CN114010367A - Artificial blood vessel with variable supporting force - Google Patents

Artificial blood vessel with variable supporting force Download PDF

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Publication number
CN114010367A
CN114010367A CN202111493268.XA CN202111493268A CN114010367A CN 114010367 A CN114010367 A CN 114010367A CN 202111493268 A CN202111493268 A CN 202111493268A CN 114010367 A CN114010367 A CN 114010367A
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CN
China
Prior art keywords
degradable
blood vessel
film
artificial blood
anchoring
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Pending
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CN202111493268.XA
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Chinese (zh)
Inventor
王宇飞
王沛
刘静怡
王书晗
曹苹
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Dk Medical Technology Co ltd
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Dk Medical Technology Co ltd
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Priority to CN202111493268.XA priority Critical patent/CN114010367A/en
Publication of CN114010367A publication Critical patent/CN114010367A/en
Pending legal-status Critical Current

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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
    • A61F2/02—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
    • 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
    • A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
    • A61F2250/0039—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in diameter

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  • Health & Medical Sciences (AREA)
  • Gastroenterology & Hepatology (AREA)
  • Pulmonology (AREA)
  • Cardiology (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Transplantation (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Prostheses (AREA)

Abstract

The invention provides an artificial blood vessel with variable supporting force, which comprises a first fixing device, an artificial blood vessel body and a second fixing device which are sequentially communicated. Compared with the prior art, the artificial blood vessel fixing device provided by the invention can provide different supporting forces at different use stages, and has effective fixing and flexibility, the fixing end has a quick anchoring function and can be quickly connected with blood vessel tissues, the middle artificial blood vessel body structure has excellent bending resistance, a bypass pipeline can be quickly provided at an embolism position, the operation time is shortened, the burden of a doctor is reduced, and the operation risk is reduced.

Description

Artificial blood vessel with variable supporting force
Technical Field
The invention belongs to the technical field of artificial blood vessels, and particularly relates to an artificial blood vessel with variable supporting force.
Background
Cardiovascular disease is the most fatal cause of global fatality, and vascular bypass grafting is considered to be the best choice for patients in need of long-term maintenance of revascularization. The autologous blood vessels are the most ideal donor for the blood vessel transplantation, but the wide application of the autologous blood vessel transplantation is greatly limited due to the small source of the autologous blood vessels and the traumatic damage to the incisional sites, so that the artificial blood vessels become a substitute for a plurality of severely-narrow or occlusive blood vessels. At present, artificial blood vessels are mostly made of nylon, terylene, polytetrafluoroethylene and other polymer synthetic materials, are suitable for replacing and reconstructing blood vessels at all parts of the whole body, and have satisfactory clinical effects when being applied to large and medium-caliber artificial blood vessels.
In the traditional surgical technology, when an artificial blood vessel stent transplantation operation is carried out, doctors are required to suture and connect artificial blood vessels at two ends, dozens to hundreds of needles are generally required to be sutured, the anastomosis of simply suturing two artificial blood vessels is required to be more than ten minutes, the operation time is long, and the operation has adverse effects on blood circulation recovery, body health and even life of patients in cardiovascular operations, particularly heart large blood vessel operations. In the prior art, in order to avoid the above problems, many non-suture techniques, such as a magnetic tube method, a blood vessel anastomosis clip, a needle ring method, a blood vessel adhesive, etc., have appeared, but these non-suture techniques generally require a large amount of auxiliary tools to complete the blood vessel anastomosis, and the anastomosis effect is not good.
Chinese patent application No. CN200620148225.2 discloses a complex of an artificial blood vessel and an artificial stent blood vessel, comprising: the artificial blood vessel is positioned at the front half part and the artificial stent blood vessel is positioned at the back half part, the joint of the artificial blood vessel and the artificial stent blood vessel is a sleeve-shaped suture edge to shorten the time of deep low temperature and loop stopping in an operation, so that the injury of a patient is relieved, the recovery of the patient is promoted, and the artificial stent blood vessel is directly implanted into an aortic arch and a descending aorta under the condition of deep low temperature and loop stopping, so that the circulation is recovered as soon as possible, but the implantation mode is the same as that of the traditional artificial blood vessel, and the rapid connection with the blood vessels at two ends cannot be realized.
Chinese patent application No. CN201510998350.6 discloses a simple artificial blood vessel quick connection structure, which comprises an artificial blood vessel, a connection ring is nested outside one side of the artificial blood vessel, and a threading hole is arranged on the circumferential side wall of the connection ring. The product is connected with other artificial blood vessels through threading holes on the circumferential side wall, although the connection efficiency is improved, the connection is still completed through a mode of sewing for many times, and the problem of quick connection cannot be effectively solved.
Chinese patent application No. CN202011474495.3 discloses a method for preparing a self-anastomotic artificial blood vessel stent, which provides a double-layered stent composed of an intravascular inner-layer stent and an intravascular intermediate-layer stent, wherein an anastomotic sleeve with the same inner diameter as the intravascular inner-layer stent is extruded and printed at both ends of the double-layered stent by using a shape memory material, and the deformation of the anastomotic sleeve can be controlled by changing the external temperature, so that the purpose of self-anastomosing the artificial blood vessel and the autologous blood vessel is realized, but the connection of both ends is easy to fall off, and the reliability is poor.
Chinese patent application No. CN201420060256.7 discloses an intra-arterial stent prosthesis mainly used for repairing arterial blood vessels, which mainly comprises two parts, namely a prosthesis and a stent, wherein the prosthesis is a fabric with a grid structure, and the prosthesis and the stent are mutually fixed. But the product can only be used in the arterial lumen and cannot establish a bypass vascular channel.
Chinese patent application No. CN201621374148.2 discloses an artificial vascular system, which comprises an artificial blood vessel, a fixing line and two delivery rods, wherein the delivery rods are all located in the artificial blood vessel, and one ends of the two delivery rods, which are provided with protection valves, respectively extend out from the outlets of the two delivery rods, and the tapered ends of the two delivery rods respectively extend out from anchoring umbrella parts at both ends of the artificial blood vessel; one end of the fixing wire is bound with the anchoring umbrella part, and the anchoring umbrella part is gradually opened when the fixing wire is loosened. This product structure complicacy complex operation, and still need water injection leak protection in the leak protection bag at both ends when anchoring umbrella portion opens, increase doctor's burden and reduce the apparatus reliability.
Disclosure of Invention
In view of the above, the present invention provides an artificial blood vessel with variable supporting force, which can be connected to the vascular tissue quickly.
The invention provides an artificial blood vessel with variable supporting force, which comprises a first fixing device, an artificial blood vessel body and a second fixing device which are sequentially communicated;
the first fixing device comprises a first tectorial tubular stent and a first wrapping structure wrapped outside the first tectorial tubular stent;
the first tectorial tubular stent comprises a first support structure, a first macromolecule inner tectorial membrane arranged on the inner wall of the first support structure and a first macromolecule outer tectorial membrane arranged on the outer wall of the first support structure;
the second fixing device comprises a second film-coated tubular stent and a second wrapping structure wrapping the second film-coated tubular stent;
the second film-coated tubular stent comprises a second supporting structure, a second macromolecule inner film and a second macromolecule outer film, wherein the second macromolecule inner film is arranged on the inner wall of the second supporting structure, and the second macromolecule outer film is arranged on the outer wall of the second supporting structure;
the first support structure and the second support structure each independently comprise a degradable support portion and a non-degradable support portion.
Preferably, the diameter of one end, connected with the artificial blood vessel body, of the first coated tubular stent in a relaxed state is the same as that of the artificial blood vessel body, and the diameter of one end, far away from the artificial blood vessel body, of the first coated tubular stent is 1-3 times of that of the artificial blood vessel body;
the diameter of one end of the second tectorial membrane tubular stent, which is connected with the human blood vessel body in a relaxed state, is the same as that of the artificial blood vessel body, and the diameter of one end far away from the artificial blood vessel body is 1-3 times of that of the artificial blood vessel body.
Preferably, the first film-coated tubular scaffold comprises a connecting region and an anchoring region, and a raised barb structure is arranged on the first supporting structure of the anchoring region;
the second film-coated tubular bracket comprises a connecting area and an anchoring area, and a second supporting structure of the anchoring area is provided with a raised barb structure;
the height of barb structure is 0.1 ~ 3 mm.
Preferably, the connecting area of the first film-coated tubular stent is formed by weaving degradable wires and non-degradable wires; or the annular nondegradable support parts and the annular degradable support parts are alternately arranged along the length direction of the first film-coated tubular stent;
the connecting area of the second film-coated tubular stent is formed by weaving degradable filaments and non-degradable filaments; or the annular nondegradable support parts and the annular degradable support parts are alternately arranged along the length direction of the second film-coated tubular stent.
Preferably, the anchoring area of the first film-coated tubular stent comprises a strip-shaped non-degradable supporting part and a ring-shaped degradable supporting part which are arranged in an extending way along the length direction of the first film-coated tubular stent;
the anchoring area of the first film-coated tubular stent comprises a strip-shaped non-degradable supporting part and an annular degradable supporting part which are arranged in an extending way along the length direction of the first film-coated tubular stent;
the anchoring area of the second tectorial tubular stent comprises a strip-shaped non-degradable supporting part and an annular degradable supporting part which are arranged in an extending way along the length direction of the second tectorial tubular stent;
the anchoring area of the second tectorial tubular stent comprises a strip-shaped non-degradable supporting part and an annular degradable supporting part which are arranged in an extending way along the length direction of the second tectorial tubular stent; .
Preferably, the anchoring area of the first film-coated tubular stent further comprises a strip-shaped degradable supporting part which is arranged along the length direction of the first film-coated tubular stent in an extending way; the strip-shaped degradable support parts are arranged between two adjacent strip-shaped non-degradable support parts;
the anchoring area of the second tectorial tubular stent also comprises a strip-shaped degradable supporting part which is arranged along the length direction of the second tectorial tubular stent in an extending way; the strip-shaped degradable support parts are arranged between two adjacent strip-shaped non-degradable support parts.
Preferably, the anchoring zone of the first stent-graft is of a single-layer structure or a double-layer structure; when the anchoring area is of a single-layer structure, a raised barb structure is arranged on the outer surface of the first supporting structure of the anchoring area; when the anchoring area is of a double-layer structure, the anchoring area comprises an outer anchoring area and an inner anchoring area; the inner surface of the outer anchoring area is provided with a raised barb structure; the outer surface of the inner side anchoring area is provided with a raised barb structure;
the anchoring area of the second film-coated tubular bracket is of a single-layer structure or a double-layer structure; when the anchoring area is of a single-layer structure, a raised barb structure is arranged on the outer surface of the second supporting structure of the anchoring area; when the anchoring area is of a double-layer structure, the anchoring area comprises an outer anchoring area and an inner anchoring area; the inner surface of the outer anchoring area is provided with a raised barb structure; the surface in inboard anchor region is provided with bellied barb structure.
Preferably, when the anchoring area of the first film-coated tubular scaffold is of a single-layer structure, a hole-shaped structure is arranged at the position of the first macromolecule outer film corresponding to the barb structure, and the barb structure is exposed through the hole-shaped structure;
when the anchoring area of the first film-coated tubular bracket is of a double-layer structure, the position of the first macromolecule inner film of the outer anchoring area, which corresponds to the barb structure, is provided with a hole-shaped structure, and the barb structure is exposed through the hole-shaped structure; the first macromolecule outer covering film of the inner side anchoring area is provided with a hole-shaped structure corresponding to the barb structure, and the barb structure is exposed through the hole-shaped structure;
when the anchoring area of the second film-coated tubular bracket is of a single-layer structure, a hole-shaped structure is arranged at the position of the second macromolecule outer film corresponding to the barb structure, and the barb structure is exposed through the hole-shaped structure;
when the anchoring area of the second film-coated tubular bracket is of a double-layer structure, the position of the second macromolecule inner film of the outer anchoring area, which corresponds to the barb structure, is provided with a hole-shaped structure, and the barb structure is exposed through the hole-shaped structure; the position that the tectorial membrane is provided with the poroid structure corresponding to the barb structure outside the second polymer of inboard anchoring zone, exposes the barb structure through the poroid structure.
Preferably, the area ratio of the degradable support part to the non-degradable support part of the first support structure is 1: (0.5-2).
Preferably, the thicknesses of the first support structure and the second support structure are respectively and independently 0.1-1.2 mm; the thicknesses of the first macromolecule inner coating film, the first macromolecule outer coating film, the second macromolecule inner coating film and the second macromolecule outer coating film are respectively 0.02-0.5 mm independently.
The invention provides an artificial blood vessel with variable supporting force, which comprises a first fixing device, an artificial blood vessel body and a second fixing device which are sequentially communicated; the first fixing device comprises a first tectorial tubular stent and a first wrapping structure wrapped outside the first tectorial tubular stent; the first tectorial tubular stent comprises a first support structure, a first macromolecule inner tectorial membrane arranged on the inner wall of the first support structure and a first macromolecule outer tectorial membrane arranged on the outer wall of the first support structure; the second fixing device comprises a second film-coated tubular stent and a second wrapping structure wrapping the second film-coated tubular stent; the second film-coated tubular stent comprises a second supporting structure, a second macromolecule inner film and a second macromolecule outer film, wherein the second macromolecule inner film is arranged on the inner wall of the second supporting structure, and the second macromolecule outer film is arranged on the outer wall of the second supporting structure; the first support structure and the second support structure each independently comprise a degradable support portion and a non-degradable support portion. Compared with the prior art, the artificial blood vessel fixing device provided by the invention can provide different supporting forces at different use stages, and has effective fixing and flexibility, the fixing end has a quick anchoring function and can be quickly connected with blood vessel tissues, the middle artificial blood vessel body structure has excellent bending resistance, a bypass pipeline can be quickly provided at an embolism position, the operation time is shortened, the burden of a doctor is reduced, and the operation risk is reduced.
Drawings
FIG. 1 is a schematic structural diagram of an artificial blood vessel with variable supporting force provided by the present invention;
FIG. 2 is a schematic view of a wrap structure provided by the present invention;
FIG. 3 is a schematic view of the package structure opening process;
FIG. 4 is a schematic view of the flare shape of the covered tubular stent provided by the present invention;
FIG. 5 is a schematic view of a partial structure of an artificial blood vessel provided by the present invention;
FIG. 6 is a schematic view of a partial structure of an artificial blood vessel provided by the present invention;
FIG. 7 is a schematic view of a partial structure of an artificial blood vessel provided by the present invention;
FIG. 8 is a schematic view of the connection of the anchoring region of the artificial blood vessel to the vascular tissue when the anchoring region is a single layer;
FIG. 9 is a schematic view of the connection of the anchoring region of the artificial blood vessel with the vascular tissue when the anchoring region is a double layer;
FIG. 10 is a schematic view of the connection of the anchoring region of the artificial blood vessel with the vascular tissue when the anchoring region is a bilayer according to the present invention.
Detailed Description
The technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the embodiments of the present invention, and it is obvious that the described embodiments are only a part of the embodiments of the present invention, and not all of the embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.
The invention provides an artificial blood vessel with variable supporting force, which comprises a first fixing device, an artificial blood vessel body and a second fixing device which are sequentially communicated;
the first fixing device comprises a first tectorial tubular stent and a first wrapping structure wrapped outside the first tectorial tubular stent;
the first tectorial tubular stent comprises a first support structure, a first macromolecule inner tectorial membrane arranged on the inner wall of the first support structure and a first macromolecule outer tectorial membrane arranged on the outer wall of the first support structure;
the second fixing device comprises a second film-coated tubular stent and a second wrapping structure wrapping the second film-coated tubular stent;
the second film-coated tubular stent comprises a second supporting structure, a second macromolecule inner film and a second macromolecule outer film, wherein the second macromolecule inner film is arranged on the inner wall of the second supporting structure, and the second macromolecule outer film is arranged on the outer wall of the second supporting structure;
the first support structure and the second support structure each independently comprise a degradable support portion and a non-degradable support portion.
Referring to fig. 1, fig. 1 is a schematic structural view of an artificial blood vessel with variable supporting force provided by the present invention, wherein 100 is an artificial blood vessel body, 200 is a covered tubular stent, 300 is a wrapping structure, and 320 is a pull wire.
The fixing device of the artificial blood vessel provided by the invention can realize effective connection and fixation with the blood vessel while realizing variable supporting force by matching the self-expandable and wrapping structures, can realize reliable fixation during implantation by matching the degradable material and the non-degradable material, and can reduce stimulation to the tissue by gradual degradation of the degradable material along with gradual healing of the tissue in the later stage, improve the flexibility of the blood vessel and prevent tissue hyperplasia in the blood vessel and restenosis of the blood vessel; moreover, the artificial blood vessel provided by the invention has good flexibility, bending resistance and good anchoring function.
The artificial blood vessel provided by the invention comprises an artificial blood vessel body; the outer diameter of the artificial blood vessel body is preferably 3-24 mm, and more preferably 5-20 mm; the outer surface of the artificial blood vessel body is preferably provided with corrugated bulges so that the blood vessel body structure has good flexibility and biocompatibility; the artificial blood vessel body is preferably formed by one or more of nylon, terylene, polyurethane, PTFE (polytetrafluoroethylene), EPTFE (porous polytetrafluoroethylene) and natural mulberry silk; the artificial blood vessel body can be woven by the materials, and the inner surface of the artificial blood vessel body is coated with the coating formed by the high polymer materials.
Two ends of the artificial blood vessel body are respectively communicated with the first fixing device and the second fixing device; the first fixing device and the second fixing device can be connected with the artificial blood vessel body through one or more of sewing, bonding and hot pressing.
The first fixing device comprises a first tectorial tubular stent and a first wrapping structure wrapping the first tectorial tubular stent. Wherein the outer diameter of the first wrapping structure is preferably smaller than the outer diameter of the artificial blood vessel body; the first wrapping structure is preferably a cylindrical high-polymer braided structure, is further preferably one or more braided structures of nylon, terylene, polyurethane and natural silk, wraps the first coating bracket and enables the first coating bracket of the self-expansion structure to keep a compressed state; the first wrapping structure is provided with a pull wire along the axial direction, the first coating structure wraps the first film-coated bracket through the pull wire, and the free end of the pull wire is positioned at one end far away from the artificial blood vessel body; when the pull wire is pulled away, the first wrapping structure is gradually opened from the end face, so that the first covered stent is gradually opened from the end face to the middle. Referring to fig. 2 and 3, fig. 2 is a schematic view of a wrapping structure provided by the present invention, and fig. 3 is a schematic view of an opening process of the wrapping structure, in which 310 is a cylindrical polymer woven fabric, 311 is an unopened region of the cylindrical polymer woven fabric, 312 is an opened region of the cylindrical polymer woven fabric, and 320 is a pull wire. Tectorial membrane support is for expanding the structure certainly, is wrapped up by parcel structure before the use, and the structural stay wire that is equipped with of parcel, when fixing device reachs predetermined position, will act as go-between and take out, and tectorial membrane support is gradually opened to being fixed in the vascular wall completely to middle zone by the terminal surface this moment, provides effective smooth and easy bypass route for blood, connects effective reliable easy operation swiftly, effectively reduces the damage to blood vessel, improves the operation success rate.
For convenience of description, in the present invention, the structure in a relaxed state is described below for both the first stent-graft and the second stent-graft unless otherwise specified.
In the invention, the diameter of the first tectorial membrane tubular stent at one end connected with the artificial blood vessel body in a relaxed state is directly the same as that of the artificial blood vessel body so as to facilitate better connection, and the diameter of one end far away from the artificial blood vessel body is preferably 1-3 times, more preferably 1-2.5 times, still more preferably 1.1-2 times and most preferably 1.1-1.5 times of the diameter of the artificial blood vessel body; in some embodiments provided by the present invention, the diameter of the end of the first stent graft distal to the artificial blood vessel body is preferably 1.14 times, 1.25 times, 1.4 times or 1.5 times the diameter of the artificial blood vessel body. Because the diameter of one end far away from the artificial blood vessel body is larger than that of the other end, the end, far away from the artificial blood vessel body, of the first coating tubular body is in a horn mouth shape. Referring to fig. 4, fig. 4 is a schematic view of the flare shape of the tubular stent graft provided by the present invention.
The first tectorial membrane tubular stent comprises a first support structure, a first macromolecule inner tectorial membrane arranged on the inner wall of the first support structure and a first macromolecule outer tectorial membrane arranged on the outer wall of the first support structure.
In the invention, the thickness of the first support structure is preferably 0.1-1.2 mm; the first support structure is formed by cutting a tube and/or weaving wires; the cutting mode is preferably laser cutting; the thickness of the pipe is preferably 0.1-1.2 mm, more preferably 0.2-0.8 mm, and further preferably 0.3-0.4 mm; the diameter of the wire is preferably 0.03-0.5 mm, and more preferably 0.08-0.3 mm; the first support structure comprises a degradable support portion and a non-degradable support portion; the area ratio of the degradable portion to the non-degradable portion is preferably 1: (0.5 to 2); the degradable support portion is preferably formed of a degradable metal and/or a degradable polymer; the degradable metal is preferably one or more of pure magnesium, magnesium-based alloy, iron-based alloy and zinc-based alloy; the degradable polymer is preferably one or more of polylactic acid PLA, L-PLA, polyglycolic acid/polylactic acid copolymer PGLA, polycaprolactone PCL, polyhydroxybutyrate valerate PHBV, polyacetylglutamate PAGA, polyorthoester POE, polyethylene oxide/polybutylene copolymer PEO/PBTP, polylactide-co-caprolactone copolymer PLC and polycyclohexanone PDO; the non-degradable portion is preferably formed of a non-degradable metal, and is further preferably formed of a nickel titanium alloy.
The first stent-graft preferably comprises a connecting region and an anchoring region. Referring to fig. 5 to 7, fig. 5 to 7 are schematic views of partial structures of an artificial blood vessel provided by the present invention, wherein 100 is an artificial blood vessel body, 210 is an anchoring region, 211 is a strip-shaped non-degradable supporting portion, 212 is a strip-shaped degradable supporting portion, 231 and 230 are barb structures, 240 is a non-degradable wire, 241 is a degradable wire, 260 is a polymer coating, 250 is an annular non-degradable supporting portion, and 251 is an annular degradable supporting portion.
The first film-coated tubular stent is connected with the artificial blood vessel body through a connecting area; in the invention, the connecting area is preferably formed by weaving degradable wires and non-degradable wires, or the annular non-degradable supporting part and the annular degradable supporting part are alternately arranged along the length direction of the first film-coated tubular stent; wherein the diameters of the degradable wire and the non-degradable wire are respectively and independently preferably 0.03-0.5 mm, and more preferably 0.08-0.3 mm; the width of the woven grid structure is preferably 1-5 mm, and more preferably 2-3 mm; the height is preferably 1-5 mm, and more preferably 2-3 mm; the annular nondegradable support portion and the annular degradable support portion are further preferably annular nondegradable support portions and annular degradable support portions having a W shape; the "W" shape has good radial elastic function (compression and rebound); the widths of the annular nondegradable support part and the annular degradable support part are respectively and independently 0.3-0.6 mm; the distance between the adjacent annular nondegradable support parts and the annular structures of the annular degradable support parts is preferably 3-6 mm; the joint region having a braided structure or an alternating loop structure has excellent flexibility and bending resistance.
The anchoring area preferably comprises a strip-shaped non-degradable supporting part and a ring-shaped degradable supporting part which are arranged in an extending way along the length direction of the first film-coated tubular stent; the width of the strip-shaped non-degradable supporting part is preferably 0.2-0.4 mm; the strip-shaped non-degradable supporting part is preferably obtained by cutting a non-degradable pipe; the distance between every two adjacent strip-shaped non-degradable supporting parts along the outer surface of the first film-coated tubular bracket is preferably 3-6 mm; the width of the annular degradable support part is preferably 0.3-0.6 mm; the distance between adjacent annular degradable supporting parts is preferably 3-6 mm; the annular degradable support part is preferably an annular degradable support part having a W shape. In order to further improve the flexibility of the artificial blood vessel, the anchoring area of the first film-coated tubular stent preferably further comprises a strip-shaped degradable supporting part which is arranged in an extending way along the length direction of the first film-coated tubular stent; the strip-shaped degradable support parts are arranged between two adjacent strip-shaped non-degradable support parts; the distance between the adjacent strip-shaped degradable supporting parts and the adjacent strip-shaped non-degradable supporting parts is preferably 3-6 mm; the width of the strip-shaped degradable support part is preferably 0.3-0.6 mm; the strip-shaped degradable support part is preferably formed by cutting degradable tubing; in the present invention, the anchoring zone of the first stent-graft preferably further comprises an annular non-degradable support portion; the annular non-degradable support portions are arranged between the annular degradable support portions; the annular non-degradable support portion is preferably an annular non-degradable support portion having a W shape; the width of the annular non-degradable supporting part is preferably 0.3-0.6 mm; the distance between the adjacent annular non-degradable supporting parts and the annular degradable supporting parts is preferably 3-6 mm.
In the invention, the first supporting structure of the anchoring area is preferably provided with a raised barb structure so as to enhance the bonding force between the anchoring area and the vascular tissue; the height of the barb structure is preferably 0.1-3 mm, more preferably 0.2-2 mm, still more preferably 0.2-1 mm, and most preferably 0.3-0.5 mm; the barb structure can be a degradable barb structure or a non-degradable barb structure, and preferably at least comprises the non-degradable barb structure; the degradable barb structures are preferably formed from degradable metals and/or degradable polymers; the degradable metal and the degradable polymer are the same as above, and are not described again; the non-degradable barb structures are preferably formed from a non-degradable metal, and more preferably from a nickel titanium alloy. The anchoring area of the artificial blood vessel provided by the invention can be of a single-layer structure or a double-layer structure; when the anchoring area is of a single-layer structure, the outer surface of the first supporting structure of the anchoring area is preferably provided with a raised barb structure, and the outer surface of the anchoring area is anchored with the inner wall of the vascular tissue; referring to fig. 8, fig. 8 is a schematic view illustrating the connection between the anchoring region of the artificial blood vessel and the vascular tissue when the anchoring region is a single layer, wherein 000 is the vessel wall, 100 is the artificial blood vessel body, 210 is the anchoring region of the single layer, and 230 is a barb structure; when the anchoring area is of a double-layer structure, the structures at the two sides can be the same or different, the two anchoring areas are connected with the artificial blood vessel body through the connecting area, and at the moment, the anchoring area comprises an outer anchoring area and an inner anchoring area; the inner surface of the outer anchoring area is provided with a raised barb structure; the outer surface of the inner side anchoring area is provided with a raised barb structure; after the release, the outer anchoring area is positioned at the outer side of the vascular tissue and attached to the outer side of the vascular tissue wall, and the inner anchoring area is positioned at the inner side of the vascular tissue and attached to the inner side of the vascular tissue wall; referring to fig. 9 and 10, fig. 9 and 10 are schematic views illustrating the connection between the anchoring region of the artificial blood vessel and the vascular tissue when the anchoring region of the artificial blood vessel provided by the present invention is a double layer, wherein 000 is the vessel wall, 100 is the artificial blood vessel body, 220 is the double layer anchoring region, 221 is the outer anchoring region, 222 is the inner anchoring region, 230 and 231 are barb structures, and 260 is a polymer coating.
The inner wall of the first support structure is provided with a first macromolecule inner coating film, and the outer wall of the first support structure is provided with a first macromolecule outer coating film, so that the whole first support structure is coated; the thicknesses of the first macromolecule inner coating film and the second macromolecule outer coating film are respectively and independently preferably 0.02-0.5 mm; the first polymer inner coating film and the second polymer outer coating film are preferably formed of one or more of PTFE (polytetrafluoroethylene), EPTFE (porous polytetrafluoroethylene), FEP (fluorinated ethylene propylene copolymer or perfluoroethylene propylene copolymer), and TPU (thermoplastic polyurethane elastomer rubber), independently. In the present invention, the first inner polymer coating and the first outer polymer coating may be formed by coating or hot pressing on the first support structure, so that the first inner polymer coating, the first support structure and the first outer polymer coating form a coated tubular stent as a whole.
In the invention, further, the surface of the first macromolecule inner covering film and/or the first macromolecule outer covering film corresponding to the barb structure of the anchoring area is preferably provided with a hole-shaped structure so as to expose the barb structure; the barb structure of the first support structure is exposed through the porous structure, so that the rivet can be better riveted with vascular tissues, and the degradation of the degradable part can be accelerated; when the anchoring area of the first film-coated tubular bracket is of a single-layer structure, a hole-shaped structure is arranged at the position of the first macromolecule outer film, which corresponds to the barb structure, and the barb structure is exposed through the hole-shaped structure; when the anchoring area of the first film-coated tubular bracket is of a double-layer structure, the position of the first macromolecule inner film of the outer anchoring area, corresponding to the barb structure, is provided with a hole-shaped structureExposing the barb structure through the hole-shaped structure; the first macromolecule outer covering film of the inner side anchoring area is provided with a hole-shaped structure corresponding to the barb structure, and the barb structure is exposed through the hole-shaped structure; the porous structure can be circular, oval, triangular, quadrilateral or polygonal, and is not particularly limited; when the hole-shaped structure is circular, the diameter of the hole-shaped structure is preferably 0.1-1 mm, and more preferably 0.2-0.8 mm; when the porous structure is non-circular, the area of the porous structure is preferably 0.02-0.08 mm2More preferably 0.03 to 0.06mm2(ii) a The distance between the adjacent hole structures is preferably 1-8 mm, more preferably 2-6 mm, and further preferably 3-6 mm; in the present invention, the total area of the hole structure at the anchoring region far away from the artificial blood vessel body is larger than the total area of the anchoring region close to the artificial blood vessel body; under the condition that the hole structures have the same area, the distance between the anchoring areas of the adjacent hole structures far away from the artificial blood vessel body is smaller than the distance between the anchoring areas close to the artificial blood vessel body; with the same spacing of adjacent hole structures, the area of the hole structures distal from the anchoring region of the vascular body of the worker is greater than the area of the hole structures proximal to the anchoring region of the artificial body.
The second fixing device comprises a second film-coated tubular stent and a second wrapping structure wrapping the second film-coated tubular stent. Wherein the outer diameter of the second wrapping structure is preferably smaller than the outer diameter of the artificial blood vessel body; the second wrapping structure is preferably a cylindrical polymer braided structure, is further preferably one or more braided structures of nylon, terylene, polyurethane and natural silk, wraps the second covered stent and enables the second covered stent of the self-expanding structure to keep a compressed state; the second wrapping structure is provided with a pull wire along the axial direction, the second coating bracket is wrapped by the pull wire, and the free end of the pull wire is positioned at one end far away from the artificial blood vessel body; when the pull wire is pulled open, the second wrapping structure is gradually opened from the end surface, so that the first covered stent is gradually opened from the end surface to the middle.
In the invention, the diameter of the second tectorial membrane tubular stent at one end connected with the artificial blood vessel body in a relaxed state is directly the same as that of the artificial blood vessel body so as to facilitate better connection, and the diameter of one end far away from the artificial blood vessel body is preferably 1-3 times, more preferably 1-2.5 times, still more preferably 1.1-2 times and most preferably 1.1-1.5 times of the diameter of the artificial blood vessel body; in some embodiments provided by the present invention, the diameter of the end of the second stent graft distal to the artificial blood vessel body is preferably 1.14 times, 1.25 times, 1.4 times or 1.5 times the diameter of the artificial blood vessel body. Because the diameter of one end far away from the artificial blood vessel body is larger than that of the other end, the end, far away from the artificial blood vessel body, of the second coating tubular body is in a horn mouth shape.
The second tectorial membrane tubular stent comprises a second supporting structure, a second macromolecule inner tectorial membrane arranged on the inner wall of the second supporting structure and a second macromolecule outer tectorial membrane arranged on the outer wall of the second supporting structure.
In the invention, the thickness of the second support structure is preferably 0.1-1.2 mm; the second support structure is formed by cutting a tube and/or weaving wires; the cutting mode is preferably laser cutting; the thickness of the pipe is preferably 0.1-1.2 mm, more preferably 0.2-0.8 mm, and further preferably 0.3-0.4 mm; the diameter of the wire is preferably 0.03-0.5 mm, and more preferably 0.08-0.3 mm; the second support structure comprises a degradable support portion and a non-degradable support portion; the area ratio of the degradable portion to the non-degradable portion is preferably 1: (0.5 to 2); the degradable support portion is preferably formed of a degradable metal and/or a degradable polymer; the degradable metal is preferably one or more of pure magnesium, magnesium-based alloy, iron-based alloy and zinc-based alloy; the degradable polymer is preferably one or more of polylactic acid PLA, L-PLA, polyglycolic acid/polylactic acid copolymer PGLA, polycaprolactone PCL, polyhydroxybutyrate valerate PHBV, polyacetylglutamate PAGA, polyorthoester POE, polyethylene oxide/polybutylene copolymer PEO/PBTP, polylactide-co-caprolactone copolymer PLC and polycyclohexanone PDO; the non-degradable portion is preferably formed of a non-degradable metal, and is further preferably formed of a nickel titanium alloy.
The second stent-graft preferably comprises a connecting region and an anchoring region.
The second film-coated tubular stent is connected with the artificial blood vessel body through a connecting area; in the invention, the connecting area is preferably formed by weaving degradable wires and non-degradable wires, or the annular non-degradable supporting part and the annular degradable supporting part are alternately arranged along the length direction of the second film-coated tubular stent; wherein the diameters of the degradable wire and the non-degradable wire are respectively and independently preferably 0.03-0.5 mm, and more preferably 0.08-0.3 mm; the width of the woven grid structure is preferably 1-5 mm, and more preferably 2-3 mm; the height is preferably 1-5 mm, and more preferably 2-3 mm; the annular nondegradable support portion and the annular degradable support portion are further preferably annular nondegradable support portions and annular degradable support portions having a W shape; the distance between the end points on the two sides of the W shape is preferably 2-8 mm, and more preferably 3-6 mm; the distance between two adjacent end points of the W shape on one side is preferably 1-4 mm; the width of the annular non-degradable supporting part and the annular degradable supporting part is preferably 0.3-0.6 mm; the distance between the adjacent annular nondegradable support parts and the annular structures of the annular degradable support parts is preferably 3-6 mm; the connecting region has excellent compliance and bending resistance.
The anchoring area preferably comprises a strip-shaped non-degradable supporting part and an annular degradable supporting part which are arranged in an extending way along the length direction of the second tectorial tubular stent; the width of the strip-shaped non-degradable supporting part is preferably 0.2-0.4 mm; the strip-shaped non-degradable supporting part is preferably obtained by cutting a non-degradable pipe; the distance between every two adjacent strip-shaped non-degradable supporting parts along the outer surface of the second film-coated tubular support is preferably 3-6 mm; the width of the annular degradable support part is preferably 0.3-0.6 mm; the distance between adjacent annular degradable supporting parts is preferably 3-6 mm; the annular degradable support part is preferably an annular degradable support part having a W shape. In order to further improve the flexibility of the artificial blood vessel, the anchoring area of the second film-coated tubular stent preferably further comprises a strip-shaped degradable supporting part which is arranged in an extending way along the length direction of the second film-coated tubular stent; the strip-shaped degradable support parts are arranged between two adjacent strip-shaped non-degradable support parts; the distance between the adjacent strip-shaped degradable supporting parts and the adjacent strip-shaped non-degradable supporting parts is preferably 3-6 mm; the width of the strip-shaped degradable support part is preferably 0.3-0.6 mm; the strip-shaped degradable support part is preferably formed by cutting degradable tubing; in the present invention, the anchoring zone of the second stent-graft preferably further comprises an annular non-degradable support portion; the annular non-degradable support portions are arranged between the annular degradable support portions; the annular non-degradable support portion is preferably an annular non-degradable support portion having a W shape; the width of the annular non-degradable supporting part is preferably 0.3-0.6 mm; the distance between the adjacent annular non-degradable supporting parts and the annular degradable supporting parts is preferably 3-6 mm.
In the invention, the second support structure of the anchoring area is preferably provided with a raised barb structure so as to enhance the bonding force between the anchoring area and the vascular tissue; the height of the barb structure is preferably 0.1-3 mm, more preferably 0.2-2 mm, still more preferably 0.2-1 mm, and most preferably 0.3-0.5 mm; the barb structure can be a degradable barb structure or a non-degradable barb structure, and preferably at least comprises the non-degradable barb structure; the degradable barb structures are preferably formed from degradable metals and/or degradable polymers; the degradable metal and the degradable polymer are the same as above, and are not described again; the non-degradable barb structures are preferably formed from a non-degradable metal, and more preferably from a nickel titanium alloy. The anchoring area of the artificial blood vessel provided by the invention can be of a single-layer structure or a double-layer structure; when the anchoring area is of a single-layer structure, the outer surface of the second supporting structure of the anchoring area is preferably provided with a raised barb structure, and the outer surface of the anchoring area is anchored with the inner wall of the vascular tissue; referring to fig. 8, fig. 8 is a schematic view illustrating the connection between the anchoring region of the artificial blood vessel and the vascular tissue when the anchoring region is a single layer, wherein 000 is the vessel wall, 100 is the artificial blood vessel body, 210 is the anchoring region of the single layer, and 230 is a barb structure; when the anchoring area is of a double-layer structure, the structures at the two sides can be the same or different, the two anchoring areas are connected with the artificial blood vessel body through the connecting area, and at the moment, the anchoring area comprises an outer anchoring area and an inner anchoring area; the inner surface of the outer anchoring area is provided with a raised barb structure; the outer surface of the inner side anchoring area is provided with a raised barb structure; after the release, the outer anchoring area is positioned at the outer side of the vascular tissue and attached to the outer side of the vascular tissue wall, and the inner anchoring area is positioned at the inner side of the vascular tissue and attached to the inner side of the vascular tissue wall; referring to fig. 9 and 10, fig. 9 and 10 are schematic views illustrating the connection between the anchoring region of the artificial blood vessel and the vascular tissue when the anchoring region of the artificial blood vessel provided by the present invention is a double layer, wherein 000 is the vessel wall, 100 is the artificial blood vessel body, 220 is the double layer anchoring region, 221 is the outer anchoring region, 222 is the inner anchoring region, 230 and 231 are barb structures, and 260 is a polymer coating.
The inner wall of the second support structure is provided with a second macromolecule inner coating film, and the outer wall of the second support structure is provided with a second macromolecule outer coating film, so that the whole second support structure is coated; the thicknesses of the second macromolecule inner coating film and the second macromolecule outer coating film are respectively and independently preferably 0.02-0.5 mm; the second polymer inner coating film and the second polymer outer coating film are each independently preferably formed of one or more of PTFE (polytetrafluoroethylene), EPTFE (porous polytetrafluoroethylene), FEP (fluorinated ethylene propylene copolymer or perfluoroethylene propylene copolymer), and TPU (thermoplastic polyurethane elastomer rubber). In the present invention, the second polymer inner coating and the second polymer outer coating can be formed by coating on the second supporting structure or by hot pressing, so that the second polymer inner coating, the second supporting structure and the second polymer outer coating form a coated tubular stent as a whole.
In the invention, further, the surface of the second macromolecule inner covering film and/or the second macromolecule outer covering film corresponding to the barb structure of the anchoring area is preferably provided with a hole-shaped structure so as to expose the barb connection structure; the barb structure of the second support structure is exposed through the porous structure, so that the rivet can be better riveted with vascular tissues, and the degradation of the degradable part can be accelerated; when the anchoring area of the second film-coated tubular bracket is of a single-layer structure, a hole-shaped structure is arranged at the position of the second macromolecule outer film corresponding to the barb structure, and the barb structure is exposed through the hole-shaped structure; when the anchoring area of the second film-coated tubular stent is of a double-layer structure, the second height of the outer anchoring areaThe position of the intramolecular tectorial membrane corresponding to the barb structure is provided with a hole-shaped structure, and the barb structure is exposed through the hole-shaped structure; the second macromolecule outer covering film of the inner side anchoring area is provided with a hole-shaped structure corresponding to the barb structure, and the barb structure is exposed through the hole-shaped structure; the porous structure can be circular, oval, triangular, quadrilateral or polygonal, and is not particularly limited; when the hole-shaped structure is circular, the diameter of the hole-shaped structure is preferably 0.1-1 mm, and more preferably 0.2-0.8 mm; when the porous structure is non-circular, the area of the porous structure is preferably 0.02-0.08 mm2More preferably 0.03 to 0.06mm2(ii) a The distance between the adjacent hole structures is preferably 1-8 mm, more preferably 2-6 mm, and further preferably 3-6 mm; in the present invention, the total area of the hole structure at the anchoring region far away from the artificial blood vessel body is larger than the total area of the anchoring region close to the artificial blood vessel body; under the condition that the hole structures have the same area, the distance between the anchoring areas of the adjacent hole structures far away from the artificial blood vessel body is smaller than the distance between the anchoring areas close to the artificial blood vessel body; with the same spacing of adjacent hole structures, the area of the hole structures distal from the anchoring region of the vascular body of the worker is greater than the area of the hole structures proximal to the anchoring region of the artificial body.
The artificial blood vessel fixing device provided by the invention can provide different supporting forces in different use stages, so that effective fixing and flexibility are considered, the fixing device has a quick anchoring function at the fixing end, can be quickly linked with blood vessel tissues, the middle artificial blood vessel body structure has excellent bending resistance, a bypass pipeline can be quickly provided at an embolism position, the operation time is shortened, the burden of a doctor is reduced, and the operation risk is reduced.
The invention also provides a using method of the artificial blood vessel, wherein one end of the fixing device is placed into the blood vessel with the window, the pull wire of the wrapping structure is slowly pulled after the fixing device reaches a preset position, so that the covered stent in the wrapping structure is slowly opened, and the wrapping structure is withdrawn after the fixing device is completely opened, so that the barbs on the stent are fully anchored on the blood vessel wall. And repeating the operations to perform the connection operation of the other end, thereby completing the establishment of the whole bypass pipeline. In the early stage of implantation, the covered stent for fixation has stronger mechanical property and can ensure effective link with the vascular wall, and the degradable material in the implanted covered stent is gradually degraded along with the time, so that the connecting part of the implanted covered stent and the vascular wall is more flexible, the stimulation to the vascular wall tissue is reduced, and the tissue hyperplasia and the vascular restenosis are effectively prevented.
In order to further explain the present invention, the following describes a vascular prosthesis with variable supporting force in detail with reference to the following embodiments.
The reagents used in the following examples are all commercially available.
Example 1
As shown in figure 1, the invention consists of 100 artificial blood vessel structures and 200 covered stents, wherein the 200 covered stents are wrapped and fixed by 300 wrapping structures in a compressed state. The 100 artificial blood vessel structure is a mixed braided fabric of terylene and natural silk, has corrugated protrusions on the surface, has good flexibility and biocompatibility, and has a diameter of 7mm and a length of 160 mm; the 300-wrapping structure is a barrel-shaped braided fabric made of terylene, 320 nylon drawn wires are arranged on the barrel-shaped braided fabric, the outer diameter of the barrel-shaped braided fabric is 6mm, and the length of the barrel-shaped braided fabric is 28 mm.
The 200 tectorial membrane stent is a 210 monolayer anchoring stent and is connected with the artificial blood vessel in a sewing mode, as shown in figure 5, the length is 30mm, 260 macromolecule tectorial membrane is EPTFE (the thickness is 0.3mm), the membrane is provided with a round hole with the outer diameter of 0.2mm, and the hole distance of an anchoring area close to the 100 artificial blood vessel connecting section is 5 mm; the distance between the outer end faces is 3 mm. The polymer film is connected and fused with the supporting structure in a hot pressing mode, a support (the width of a woven grid is 2mm, the height of the woven grid is 3mm, and the woven length of the woven grid is 8mm) consisting of 240 nickel titanium woven wires and 241 degradable magnesium alloy woven wires is arranged inside the artificial blood vessel connecting end, and the diameter of the woven wire is 0.04mm, so that the flexibility and the bending resistance are excellent; the inner part (namely an anchoring area) of the connecting end of the vascular tissue is strip nickel-titanium cutting, the W-shaped nickel-titanium cutting support and the W-shaped polylactic acid copolymer PGLA degradable cutting support (6 strip cutting supports are uniformly distributed in the outer diameter direction, the thickness of the cutting support is 0.3mm, the width of the cutting support is 0.4mm, the distance between every two adjacent W-shaped cutting supports is 4mm, the distance between the end points at two sides of the W shape is 3mm, the total length of the strip cutting support positioned between every two adjacent end points at one side is 2mm is 20mm), the height of the structure provided with the 230 nickel-titanium alloy barb and the 231 polycaprolactone PCL degradable barb is 0.3mm, the barb structure is exposed out through a circular hole of a polymer film, after heat treatment at different temperatures, the shape of the stent is 8mm as d outer diameter in figure 4, and the superelasticity of nickel-titanium metal and high polymer material and the 231 polycaprolactone PCL degradable barb structure enable the whole 200 covered stent to have good elasticity and tissue anchoring capability.
The first windowing treatment is carried out at one end of a blood vessel with lesion length of about 150mm, a guide wire is led out from the first window, then the guide wire passes through the artificial vascular system with variable supporting force, the second windowing treatment is carried out at the position of about 155mm at the other end of a lesion area, and then the guide wire passes through the second window to complete the installation preparation work.
Firstly, slowly plugging a 300-wrapped structure with a 200-layer stent into vascular tissue along a guide wire at a second window, slowly pulling 320 nylon pull wires after reaching a preset position, gradually opening 310 cylindrical high-molecular braided fabric, gradually releasing a stent from the outer side end face to the middle area as shown in fig. 3, withdrawing the wrapped structure after completely opening to enable barbs on the stent to be fully anchored on the vascular tissue, fully attaching the inner wall of the blood vessel to the stent coating, and then repeating the above operations at the first window to complete the establishment of the whole bypass pipeline as shown in fig. 8. The guide wire is withdrawn after the above operations are finished.
After the artificial vascular system of the embodiment 1 is implanted, because the coating structures at the two ends of the stent are fully attached to the inner wall of the blood vessel, the stability of blood flow is effectively improved, the turbulence phenomenon caused by uneven anastomotic stoma is reduced, so that the probability of thrombus formation is reduced, and the effective patency rate and treatment effect are further ensured; after 1 week, the degradable material in the covered stent of the vascular tissue connecting section gradually starts to degrade, and the density of the round holes on the polymer film is gradually increased from inside to outside, so that the degradation rate of the end face close to the outside is 30% higher than that of the artificial vascular connecting section close to 100, the fixing force is released in a short time, the stimulation to vascular wall tissues is reduced, the degradable material loses the supporting force after 4 weeks, and the complete degradation is completed after 10 weeks. In the process, the stimulation to the vascular wall tissue is gradually reduced from two ends to the inner side, so that the tissue hyperplasia and the vascular embolism are effectively prevented.
Example 2
As shown in figure 1, the invention consists of 100 artificial blood vessel structures and 200 covered stents, wherein the 200 covered stents are wrapped and fixed by 300 wrapping structures in a compressed state. The 100 artificial blood vessel structure is a mixed braided fabric of terylene and polyurethane, the inner side of the mixed braided fabric is attached with PTFE (polytetrafluoroethylene), the surface of the artificial blood vessel structure has stripe-shaped protrusions with good flexibility and supporting performance, the diameter is 8mm, and the length is 220 mm; the 300-wrapping structure is a barrel-shaped braided fabric made of polyurethane and nylon, 320 nylon wire drawing wires are arranged on the barrel-shaped braided fabric, the outer diameter of the barrel-shaped braided fabric is 5mm, and the length of the barrel-shaped braided fabric is 40 mm.
200, the tectorial membrane stent is a 210-monolayer anchoring stent and is connected with the artificial blood vessel in a bonding mode, for example, the length of figure 6 is 40mm, 260 high polymer tectorial membrane (the thickness is 0.2mm) is EPTFE (porous polytetrafluoroethylene) and FEP (fluorinated ethylene propylene copolymer or perfluoroethylene propylene copolymer), round holes with different sizes are arranged on the membrane, the distance between the round holes is 6mm, and the diameter of the round hole of the high polymer membrane close to the connection section of the artificial blood vessel is 0.3 mm; the diameter of the round hole close to the end surface of the outer side is 0.4 mm. The polymer film is connected and fused with the supporting structure in a hot pressing mode, and the diameter of the polymer film is 1.5 mm. The connection region of the 200-layered membrane stent consists of 250 annular nickel-titanium cutting supports and 251 annular pure-magnesium cutting supports (the cutting supports are W-shaped, the distance between end points at two sides of the W shape is 5mm, the distance between two adjacent end points at one side is 1mm, the width of the cutting supports is 0.3mm, the distance between the adjacent cutting supports is 5mm, the total length of the connection region and the anchoring region cutting supports is 38mm, the ratio of the two is 1: 1), a pipe with the wall thickness of 0.2mm is cut by laser cutting, the anchoring region is also provided with strip-shaped nickel-titanium cutting supports and strip-shaped pure-magnesium cutting supports, the annular nickel-titanium cutting supports and the annular pure-magnesium cutting supports in the anchoring region are connected along the length direction of the anchoring region, 8 nickel-titanium cutting supports are uniformly distributed in the outer diameter direction, the nickel-titanium cutting supports and the pure-magnesium cutting supports are arranged at intervals, and the width of the nickel-titanium cutting supports is 0.3mm, the width of the pure magnesium cutting support is 0.4mm, and the height of a 230 nickel-titanium barb structure arranged on the outer side of the nickel-titanium cutting support in the anchoring area is 0.3 mm; the degradable barb structure height that the pure magnesium cutting supported the outside and was equipped with 231 pure magnesium is 0.4mm, and the barb structure leaks out through the round hole of polymer tectorial membrane naked, and its appearance is 10mm as e external diameter in figure 4 after moulding and thermal treatment.
The first windowing treatment is carried out at one end of a blood vessel with lesion length of about 200mm, the guide wire is led out from the first window, then the guide wire passes through the artificial vascular system with variable supporting force in the embodiment, the second windowing treatment is carried out at the position of about 210mm at the other end of the lesion area, and then the guide wire passes through the second window to complete the installation preparation work.
Firstly, slowly plugging a 300-wrapped structure with a 200-layer stent into vascular tissue along a guide wire at a second window, slowly pulling 320 nylon pull wires after reaching a preset position, gradually opening 310 cylindrical high-molecular braided fabric, gradually releasing a stent from the outer side end face to the middle area as shown in fig. 3, withdrawing the wrapped structure after completely opening to enable barbs on the stent to be fully anchored on the vascular tissue, fully attaching the inner wall of the blood vessel to the stent coating, and then repeating the above operations at the first window to complete the establishment of the whole bypass pipeline as shown in fig. 8. The guide wire is withdrawn after the above operations are finished.
After the artificial blood vessel is implanted, the coating structures at the two ends of the stent are fully attached to the inner wall of the blood vessel, so that the stability of blood flow is effectively improved, the turbulent flow phenomenon caused by uneven anastomotic stoma is reduced, the probability of thrombus formation is reduced, and the effective patency rate and treatment effect are further ensured; after 3 days, with the inside degradable material of tectorial membrane support of vascular tissue linkage segment progressively begins to degrade, because of the round hole diameter that is equipped with on the polymer film progressively increases from inside to outside, so the degradation rate of nearly outside terminal surface is higher than nearly 100 artificial blood vessel linkage segment 20%, make the stationary force release in short time, reduced the stimulation to vascular wall tissue, degradable material loses the holding power after 2 weeks, 8 weeks all degradation finish, through the stimulation to vascular wall tissue reduce by both ends inside side progressively effectively to prevent hyperplasia and vascular embolism.
Example 3
As shown in figure 1, the invention consists of 100 artificial blood vessel structures and 200 covered stents, wherein the 200 covered stents are wrapped and fixed by 300 wrapping structures in a compressed state. The 100 artificial blood vessel structure is a polyurethane braided fabric, the inner side and the outer side of the artificial blood vessel structure are both attached with EPTFE (porous polytetrafluoroethylene), corrugated bulges exist on the surface of the artificial blood vessel structure, the flexibility and the blood permeability are good, the diameter is 5mm, and the length is 180 mm; the 300-wrapping structure is a barrel-shaped braided fabric made of polyurethane and terylene, 320 polyurethane wire drawing is arranged on the barrel-shaped braided fabric, the outer diameter of the barrel-shaped braided fabric is 4mm, and the length of the barrel-shaped braided fabric is 20 mm. The 200 tectorial membrane stent is a 210 monolayer anchoring stent and is connected with the artificial blood vessel in a hot-pressing mode, as shown in figure 7, the length is 25mm, 260 macromolecule tectorial membrane is PTFE (polytetrafluoroethylene) and EPTFE (porous polytetrafluoroethylene), round holes with different sizes are arranged on the membrane, the distance between the round holes is 6mm, and the diameter of the round hole of the macromolecule membrane close to the 100 artificial blood vessel connecting section is 0.4 mm; the diameter of the round hole close to the end surface of the outer side is 0.8 mm. The polymer film is connected and fused with the supporting structure in a hot melting mode, and is formed by alternately arranging 250 annular nickel-titanium cutting supports and 251 annular polyhydroxybutyrate valerate PHBV cutting supports in the connecting end of the artificial blood vessel (the cutting supports are W-shaped, the distance between the end points on the two sides of the W-shaped is 3mm, the distance between the two adjacent end points on one side is 1mm, the width of the cutting supports is 0.3mm, the distance between the adjacent cutting supports is 3mm, the total length of the connecting area and the anchoring area cutting supports is 22mm), a pipe with the wall thickness of 0.2mm is cut by laser cutting, the anchoring area is also provided with strip-shaped nickel-titanium cutting supports, the annular nickel-titanium cutting supports and the polyhydroxybutyrate valerate PHBV cutting supports in the anchoring area are connected together along the length direction of the anchoring area, and 8 nickel-titanium cutting supports are uniformly distributed in the outer diameter direction; the nickel titanium cutting supports the width and is 0.35mm, and the degradable barb structure height that the outside was equipped with 231 polylactic acid PLA is supported in the cutting of anchoring zone is 0.4mm, and the barb structure exposes out through the round hole of polymer tectorial membrane, and its appearance is 7mm as d external diameter in figure 4 after moulding and thermal treatment.
And performing first windowing treatment at one end of the blood vessel with the lesion length of about 170mm, and performing second windowing treatment at the position of about 175mm at the other end of the lesion area to finish the installation preparation work.
Slowly plugging a 300-wrapped structure with a 200-coated stent into any one window, slowly pulling 320 polyurethane pull wires after reaching a preset position, gradually opening 310 cylindrical polymer braided fabric, gradually releasing the stent from the outer side end face to the middle area as shown in fig. 4, withdrawing the wrapped structure after completely opening to enable barbs on the stent to be fully anchored on blood vessel tissue, fully attaching the inner wall of the blood vessel to a stent coating, and repeating the above operations at the first window to complete the establishment of the whole bypass pipeline as shown in fig. 8.
After the artificial blood vessel is implanted, the coating structures at the two ends of the stent are fully attached to the inner wall of the blood vessel, so that the stability of blood flow is effectively improved, the turbulent flow phenomenon caused by uneven anastomotic stoma is reduced, the probability of thrombus formation is reduced, and the effective patency rate and treatment effect are further ensured; after 2 weeks, the degradable material inside the covered stent of the vascular tissue connecting section gradually starts to degrade, the diameter of a round hole arranged on a polymer membrane is gradually increased from inside to outside, so that the degradation rate of the end face close to the outside is higher than that of the artificial vascular connecting section close to 100 percent, the fixing force is released in a short time, the stimulation to the vascular wall tissue is reduced, the supporting force of the degradable material is lost after 4 weeks, the degradation is completed after 10 weeks, the degradation is completed completely, the degradation from the two ends to the inside through the stimulation to the vascular wall tissue is gradually reduced in the above process, and the tissue proliferation and the vascular embolism are effectively prevented.
Example 4
As shown in figure 1, the invention consists of 100 artificial blood vessel structures and 200 covered stents, wherein the 200 covered stents are wrapped and fixed by 300 wrapping structures in a compressed state. The 100 artificial blood vessel structure is a mixed braided fabric of nylon and terylene, the inner sides of the artificial blood vessel structure are attached with PTFE (polytetrafluoroethylene), the surface is axially provided with corrugated bulges respectively, and the artificial blood vessel structure has good flexibility and blood permeability, the diameter is 8mm, and the length is 200 mm; the 300-wrapping structure is a barrel-shaped braided fabric made of polyurethane and terylene, 320 polyurethane wire drawing is arranged on the barrel-shaped braided fabric, the outer diameter of the barrel-shaped braided fabric is 6mm, and the length of the barrel-shaped braided fabric is 40 mm. The 200 tectorial membrane support is a 220 double-layer anchoring support and is connected with the artificial blood vessel in a hot-pressing mode, the outer anchoring support of the 221 double-layer anchoring support of the 220 double-layer anchoring support is made of an iron-based degradable alloy pipe with the wall thickness of 0.3mm by laser cutting, and the length of the outer anchoring support is equal to that of the iron-based degradable alloy pipeThe thickness of the inner side anchoring support of the 222 double-layer anchoring support is 32mm, the inner side anchoring support of the 222 double-layer anchoring support is made of a nickel-titanium alloy pipe with the wall thickness of 0.35mm through laser cutting (the cutting support has a W shape, the distance between end points on two sides of the W shape is 6mm, the distance between two adjacent end points on one side is 1mm, the width of the cutting support is 0.25mm, the distance between two adjacent cutting supports is 6mm), and the length is 38 mm; the anchoring area is also provided with strip-shaped iron-based degradable cutting supports and strip-shaped nickel-titanium alloy cutting supports, the strip-shaped iron-based degradable cutting supports and the strip-shaped nickel-titanium alloy cutting supports respectively connect the annular iron-based degradable cutting supports and the annular nickel-titanium alloy cutting supports in the anchoring area along the length direction of the anchoring area, 10 pieces of the strip-shaped iron-based degradable cutting supports and the strip-shaped nickel-titanium alloy cutting supports are uniformly distributed in the outer diameter direction of the cutting supports, the nickel-titanium alloy cutting supports and the iron-based degradable cutting supports are arranged at intervals, the width of the nickel-titanium cutting supports is 0.35mm, and the width of the iron-based degradable cutting supports is 0.45 mm; 260 high polymer film (thickness 0.05mm) is EPTFE (porous polytetrafluoroethylene) and FEP (perfluoroethylene propylene copolymer), and the area of the film is about 0.05mm2The distance between the oval holes close to the 100 artificial blood vessel connecting sections is 6 mm; the distance between the outer end faces is 3 mm. The polymer film is connected and fused with the supporting structure in a hot melting mode, 240-nickel-titanium woven wire supports (the width of a woven grid is 2mm, the height of the woven grid is 3mm, and the woven length of the woven grid is 8mm) are arranged inside the artificial blood vessel connecting end, and the woven wire has excellent flexibility and bending resistance when the diameter of the woven wire is 0.08 mm; as shown in the tube tissue connecting end of fig. 10, the outer anchoring bracket of the 221 double-layer anchoring bracket is provided with an iron-based degradable alloy barb structure with the height of 0.35 mm; 222 the inner side of the double-layer anchoring bracket is provided with a nickel titanium alloy barb structure with a height of 0.40mm, the shape is shown as g in figure 4 after shaping and heat treatment, and the maximum outer diameter is 12 mm.
The first windowing treatment is carried out at one end of the blood vessel with the lesion length of about 220mm, and the second windowing treatment is carried out at the position of about 240mm at the other end of the lesion region, so that the installation preparation work is completed.
Inserting a 300-wrapping structure with a 200-layer stent into any one window, slowly pulling 320 nylon pull wires after reaching a preset position, gradually opening 310 cylindrical high-molecular braided fabric, adjusting to confirm that the inner anchoring stent of a 222-layer anchoring stent is positioned on the inner side of a blood vessel wall after the inner anchoring stent of the double-layer stent is opened, slowly pulling 320 polyurethane pull wires, gradually releasing the stents from the outer end faces to the middle area at the same time as shown in fig. 4, withdrawing the wrapping structure after being completely opened to enable barbs on the stent to be fully anchored on the blood vessel tissue as shown in fig. 10, fully attaching the inner wall of the blood vessel to a stent coating, repeating the above operations at a first window, and completing the establishment of the whole bypass pipeline as shown in fig. 9.
After the artificial blood vessel is implanted, the coating structures at the two ends of the stent are fully attached to the inner wall of the blood vessel, so that the stability of blood flow is effectively improved, the turbulent flow phenomenon caused by uneven anastomotic stoma is reduced, the probability of thrombus formation is reduced, and the effective patency rate and treatment effect are further ensured; after 2 weeks, the degradable material inside the covered stent of the vascular tissue connecting section gradually starts to degrade, the density of elliptical holes arranged on the polymer film is gradually increased from inside to outside, so that the degradation rate of the end surface of the proximal outer side is 25% higher than that of the artificial vascular connecting section of the proximal 100, the fixing force is released in a shorter time, the stimulation to the vascular wall tissue is reduced, the supporting force of the degradable material is lost after 4 weeks, the complete degradation is completed after 10 weeks, the supporting force of the degradable material is lost after 8 weeks, the complete degradation is completed after 20 weeks, and the tissue proliferation and the vascular embolism are effectively prevented by gradually reducing the stimulation to the vascular wall tissue from two ends to the inside in the processes.
Example 5
As shown in fig. 1, the artificial blood vessel of this embodiment is composed of 100 artificial blood vessel structures and 200 covered stents, and the 200 covered stents are wrapped and fixed by the 300 wrapped structure in a compressed state. The 100 artificial blood vessel structure is a mixed braided fabric of nylon and terylene, the inner sides of the artificial blood vessel structure are attached with PTFE (polytetrafluoroethylene), the surface is axially provided with corrugated bulges respectively, and the artificial blood vessel structure has good flexibility and blood permeability, the diameter is 8mm, and the length is 200 mm; the 300-wrapping structure is a barrel-shaped braided fabric made of polyurethane and terylene, 320 polyurethane wire drawing is arranged on the barrel-shaped braided fabric, the outer diameter of the barrel-shaped braided fabric is 6mm, and the length of the barrel-shaped braided fabric is 40 mm. The 200 tectorial membrane stent is a 220 double-layer anchoring stent and is connected with an artificial blood vessel in a hot-pressing mode, and the outer anchoring stent of the 221 double-layer anchoring stent of the 220 double-layer anchoring stent is manufactured by an iron-based degradable alloy pipe with the wall thickness of 0.3mm through laser cuttingThe inner side anchoring bracket of the 222 double-layer anchoring bracket is manufactured by laser cutting of a nickel-titanium alloy pipe with the wall thickness of 0.35mm (the cutting support has a W shape, the width of the cutting support is 0.25mm, the distance between the adjacent cutting supports is 8mm), and the length is 38 mm; the anchoring area is also provided with strip-shaped iron-based degradable cutting supports and strip-shaped nickel-titanium alloy cutting supports, and the strip-shaped iron-based degradable cutting supports and the strip-shaped nickel-titanium alloy cutting supports respectively connect the annular iron-based degradable cutting supports and the annular nickel-titanium alloy cutting supports in the anchoring area along the length direction of the anchoring area, 6 cutting supports are uniformly distributed in the outer diameter direction, the nickel-titanium alloy cutting supports and the iron-based degradable cutting supports are arranged at intervals, the width of the nickel-titanium cutting supports is 0.4mm, and the width of the iron-based degradable cutting supports is 0.5 mm; 260 high polymer film (thickness 0.15mm) is EPTFE (porous polytetrafluoroethylene) and FEP (perfluoroethylene propylene copolymer), polygonal holes with different areas are arranged on the film, and the area of the polygonal hole close to the 100 artificial blood vessel connecting section is 0.03mm2The hole spacing is 6 mm; the area of the polygonal hole close to the end surface of the outer side is 0.06mm2The pitch was 3 mm. The polymer film is connected and fused with the supporting structure in a hot melting mode, a 240 nickel titanium woven wire supporting tool (the width of a woven grid is 3.5mm, the height of the woven grid is 3mm, and the woven length of the woven grid is 30mm) is arranged inside the artificial blood vessel connecting end, and the diameter of the woven wire is 0.08mm, so that the flexibility and the bending resistance are excellent; as shown in fig. 10, at the end connected with vascular tissue, the outer anchoring stent of the 221 double-layer anchoring stent is provided with an iron-based degradable alloy barb structure with the height of 0.35 mm; 222 the inner side of the double-layer anchoring bracket is provided with a nickel titanium alloy barb structure with a height of 0.40mm, the shape is shown as g in figure 4 after shaping and heat treatment, and the maximum outer diameter is 12 mm.
The first windowing treatment is carried out at one end of the blood vessel with the lesion length of about 220mm, and the second windowing treatment is carried out at the position of about 240mm at the other end of the lesion region, so that the installation preparation work is completed.
Inserting a 300-wrapping structure with a 200-layer stent into any one window, slowly pulling 320 nylon pull wires after reaching a preset position, gradually opening 310 cylindrical high-molecular braided fabric, adjusting to confirm that the inner anchoring stent of a 222-layer anchoring stent is positioned on the inner side of a blood vessel wall after the inner anchoring stent of the double-layer stent is opened, slowly pulling 320 polyurethane pull wires, gradually releasing the stents from the outer end faces to the middle area at the same time as shown in fig. 9, completely opening and withdrawing the wrapping structure to enable barbs on the stent to be fully anchored on blood vessel tissue as shown in fig. 10, fully attaching the inner wall of the blood vessel to a stent coating, and repeating the above operations at a first window to complete the establishment of the whole bypass pipeline as shown in fig. 9.
After the artificial blood vessel is implanted, the coating structures at the two ends of the stent are fully attached to the inner wall of the blood vessel, so that the stability of blood flow is effectively improved, the turbulent flow phenomenon caused by uneven anastomotic stoma is reduced, the probability of thrombus formation is reduced, and the effective patency rate and treatment effect are further ensured; after 2 weeks, with the inside degradable material of tectorial membrane support of vascular tissue linkage segment progressively begins to degrade, because of the polygon hole area and the density that are equipped with on the macromolecular membrane progressively increase from inside to outside, so the degradation rate of nearly outside terminal surface is higher than nearly 100 artificial blood vessel linkage segment 35%, make the clamping force release in the shorter time, the stimulation to vascular wall tissue has been reduced, degradable material loses the holding power after 8 weeks, 20 weeks after all degradation finish, through the stimulation to vascular wall tissue reduce progressively by both ends inboard effectively prevent hyperplasia and vascular embolism.

Claims (10)

1. An artificial blood vessel with variable supporting force is characterized by comprising a first fixing device, an artificial blood vessel body and a second fixing device which are sequentially communicated;
the first fixing device comprises a first tectorial tubular stent and a first wrapping structure wrapped outside the first tectorial tubular stent;
the first tectorial tubular stent comprises a first support structure, a first macromolecule inner tectorial membrane arranged on the inner wall of the first support structure and a first macromolecule outer tectorial membrane arranged on the outer wall of the first support structure;
the second fixing device comprises a second film-coated tubular stent and a second wrapping structure wrapping the second film-coated tubular stent;
the second film-coated tubular stent comprises a second supporting structure, a second macromolecule inner film and a second macromolecule outer film, wherein the second macromolecule inner film is arranged on the inner wall of the second supporting structure, and the second macromolecule outer film is arranged on the outer wall of the second supporting structure;
the first support structure and the second support structure each independently comprise a degradable support portion and a non-degradable support portion.
2. The artificial blood vessel of claim 1, wherein the diameter of the first stent graft connected to the artificial blood vessel in the relaxed state is the same as the diameter of the artificial blood vessel, and the diameter of the stent graft away from the artificial blood vessel is 1 to 3 times the diameter of the artificial blood vessel;
the diameter of one end of the second tectorial membrane tubular stent, which is connected with the human blood vessel body in a relaxed state, is the same as that of the artificial blood vessel body, and the diameter of one end far away from the artificial blood vessel body is 1-3 times of that of the artificial blood vessel body.
3. The prosthesis of claim 1 wherein the first stent-graft comprises a connecting region and an anchoring region, the first support structure of the anchoring region having raised barb structures disposed thereon;
the second film-coated tubular bracket comprises a connecting area and an anchoring area, and a second supporting structure of the anchoring area is provided with a raised barb structure;
the height of barb structure is 0.1 ~ 3 mm.
4. The artificial blood vessel according to claim 3, wherein the connection region of the first stent-graft is woven from degradable filaments and non-degradable filaments; or the annular nondegradable support parts and the annular degradable support parts are alternately arranged along the length direction of the first film-coated tubular stent;
the connecting area of the second film-coated tubular stent is formed by weaving degradable filaments and non-degradable filaments; or the annular nondegradable support parts and the annular degradable support parts are alternately arranged along the length direction of the second film-coated tubular stent.
5. The artificial blood vessel of claim 3, wherein the anchoring region of the first stent-graft comprises a strip-shaped non-degradable support part and a ring-shaped degradable support part which are arranged along the length direction of the first stent-graft in an extending way;
the anchoring area of the first film-coated tubular stent comprises a strip-shaped non-degradable supporting part and an annular degradable supporting part which are arranged in an extending way along the length direction of the first film-coated tubular stent;
the anchoring area of the second tectorial tubular stent comprises a strip-shaped non-degradable supporting part and an annular degradable supporting part which are arranged in an extending way along the length direction of the second tectorial tubular stent;
the anchoring area of the second tectorial tubular stent comprises a strip-shaped non-degradable supporting part and an annular degradable supporting part which are arranged in an extending way along the length direction of the second tectorial tubular stent; .
6. The artificial blood vessel of claim 5, wherein the anchoring region of the first stent-graft further comprises a strip-shaped degradable support part extending along the length direction of the first stent-graft; the strip-shaped degradable support parts are arranged between two adjacent strip-shaped non-degradable support parts;
the anchoring area of the second tectorial tubular stent also comprises a strip-shaped degradable supporting part which is arranged along the length direction of the second tectorial tubular stent in an extending way; the strip-shaped degradable support parts are arranged between two adjacent strip-shaped non-degradable support parts.
7. The prosthesis of claim 3 wherein the anchoring zone of the first stent-graft is of a single-layer structure or a double-layer structure; when the anchoring area is of a single-layer structure, a raised barb structure is arranged on the outer surface of the first supporting structure of the anchoring area; when the anchoring area is of a double-layer structure, the anchoring area comprises an outer anchoring area and an inner anchoring area; the inner surface of the outer anchoring area is provided with a raised barb structure; the outer surface of the inner side anchoring area is provided with a raised barb structure;
the anchoring area of the second film-coated tubular bracket is of a single-layer structure or a double-layer structure; when the anchoring area is of a single-layer structure, a raised barb structure is arranged on the outer surface of the second supporting structure of the anchoring area; when the anchoring area is of a double-layer structure, the anchoring area comprises an outer anchoring area and an inner anchoring area; the inner surface of the outer anchoring area is provided with a raised barb structure; the surface in inboard anchor region is provided with bellied barb structure.
8. The artificial blood vessel of claim 7, wherein when the anchoring area of the first coated tubular stent is a single-layer structure, the first polymer outer coating is provided with a hole structure corresponding to the barb structure, and the barb structure is exposed through the hole structure;
when the anchoring area of the first film-coated tubular bracket is of a double-layer structure, the position of the first macromolecule inner film of the outer anchoring area, which corresponds to the barb structure, is provided with a hole-shaped structure, and the barb structure is exposed through the hole-shaped structure; the first macromolecule outer covering film of the inner side anchoring area is provided with a hole-shaped structure corresponding to the barb structure, and the barb structure is exposed through the hole-shaped structure;
when the anchoring area of the second film-coated tubular bracket is of a single-layer structure, a hole-shaped structure is arranged at the position of the second macromolecule outer film corresponding to the barb structure, and the barb structure is exposed through the hole-shaped structure;
when the anchoring area of the second film-coated tubular bracket is of a double-layer structure, the position of the second macromolecule inner film of the outer anchoring area, which corresponds to the barb structure, is provided with a hole-shaped structure, and the barb structure is exposed through the hole-shaped structure; the position that the tectorial membrane is provided with the poroid structure corresponding to the barb structure outside the second polymer of inboard anchoring zone, exposes the barb structure through the poroid structure.
9. The prosthesis of claim 1, wherein the area ratio of degradable support portion to non-degradable support portion of the first support structure is 1: (0.5-2).
10. The artificial blood vessel of claim 1, wherein the first support structure and the second support structure each independently have a thickness of 0.1-1.2 mm; the thicknesses of the first macromolecule inner coating film, the first macromolecule outer coating film, the second macromolecule inner coating film and the second macromolecule outer coating film are respectively 0.02-0.5 mm independently.
CN202111493268.XA 2021-12-08 2021-12-08 Artificial blood vessel with variable supporting force Pending CN114010367A (en)

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CN202111493268.XA CN114010367A (en) 2021-12-08 2021-12-08 Artificial blood vessel with variable supporting force

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