pressure (10-14atm), the stent can be successfully buckled, no stent curls into the lumen; the stent basically maintains a preset lumen diameter, with very low acute Elastic retraction rate (0.3%). Prove that this bracket design operation is feasible.
- the design of the edge slider type bracket compensates for the shortage of the buckle type bracket, and the bracket can ensure the buckle, but the small teeth on both sides of the bracket should be designed to be fine and cannot affect the expansion of the bracket; however, the length of the bracket should ensure the maximum supporting force of the bracket is Premise, the downside is that it cannot be applied to long brackets.
- the middle slider type bracket also compensates for the shortage of the edge slider bracket, which is similar to connecting the two edge slider brackets, both the edge slider and the middle slider. A stent suitable for long lesions.
- the double-buckle type bracket has both a buckle and an edge slider, which makes the bracket more supportive during use and ensures that the bracket is buckled.
- the PDO edge slider type bracket can be released under normal release pressure (10-14atm), the bracket can be successfully buckled, no bracket curls into the lumen; the stent basically maintains the preset lumen diameter, which has extremely low Acute elastic retraction rate (0.3%). Prove that this bracket design operation is feasible.
- PCL Polycaprolactone
- PCL edge slide-type brackets can be released under normal release pressure (l l-15atm), the stent can be successfully buckled, no stent curls into the lumen; the stent basically maintains a preset lumen diameter, which is extremely low The acute elastic retraction rate (0.35 %). Prove that this bracket design operation is feasible.
- PGA edge slide-type brackets can be released under normal release pressure (ll-15atm), the stent can be successfully buckled, no stent curls into the lumen; the stent basically maintains a preset lumen diameter, with extremely low Acute elastic retraction rate (0.35 %). Prove that this bracket design operation is feasible.
- PHB Polyhydroxybutyrate
- the PHB edge slide-type bracket can be released under normal release pressure (l l-15atm), the stent can be successfully buckled, no stent curls into the lumen; the stent basically maintains the preset lumen diameter, which is extremely low The acute elastic retraction rate (0.35 %). Prove that this bracket design operation is feasible.
- PLLA edge slide-type brackets can be released under normal release pressure (ll-15atm), the stent can be successfully buckled, no stent curls into the lumen; the stent basically maintains a preset lumen diameter, with extremely low Acute elastic retraction rate (0.35 %). Prove that this bracket design operation is feasible.
- the in vitro simulated release of the edge-sliding type brackets of the five materials showed that the edge-sliding type brackets of the five materials can be released under the normal release pressure, and the stent can be successfully buckled without the stent curling into the lumen;
- the pre-set lumen diameter is maintained substantially, with an extremely low acute elastic retraction rate.
- the PDO edge slider type bracket has the lowest acute elastic retraction rate (0.3%), which is the best material for manufacturing the edge slider type bracket.
- Cispheral Patent Publication No. CN 101484195A discloses a "composite stent", which discloses a biodegradable or bioabsorbable multilayer or composite stent comprising a biodegradable polymeric material (such as polylactic acid) PLA, polylactide and/or polyglycolic acid PGA, polyglycolide and/or polyglycolide PLGA) coated bioabsorbable ceramic materials (eg calcium phosphate, bioactive glass).
- a biodegradable polymeric material such as polylactic acid) PLA, polylactide and/or polyglycolic acid PGA, polyglycolide and/or polyglycolide PLGA
- bioabsorbable ceramic materials eg calcium phosphate, bioactive glass.
- the disadvantage is that the composite materials of PLA and PLGA have a slow degradation rate, and the complete degradation time is more than 2 years. The degradation rate of PGA is too fast, and the degradation rate can be 70%-80% in 2 weeks. The support
- the composite stent is made of various materials, and the number of stent layers is large.
- the manufacturing process is more complicated; the composite bracket has fewer buckle designs, which limits the degree of curling of the composite bracket, thereby limiting the range of use of the bracket; the angle of the buckle is large, resulting in an increase in the resistance of the stent during the expansion process, and the release pressure is increased. Increase the risk of complications.
- the bracket has only buckles at both ends, and there is no buckle in the middle. The support in the middle will be significantly reduced.
- PDO double button bracket This bracket is made of polydioxanone (PDO). Its fibers have good physical and mechanical strength, chemical stability, biocompatibility and safety, biodegradability, and easy processing.
- the surface of the PDO monofilament structure is smooth and round, which overcomes the shortcomings of the fabric which is easily damaged by the surface due to the large surface friction coefficient.
- PDO has good compatibility, slight tissue reaction, no cell reaction, and is gradually absorbed by the body after 180 days, decomposed into carbon dioxide and water, and discharged from the body, safe and reliable. Due to the ether bond in the chain, the molecular chain is flexible, so it is suitable for making monofilament sutures of various sizes.
- PDO tissue response caused by PDO is small, and it is degraded by hydrolysis in the body tissue, and the strength retention rate is large, which is particularly useful for suturing wounds with a long healing time.
- PDO is considered to be a polymer which is very suitable for the production of stents.
- the PDO double-buckle bracket is made by three-dimensional micro-jet free-formation technology.
- the computer-aided design is used to make the pre-designed three-dimensional model according to the program. It is very precise and flexible. It can change the size of the bracket mesh and the bracket according to different requirements. The thickness and the length of the slider, etc., and the convenient loading of the drug, the manufacturing process is simple.
- the size is lmm
- the head of the bracket is an outer frame
- the outer frame is provided with 2-5 buckles
- the two sides of the bracket body are provided with snap teeth.
- the snap-tooth size is 0.1mm and the angle is 30 degrees, facing away from the head of the bracket. Since the small teeth are uniformly distributed on both sides of the entire stent body, the stent can be reasonably adjusted according to the diameter of the implanted portion during use, and the application range is wide.
- the angle of the snap teeth is small, reducing the resistance of the stent during expansion, and the release pressure is slightly smaller, reducing the risk of complications.
- the buckle of the bracket head can be inserted into the mesh of the bracket during use, which can ensure a strong and uniform supporting force of the bracket.
- the PDO double-buckle bracket is also equipped with a matching stent delivery system to make the procedure easier.
- the delivery device consists of an outer cannula 3, an inner sheath 4 and a balloon catheter 5, the structure of which is shown in FIG.
- the outer sleeve 3 has a proximal end, a distal end, and an inner lumen extending between the ends.
- the inner sheath tube 4 also has a proximal end, a distal end and an inner cavity extending between the two ends.
- the outer diameter of the inner sheath tube 4 is adapted to be slidably inserted into the outer sleeve 3 cavity, and the inner sheath tube 4 is longer than the outer sleeve 3. About 4-6cm.
- the balloon catheter 5 also has a proximal end, a distal end and an inner lumen, the outer diameter of the balloon catheter 5 being adapted to be slidably inserted into the lumen of the inner sheath tube 4.
- the distal end of the balloon catheter 5 is a cone 52 and a balloon 51.
- the length and diameter of the balloon 51 can be selected according to the requirements of the stent.
- a metal marker is placed on each end of the balloon 51 to aid in positioning of the stent.
- the delivery device also includes two Y-adapters, one Y-adapter 41 disposed adjacent the inner sheath 4 and in communication with its lumen; and another Y-adapter 31 disposed at the proximal end of the outer cannula 3 in communication with its lumen.
- the function of the two Y-type adapters is to inject and aspirate the desired fluid into the lumen during delivery of the slider bracket, respectively.
- the stent By clamping the stent on the balloon 51, being fixed between the distal cone 52 of the balloon 51 and the proximal inner sheath 4, the stent can be prevented from being displaced; and the outer surface of the stent is sleeved in the outer sleeve 3, Prevent the outer layer of the stent from unfolding.
- the stent-equipped delivery device is delivered along the guide wire to the stenotic vessel, and according to the metal marker on the balloon 51, after accurate positioning, the outer cannula 3 is withdrawn, and then the balloon is placed. 5 Inflated, the stent is then expanded and adhered to the inner wall of the narrow blood vessel. Then, the inner sheath tube 4 and the outer sleeve 3 are removed together to complete the stent implantation.
- Anesthesia Fasting one day before surgery, ketamine 8-10mg/Kg intramuscular injection for anesthesia induction, atropine 0.02mg/Kg intramuscular injection, and then establish a venous access. Immediately after intravenous injection of 2 mg/Kg of succinylcholine chloride, the animals were given a tracheal intubation, ventilator assisted ventilation, and ECG monitoring. Fentanyl 2ug/Kg, ketamine 2mg/Kg and Wankesson 0.1mg/Kg were administered intermittently.
- Intervention success rate refers to the successful expansion and release of the stent at the target site, no stent shedding, displacement, vascular tear, large out Other complications such as blood.
- Complication rate refers to vascular tears, major bleeding, arterial perforation, death, etc. caused by stent and delivery system stents.
- Target vessel diameter after stent implantation The computer measures the average value of the proximal, middle, and distal measurements of the stent.
- Reference vessel diameter at both ends of the stent The reference vessel diameter at 0.5 cm outside the stent vessel was measured three times to obtain an average value, and the reference vessel diameters at both ends were added and averaged.
- the experimental pigs were sacrificed 1 month, 3 months, and 6 months after operation.
- HE staining was performed on the two ends of the stent and the middle part and the margin of the stent.
- the inflammatory reaction in the stent and the surrounding area, the growth of the granulation tissue, and the endothelium on the stent surface were observed. Growth, degradation of the scaffold, etc.
- the stent was taken out together with 0.5 mm long vascular tissue at both ends to prepare specimens, and the degree of endothelialization of the stent was observed by scanning electron microscopy. Third, the results
- the characteristics of the new slide fastener stent implantation are shown in Table 13.
- the stent implantation success rate was 88.90%, the delivery system delivery success rate was 93.30%, and the complication rate was 11.10%.
- Table 13 shows that there is no significant change in the diameter of the target vessel lumen after one month of stenting and immediately after implantation, ⁇ >0.05, no statistical significance; but the lumen diameter is lost at three months and six months after surgery. The lumen was reduced, compared with one month after implantation and one month after surgery, ⁇ 0.01, there was a statistically significant difference. However, there was no significant change in lumen diameter between the three months and six months after surgery, ⁇ >0.05, which was not statistically significant.
- the bioabsorbable PDO stent has been covered by endothelial cells, the stent rod remains intact and rarely degraded; a small amount of inflammatory cells infiltrate around the stent, and the inflammatory cells are mainly lymphocytes, plasma cells and eosinophils.
- the surface of the bioabsorbable PDO scaffold is dense and mature, the scaffold rod structure is destroyed, and some of it has been degraded; there are still inflammatory cells around the scaffold rod, and the inflammatory cells are mainly composed of lymphocytes and eosinophils. Multi-foreign macrophages.
- stent rods Six months after stenting: Most of the stent rods have been degraded; there are still a small number of inflammatory cells around the stent.
- the inflammatory cells are mainly foreign body macrophages, lymphocytes and plasma cells.
- the inflammatory cells gradually Reduced, the stent blood vessels gradually return to normal blood vessels.
- the biodegradable PDO stent was implanted into the porcine iliac artery. Visual observation showed that the stent surface was covered with a thin endometrial covering at 1 month. At 3 months, the stent was covered by the neointimal. At 6 months, the stent surface was smooth. And shiny neointimal. Scanning electron microscopy showed that the stent had been sparsely covered by endothelial cells at one month. At 3 months, the endothelial cells had been densely covered, and the intact endometrium had formed at 6 months, indicating that the stent had good cell compatibility. 3 degradability
- the stent rod At one month after operation, the stent rod remained intact and rarely degraded. At 3 months, the stent rod structure was destroyed, and some of the stent rods had been degraded. At 6 months, most of the stent rods had degraded; this indicates that the PDO stent has better degradability.
- the bioabsorbable PDO slider-type stent is successfully implanted into the porcine iliac artery through the delivery system, which is technically feasible; the stent and delivery system have a good success rate and a low complication rate, and the design is feasible; the PDO stent is short-term ( One month) has good curative effect, the diameter of the middle blood vessel is lost, mainly caused by intimal hyperplasia, but the blood vessels still maintain a good opening; with the degradation of the scaffold, the inflammatory cells aggregate, but as the material gradually degrades, inflammation The reaction will also gradually disappear; the PDO scaffold has a complete coverage of endothelial cells for one month and has good cell compatibility; the PDO scaffold has been degraded for most of 6 months and has good degradability.
- the ratio of stent diameter to vessel diameter is required to be 1.10- 1.20:1;
- the balloon is sucked back into a negative pressure, the balloon is withdrawn, and the delivery system is completely withdrawn along the guide wire.
- Acute elastic retraction rate of stent (diameter when stent is fully expanded - diameter of stent after balloon removal y diameter when stent is fully expanded).
- the PDO edge slider type bracket can be released under normal release pressure (10-15 atm), the bracket can be successfully buckled, no bracket curls into the lumen; the bracket basically maintains the preset tube
- the lumen diameter has an extremely low acute elastic retraction rate (2%). Prove that this bracket design operation is feasible.
- Anesthesia Fasting one day before surgery, ketamine 8-10mg/Kg intramuscular injection for anesthesia induction, atropine 0.02mg/Kg intramuscular injection, and then establish a venous access. Immediately after intravenous injection of 2 mg/Kg of succinylcholine chloride, the animals were given a tracheal intubation, ventilator assisted ventilation, and ECG monitoring. Fentanyl 2ug/Kg, ketamine 2mg/Kg and Wankesson 0.1mg/Kg were administered intermittently.
- the balloon is sucked into a negative pressure, the balloon is withdrawn, and the delivery system is completely withdrawn along the guide wire.
- Acute elastic retraction rate of stent (diameter when stent is fully expanded - diameter of stent after balloon removal y diameter when stent is fully expanded).
- the PDO double-buckle bracket can be released under normal release pressure (10-14atm), the stent can be successfully buckled, no stent is curled into the lumen; the stent basically maintains the preset lumen Diameter, with very low acute elastic retraction rate (2%). Prove that this bracket design operation is feasible.
- Atropine 0.02mg/kg intramuscular injection was given 30min before operation, and pigs were anesthetized with chloramphenicol 10mg/Kg and placed on the operating table for fixation.
- PDO edge slider bracket (stent length 20mm* stent diameter 8-12mm) 4, guide wire, stent delivery system and pressure pump, 4 esophageal stenosis experimental pigs, the original esophageal diameter of the experimental pig is 10 ⁇ 2mm, The diameter of the esophageal cavity after modeling was 6 ⁇ 0.5 mm.
- the delivery system loaded with the PDO slider bracket is placed along the guide wire through the mouth of the esophage target site, and the stent is accurately positioned after 15 atm*30 seconds;
- the balloon is sucked back into a negative pressure, the balloon is withdrawn, and the delivery system is completely withdrawn along the guide wire.
- Acute elastic retraction rate of stent (diameter when stent is fully expanded - diameter of stent after balloon removal y diameter when stent is fully expanded).
- the PDO edge slider type bracket can be released under normal release pressure (13-17atm), the bracket can be successfully buckled, no bracket curls into the lumen; the bracket basically maintains the preset tube
- the lumen diameter has an extremely low acute elastic retraction rate (2%). Prove that this bracket design operation is feasible.
- PDO double-buckle bracket (stent length 20mm * stent diameter 15mm) 4 each, multi-functional catheter, guide wire, stent delivery system and pressure pump, tracheal stenosis experimental pig 4, experimental pig original tracheal diameter 14 ⁇ 1.5mm, the lumen diameter after modeling is 7 ⁇ lmm.
- the multi-functional catheter is fitted with the super-sliding guide wire through the glottis into the trachea, and then the metal-reinforced guide wire is replaced.
- the guide wire is placed at the distal end of the stenosis segment and the catheter is removed;
- the stented delivery system is delivered along the guidewire to the stenosis section, 14atm*30 seconds to expand the balloon release stent; the balloon is returned to a negative pressure, the balloon is withdrawn, and the delivery system is withdrawn along the guidewire.
- Acute elastic retraction rate of stent (diameter when stent is fully expanded - diameter of stent after balloon removal y diameter when stent is fully expanded).
- the PDO double-buckle bracket can be released under normal release pressure (12-14 atm), the stent can be successfully buckled, no stent curls into the lumen; the stent basically maintains the preset lumen Diameter, with very low acute elastic retraction rate (3%). Prove that this bracket design operation is feasible.
- the arc bifurcation was separated into the abdomen through the arc-shaped incision under the right upper abdomen margin.
- the local stenosis was used to narrow the common bile duct by 50%, and the abdomen was sutured layer by layer. Postoperative routine antibiotic treatment.
- the PDO intermediate slide-type stent is implanted into the experimental porcine biliary cavity
- PDO intermediate slide type bracket (bracket length 25 mm * bracket diameter 6-8 mm) 4 each, rubber hose, stent delivery system and pressure pump, biliary stenosis test pig 4, experimental pig original biliary lumen diameter 7.5 ⁇ 0.5mm, biliary diameter 4 ⁇ 0.3mm after modeling.
- the balloon is sucked back into a negative pressure, the balloon is withdrawn, and the delivery system is completely withdrawn along the guide wire.
- Acute elastic retraction rate of stent (diameter when stent is fully expanded - diameter of stent after balloon removal y diameter when stent is fully expanded).
- the PDO intermediate slide-type bracket can be released under normal release pressure (12-14 atm), the stent can be successfully buckled, no stent is curled into the lumen; the stent basically maintains a preset tube
- the lumen diameter has an extremely low acute elastic retraction rate (3%). Prove that this bracket design operation is feasible.
- PDO edge slider type bracket (stent length 20 mm* bracket diameter 10 mm) 4 each, guide wire, Rubber hose, stent delivery system and pressure pump, urethral stricture test dogs, experimental dog original urethral cavity diameter of 10-12mm, urethral cavity diameter after modeling is 5-6mm.
- the balloon is sucked back into a negative pressure, the balloon is withdrawn, and the delivery system is completely withdrawn along the guide wire.
- Acute elastic retraction rate of stent (diameter when stent is fully expanded - diameter of stent after balloon removal y diameter when stent is fully expanded).
- the PDO edge slider type bracket can be released under normal release pressure (10-14 atm), the bracket can be successfully buckled, no bracket curls into the lumen; the bracket basically maintains the preset tube
- the lumen diameter has an extremely low acute elastic retraction rate (5%). Prove that this bracket design operation is feasible.
- the balloon is sucked back into a negative pressure, the balloon is withdrawn, and the delivery system is completely withdrawn along the guide wire.
- Acute elastic retraction rate of stent (diameter when stent is fully expanded - diameter of stent after balloon removal y diameter when stent is fully expanded).
- the PDO intermediate slide-type bracket can be released under normal release pressure (10-14 atm), the stent can be successfully buckled, no stent is curled into the lumen; the stent basically maintains the preset tube
- the lumen diameter has an extremely low acute elastic retraction rate (5%). Prove that this bracket design operation is feasible.
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Description
Claims
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
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EP10859489.6A EP2638883A4 (en) | 2010-11-12 | 2010-11-12 | BIOABSORBABLE ENDOPROTHESIS WITH ZIP AND APPLICATION THEREOF |
PCT/CN2010/078664 WO2012061992A1 (zh) | 2010-11-12 | 2010-11-12 | 一种滑扣生物可吸收支架及其应用 |
JP2013535239A JP2014500048A (ja) | 2010-11-12 | 2010-11-12 | 一種新型のスライド・ロック式生体吸収性ステント及びその使用 |
US13/881,813 US20130226277A1 (en) | 2010-11-12 | 2010-11-12 | Slide fastener bioabsorbable stent and application thereof |
Applications Claiming Priority (1)
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PCT/CN2010/078664 WO2012061992A1 (zh) | 2010-11-12 | 2010-11-12 | 一种滑扣生物可吸收支架及其应用 |
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WO2012061992A1 true WO2012061992A1 (zh) | 2012-05-18 |
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PCT/CN2010/078664 WO2012061992A1 (zh) | 2010-11-12 | 2010-11-12 | 一种滑扣生物可吸收支架及其应用 |
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US (1) | US20130226277A1 (zh) |
EP (1) | EP2638883A4 (zh) |
JP (1) | JP2014500048A (zh) |
WO (1) | WO2012061992A1 (zh) |
Families Citing this family (5)
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US9415137B2 (en) * | 2012-08-22 | 2016-08-16 | Biomet Manufacturing, Llc. | Directional porous coating |
WO2016176444A1 (en) | 2015-04-29 | 2016-11-03 | Northwestern University | 3d printing of biomedical implants |
WO2018160454A1 (en) * | 2017-02-28 | 2018-09-07 | University Of Florida Research Foundation, Inc. | Controlling esophageal temperature during cardiac ablation |
EP3332730B1 (de) * | 2017-08-08 | 2021-11-03 | Siemens Healthcare GmbH | Verfahren und trackingsystem zum nachverfolgen eines medizinischen objekts |
CN114504412A (zh) * | 2022-01-27 | 2022-05-17 | 深圳市顺美医疗股份有限公司 | 一种密网支架及其制备方法 |
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US20030055495A1 (en) * | 2001-03-23 | 2003-03-20 | Pease Matthew L. | Rolled minimally-invasive heart valves and methods of manufacture |
CN101247778A (zh) * | 2006-06-20 | 2008-08-20 | 雷瓦医药公司 | 滑动锁紧支架 |
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US3005A (en) * | 1843-03-17 | Power-loom | ||
US5266073A (en) * | 1987-12-08 | 1993-11-30 | Wall W Henry | Angioplasty stent |
DE29705218U1 (de) * | 1997-03-13 | 1997-05-15 | Koeppen, Kai-Igor, Dipl.-Industrialdesigner, 38304 Wolfenbüttel | Teilmantel-Gefäßstütze zur medizinischen Behandlung von verengten Gefäßen, insbesondere Gefäßarealen mit Gefäßabzweig |
US6083258A (en) * | 1998-05-28 | 2000-07-04 | Yadav; Jay S. | Locking stent |
US9149378B2 (en) * | 2005-08-02 | 2015-10-06 | Reva Medical, Inc. | Axially nested slide and lock expandable device |
US20070162110A1 (en) * | 2006-01-06 | 2007-07-12 | Vipul Bhupendra Dave | Bioabsorbable drug delivery devices |
US8585753B2 (en) * | 2006-03-04 | 2013-11-19 | John James Scanlon | Fibrillated biodegradable prosthesis |
US20100122698A1 (en) * | 2008-11-19 | 2010-05-20 | The Nemours Foundation | Neonatal airway stent |
US8864811B2 (en) * | 2010-06-08 | 2014-10-21 | Veniti, Inc. | Bi-directional stent delivery system |
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2010
- 2010-11-12 EP EP10859489.6A patent/EP2638883A4/en not_active Withdrawn
- 2010-11-12 JP JP2013535239A patent/JP2014500048A/ja active Pending
- 2010-11-12 US US13/881,813 patent/US20130226277A1/en not_active Abandoned
- 2010-11-12 WO PCT/CN2010/078664 patent/WO2012061992A1/zh active Application Filing
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US20030055495A1 (en) * | 2001-03-23 | 2003-03-20 | Pease Matthew L. | Rolled minimally-invasive heart valves and methods of manufacture |
CN101262835A (zh) * | 2005-08-02 | 2008-09-10 | 雷瓦医药公司 | 轴向嵌套的滑动-锁止膨胀装置 |
CN101484195A (zh) | 2006-04-27 | 2009-07-15 | 菲利浦塑料公司 | 复合支架 |
CN101247778A (zh) * | 2006-06-20 | 2008-08-20 | 雷瓦医药公司 | 滑动锁紧支架 |
CN201727614U (zh) * | 2010-02-22 | 2011-02-02 | 上海交通大学医学院附属新华医院 | 新型滑扣生物可吸收支架 |
Non-Patent Citations (1)
Title |
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See also references of EP2638883A4 |
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US20130226277A1 (en) | 2013-08-29 |
EP2638883A4 (en) | 2014-10-08 |
EP2638883A1 (en) | 2013-09-18 |
JP2014500048A (ja) | 2014-01-09 |
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