CN211096500U - Instant puncture dialysis type nanofiber artificial blood vessel - Google Patents

Abstract

The utility model provides an immediate puncture dialysis type nanofiber artificial blood vessel, the wall of which is provided with an inner layer, an outer layer and a non-porous compact coating layer positioned between the inner layer and the outer layer; wherein, the inner layer is in an electrostatic spinning nanofiber structure; an anticoagulant coating is fixed on the inner wall of the inner layer; the outer layer is in an electrostatic spinning nanofiber structure; the nonporous compact coating is internally wrapped with a bending-resistant corrugated ring which is a spiral winding wire with a spiral structure, and the spiral winding wire is spirally wound on the inner layer. The utility model also provides a preparation method of the artificial blood vessel. The inner wall and the outer wall of the artificial blood vessel are made of nano fibers, so that a natural extracellular matrix structure can be fully simulated, a good environment is provided for the growth, adhesion and migration of cells, and the high porosity is favorable for the exchange of nutrient substances; the compact layer has higher elasticity, and the puncture hole position can heal automatically, prevents the seepage of blood, shortens hemostasis time.

Description

Instant puncture dialysis type nanofiber artificial blood vessel

Technical Field

The utility model relates to the field of biomedical equipment, concretely relates to application of instant puncture dialysis type nanofiber artificial blood vessel in dialysis fistulization.

Background

One common problem with vascular prostheses is bleeding through small holes that are punctured into the wall of the graft by suture needles or dialysis needles. Commercially available vascular grafts are typically made of polyethylene terephthalate fabric or expanded polytetrafluoroethylene tubing, and materials of biological origin, such as human native saphenous vein vessels, are also used. Suture needles used to engage these vascular grafts often result in significant bleeding from the puncture before the surgical incision is closed. Dialysis treatment of a patient with renal failure requires that the patient's blood be drawn, circulated through a dialysis machine, and then returned to the patient. One common method of providing the necessary hemodialysis access is to use an artificial blood vessel for mobile venous fistulization, the graft being connected by a dialysis needle through a long tube to a dialysis machine for subcutaneous puncture. The puncture site may also produce undesirable bleeding when the dialysis needle is removed.

Suture needles during the anastomosis process, the tension forces typically cause the suture needle to elongate and enlarge the hole during the suturing process due to the tension forces applied to the suture needle during the suturing process. Bleeding from the suture hole must be blocked before the suture opening is closed. Suture hole bleeding is therefore responsible for increased blood loss and increased surgical time. Artificial blood vessels have significant value in reducing suture bleeding as well as dialysis puncture bleeding in both these areas.

It is also clinically urgent for some patients who are in urgent need of dialysis as soon as possible to have an artificial blood vessel available for hemodialysis immediately after implantation. Commercial vascular grafts currently used in hemodialysis procedures require fibrous tissue to form around the vascular prosthesis after 4-8 weeks of maturation after implantation in the body, followed by dialysis puncture, thereby reducing the risk of excessive bleeding at the puncture site. An artificial blood vessel for dialysis applications, allowing puncture to be performed early after implantation without affecting other features, is an important step forward in the field of hemodialysis access.

An ePTFE artificial blood vessel with a three-layer structure is used for a clinical early dialysis blood vessel access, a silica gel layer in the middle of the three-layer structure can provide a quick closing effect for a puncture hole, the inner layer of the vascular graft is made of a traditional ePTFE material, the middle layer of the vascular graft is made of soft elastic silica gel, the outer layer of the vascular graft is made of an ePTFE material, and the silica gel layer is used as a closing layer. Also, in chinese patent CN208974736U, the ePTFE artificial blood vessel of three-layer structure, the inner layer of which is coated with silk fibroin, but its anticoagulation effect is much lower than heparin, and it cannot provide good anticoagulation property between endothelialization of blood vessels.

For dialysis patients, the artificial blood vessel to be implanted into the body should meet the puncture condition of a dialysis needle more than 2000 times per year, and the artificial blood vessel to be implanted should meet a certain length, and puncture sites are increased as much as possible, so that a U-shaped artificial blood vessel is generally used for arteriovenous fistulation in clinic, and therefore the artificial blood vessel is required to have good bending resistance.

Therefore, an artificial blood vessel capable of solving the above problems is of great importance.

SUMMERY OF THE UTILITY MODEL

The utility model aims at providing an artificial blood vessel that can puncture immediately for dialysis patient, just can satisfy the dialysis condition after implanting internal 24-48h, can dialyze the puncture, need not do anticoagulant medicine preliminary treatment to artificial blood vessel when implanting simultaneously, and the anticoagulation coating of having certainly can satisfy the antithrombotic, prevent the inner membrance hyperplasia, further satisfies clinical application.

In order to achieve the above purpose, the utility model provides a technical scheme does:

an immediate puncture dialysis type nanofiber artificial blood vessel, the tube wall has an inner layer, an outer layer and a nonporous compact coating positioned between the inner layer and the outer layer;

the inner layer is of an electrostatic spinning nanofiber structure; an anticoagulant coating is fixed on the inner wall of the inner layer;

the outer layer is of an electrostatic spinning nanofiber structure;

the nonporous compact coating is internally wrapped with a bending-resistant fold ring, the bending-resistant fold ring is a spiral winding wire with a spiral structure, and the spiral winding wire is spirally wound on the inner layer.

Preferably, the inner diameter of the instant puncture dialysis type nanofiber artificial blood vessel is 2-8 mm.

Preferably, the thickness of the nanofibers of the inner layer is 100-600 microns. The inner layer is made of a high polymer material and polyamino polymer mixed material or a single high polymer material. The inner layer is a nano fiber tube prepared by the electrostatic spinning/spraying method of the first spinning solution.

The first spinning solution is prepared by dissolving a high polymer material and a polyamino polymer or a single high polymer material in an organic solvent according to a mass ratio of (1-9): 1, wherein the total mass volume concentration of the high polymer material and the polyamino polymer or the single high polymer material is 10-30%.

Specifically, the anticoagulant coating is formed by grafting an anticoagulant substance on the inner wall of the nanofiber tube in a covalent grafting mode.

Specifically, the nonporous dense coating has no pores and no delamination.

Preferably, the thickness of the non-porous dense coating is 10-1000 microns. The nonporous compact coating is made of a high polymer material. The nonporous dense coating is formed by applying a spray solution to the outer surface of the inner layer.

The spraying solution is prepared by dissolving a high polymer material in an organic solvent, and the mass volume concentration of the high polymer material is 1-20%.

The coating mode comprises dip coating, cladding coating, vapor deposition and ultrasonic atomization spraying.

Preferably, the diameter of the spiral-wound wire is 0.1 to 1 mm, the pitch is 1 to 6 mm, and the length of the spiral-wound wire is 40 to 5000 mm.

Specifically, the spiral wound wire is prepared by the following method: the melt-extruded wire rod with the diameter of 0.1-1 mm is wound on a stainless steel screw rod with the screw pitch of 1-8 mm, and is fixed into a spiral winding wire with a spiral structure at the high temperature of 100-200 ℃. Wherein the material of the wire is selected from polyurethane, siloxane-terminated polycarbonate, polyethylene terephthalate, or perfluoroethylene propylene copolymer.

Specifically, the partial section of the artificial blood vessel is provided with a bending-resistant ring which forms a bending area of the artificial blood vessel. The regional bending can conveniently be bent according to clinical needs and does not influence the patency of blood, for example is used for arteriovenous fistulization, and does not influence the patency of blood.

Preferably, the outer layer nanofiber has a thickness of 100-500 microns. The outer layer is made of a high polymer material. The outer layer is an electrostatic spinning nanofiber structure which is formed on the outer surface of the nonporous compact coating by a second spinning solution through an electrostatic spinning/spraying method.

The second spinning solution is prepared by dissolving a high polymer material in an organic solvent, and the mass volume concentration of the high polymer material is 1-20%.

The utility model provides an artificial blood vessel, inlayer nanofiber are made with two kinds of different polymers, and sclausura compact layer (middle level) is made by the polymer of one, and outer nanofiber is made by the polymer of one, and the parcel has the bending resistance to roll over the ring in the sclausura compact layer.

The utility model aims at providing a preparation method of instant puncture dialysis type nanofiber artificial blood vessel, its characterized in that, concrete step is as follows:

(1) preparing the first spinning solution into a nano fiber tube (defined as an inner layer) with the thickness of 0.1-1.2 mm by adopting an electrostatic spinning/spraying method;

the first spinning solution is prepared by dissolving a high polymer material and a polyamino polymer or a single high polymer material in an organic solvent according to a mass ratio of (1-9): 1, wherein the total mass volume concentration of the high polymer material and the polyamino polymer or the single high polymer material is 10-30%;

(2) coating the spraying solution on the outer surface of the nanofiber tube to form a nonporous compact coating with the thickness of 0.01-10 mm; winding the bending-resistant folding ring on the outer wall of the nanofiber tube coated with the nonporous compact coating through a spiral winding device, and continuously coating the spraying solution to wrap and fix the bending-resistant folding ring to obtain the nanofiber tube with the bending-resistant folding ring;

the spraying solution is prepared by dissolving a high polymer material in an organic solvent, wherein the mass volume concentration of the high polymer material is 1-20%;

the preparation method of the bending-resistant folding ring comprises the following steps: winding a wire rod with the diameter of 0.1-1 mm, which is extruded by melting, on a stainless steel screw rod with the screw pitch of 1-8 mm, and fixing the wire rod into a spiral winding wire with a spiral structure at the high temperature of 100-200 ℃, thus obtaining the anti-bending ring; the length of the spiral winding wire is 40-500 mm;

(3) preparing a nanofiber layer (defined as an outer layer) with the thickness of 0.1-0.5 mm on the outer surface of the nanofiber tube with the bending-resistant corrugated rings by adopting an electrostatic spinning/spraying method for the second spinning solution; the second spinning solution is prepared by dissolving a high polymer material in an organic solvent, and the mass volume concentration of the high polymer material is 10-30%;

(4) and grafting an anticoagulant substance on the inner wall of the nanofiber tube in a covalent grafting mode to form the anticoagulant coating.

The polymer materials synthesized by electrostatic spinning in the steps (1), (2) and (3) include, but are not limited to, polyurethane (aromatic, aliphatic, etc.), siloxane-terminated polycarbonate (aliphatic, aromatic), nylon, polytetrafluoroethylene, polyvinyl alcohol, polylactic acid, polyethylene, polycaprolactone; the natural polymer material comprises chitosan, collagen, silk fibroin and cellulose;

the polyamino polymer in the step (3) includes but is not limited to polydopamine, multi-arm amino-terminated polyethylene glycol, polyethylene imine, polypropylene imine, and polyimide chloride;

the organic solvent in the steps (1), (2) and (3) is one or more selected from hexafluoroisopropanol, acetone, tetrahydrofuran, dichloromethane, toluene and N, N-dimethylformamide;

the material for bending-resistant ring in step (6) includes, but is not limited to, polyurethane (aromatic, aliphatic, etc.), siloxane-terminated polycarbonate (aliphatic, aromatic), polyethylene terephthalate (PET), and perfluoroethylene propylene copolymer (FEP).

The electrostatic spinning conditions in the steps (4) and (6) are that the speed of a propulsion pump is 0.5-5ml/h, the voltage is-3.00 kv- +20kv, the moving speed of a platform is 10-100mm/s, the acceleration and deceleration time of the platform is 100 plus 9000mms, the environmental temperature is 20-40 ℃, and the relative humidity is 10-70%.

The coating process in the step (6) includes but is not limited to dip coating, cladding coating, vapor deposition, ultrasonic atomization spraying.

Compared with the prior art, the utility model discloses there is following beneficial effect:

(1) the utility model provides an instant puncture type nanofiber artificial blood vessel, the inner wall and the outer wall of the artificial blood vessel prepared by electrostatic spinning are nanofibers, which can fully simulate the structure of natural extracellular matrix, provide good environment for the growth, adhesion and migration of cells, and the higher porosity is favorable for the exchange of nutrient substances; the nanofiber has a large specific surface area, can increase the drug loading rate of anticoagulant substances, and has good elasticity and compliance.

(2) The utility model provides a pair of instant puncture type nanofiber artificial blood vessel has set up a nonporous compact layer between skin and inlayer, and the coating on nonporous compact layer has strengthened artificial blood vessel's antiseep effect and has promoted mechanical properties's promotion. The compact layer has higher elasticity, when the artificial blood vessel is punctured by a puncture needle or a suture needle, the leakage of blood can be prevented, along with taking out the needle, the puncture hole position can be automatically healed, the hemostasis time is shortened, the thrombus formation at the puncture position is reduced, and the service life is prolonged.

(3) The utility model provides a pair of instant puncture type nanofiber artificial blood vessel, the parcel has the bending resistance to roll over the ring in the fine and close coating of sclausura, and the bending resistance is the spiral winding silk that has helical structure, is the heliciform along artificial blood vessel's length direction and twines on the inlayer and form, has increased artificial blood vessel's bending resistance. The bending-resistant folded ring can keep the pipe diameter of a bending area formed by the spiral structure consistent with the pipe diameter of an unbending area, and the blood smoothness is improved. Especially to the bending region of ordinary artificial blood vessel, lead to the easy seepage of puncture hole because of self is tensile, and the utility model discloses an anti-bending is folded the ring and is increased the regional elastic deformation performance of buckling, and anti-bending is folded the ring and is cooperated the sclausura compact layer and enable the regional quick automatic healing of puncture hole of buckling, effectively prevents the seepage of the regional puncture hole of buckling.

(4) The utility model provides a pair of instant puncture type nanofiber artificial blood vessel, ethanol soak and high temperature treatment, make outer fibre compacter, and can withstand stronger mechanical frictional force.

(5) The utility model provides a pair of instant puncture type nanofiber artificial blood vessel, the blood vessel inner wall is through covalence grafting's method with anti-freezing material grafting to the internal surface, the method of physical deposition, ionic bond compares, the utility model discloses a combination is more firm, before artificial blood vessel forms endothelialization, can exert anti-coagulation characteristic, reduces thrombus and narrow formation, prolongs artificial blood vessel's live time.

(6) The utility model provides a pair of instant puncture type nanofiber artificial blood vessel, preferred as vascular graft, more preferred is used for the vascular graft of kidney dialysis.

Drawings

Fig. 1 is a schematic view of the inner wall hierarchical structure of the artificial blood vessel in example 1, mainly showing three-layer structures of an inner layer, a non-porous dense coating and an outer layer.

Fig. 2 is a schematic structural diagram of the shape of the artificial blood vessel, mainly showing the spiral structure and the bending shape of the bending-resistant folded ring in the bending region.

Fig. 3 is a structural diagram of an anticoagulant coating based on covalent bonding of carboxyl and amino reaction.

Fig. 4 is a structural diagram of an anticoagulant coating based on covalent bonding of aldehyde groups and amino groups.

Fig. 5A is the utility model discloses a nanofiber vascular prosthesis has realized the electron scanning picture of self-healing at the puncture position.

Fig. 5B is an electron scan showing that the blood vessel of expanded polytetrafluoroethylene commercially available in example 5 failed to heal at the puncture site.

Description of the symbols in the drawings:

1 is an inner layer;

101 is an anticoagulant coating;

2 is a nonporous compact coating;

201 is a bending-resistant folded ring;

and 3 is an outer layer.

Detailed Description

The technical solution of the present invention will be described clearly and completely below, and it should be understood that the described embodiments are some, but not all embodiments of the present invention. Based on the embodiments in the present invention, all other embodiments obtained by a person skilled in the art without creative efforts belong to the protection scope of the present invention.

Example 1

As shown in fig. 1 to 4, the instant puncture dialysis nanofiber vascular prosthesis has a tube wall having aninner layer 1, anouter layer 3 and a non-porousdense coating 2 between theinner layer 1 and theouter layer 3. Wherein, theinner layer 1 is an electrostatic spinning nanofiber structure, and a layer ofanticoagulation coating 101 is fixed on the inner wall of theinner layer 1; theouter layer 3 is an electrostatic spinning nanofiber structure; the nonporousdense coating layer 2 is wrapped with a bending-resistant fold 201, and the bending-resistant fold 201 is a spiral winding wire having a spiral structure, and the spiral winding wire is spirally wound around theinner layer 1.

The inner diameter of the artificial blood vessel is preferably 4 to 6 mm.

The thickness of the nanofiber of theinner layer 1 of the artificial blood vessel is preferably 100-600 microns. The material of theinner layer 1 may be a high molecular material and a polyamino polymer. Theinner layer 1 is a nano fiber tube prepared by the electrostatic spinning/spraying method of the first spinning solution. The first spinning solution is prepared by dissolving a high molecular material and a polyamino polymer in an organic solvent according to a mass ratio of (1-9): 1, wherein the total mass volume concentration of the high molecular material and the polyamino polymer is 10-30%.

Theanticoagulation coating 101 of the artificial blood vessel is formed by grafting anticoagulation substances on the inner wall of theinner layer 1 in a covalent grafting mode.

The thickness of the non-porousdense coating 2 of the artificial blood vessel is preferably 10 to 1000 microns. The nonporousdense coating 2 is made of a high polymer material. The nonporousdense coating 2 is formed by applying a spray solution to the outer surface of theinner layer 1. The spraying solution is prepared by dissolving a high polymer material in an organic solvent, wherein the mass volume concentration of the high polymer material is 1-20%.

The diameter of the spiral-wound wire is preferably 0.1 to 1 mm, the pitch is preferably 1 to 6 mm, and the length of the spiral-wound wire is preferably 40 to 5000 mm. The partial section of the artificial blood vessel has a bending-resistant loop, which forms a bending region of the artificial blood vessel, and as shown in fig. 2, the region of the middle portion having the bending-resistant loop 201 is a bending region. The regional bending can conveniently be bent according to clinical needs and does not influence the patency of blood, for example is used for arteriovenous fistulization, and does not influence the patency of blood.

The nanofiber thickness of theouter layer 3 is preferably 100-500 microns. The material of theouter layer 3 is a high polymer material. Theouter layer 3 is an electrostatic spinning nanofiber structure which is formed on the outer surface of the nonporouscompact coating 2 by using a second spinning solution through an electrostatic spinning/spraying method. The second spinning solution is prepared by dissolving a high polymer material in an organic solvent, wherein the mass volume concentration of the high polymer material is 1-20%.

Example 2

This example describes the construction and manufacturing method of an artificial blood vessel.

14.4 g of polyurethane and 1.6 g of tetraamine aminopolyethylene glycol were dissolved in 100ml of N, N-dimethylformamide solution as an inner layer electrospinning/spraying solution. 16 g of polyurethane was dissolved in 100ml of a 1:1 solution of N, N-dimethylformamide and toluene as the outer electrospinning/spraying solution. Polyurethane 10 g was dissolved in 100ml of dichloromethane as a dense layer spray solution.

The nanofiber layer with the thickness of 600 microns is manufactured by using an inner layer electrostatic spinning/spraying solution through an electrostatic spinning method to serve as an inner layer, a compact coating with the thickness of 40 microns is coated through an ultrasonic atomization spraying process, then an anti-bending ring with the wire diameter of 0.3 mm and the screw pitch of 4 mm is fixed on the surface of the compact coating through a winding device, and then the anti-bending ring is fixed by coating the spraying solution with the thickness of 10 microns. An outer layer with a thickness of 150 microns was made on the outer surface of the dense coating by electrospinning using an outer layer electrospinning/spraying solution. The structure is shown in figure 1. The degree of bending resistance is shown in fig. 2.

Example 3

Based on the method for preparing an artificial blood vessel shown in example 2, 14.4 g of polyurethane and 1.6 g of polyethyleneimine were dissolved in 100ml of a N, N-dimethylformamide solution as an inner layer electrospinning/spraying solution. 20 g of polyurethane was dissolved in 100ml of a 1:1 solution of N, N-dimethylformamide and toluene as the outer electrospinning/spraying solution. Polyurethane 10 g was dissolved in 100ml of methylene chloride as a dense layer solution.

The method comprises the steps of manufacturing a nanofiber layer with the thickness of 600 microns as an inner layer by using an inner layer electrostatic spinning/spraying solution through an electrostatic spinning method, coating a compact coating with the thickness of 40 microns through an ultrasonic atomization spraying process, fixing the anti-bending folding ring with the wire diameter of 0.3 mm and the screw pitch of 4 mm on the surface of the compact coating through a winding device, and coating the spraying solution with the thickness of 10 microns to cover and fix the anti-bending folding ring. An outer layer with a thickness of 150 microns was made on the outer surface of the dense coating by electrospinning using an outer layer electrospinning/spraying solution.

The resulting artificial blood vessel was cross-linked with 0.5% glutaraldehyde solution for 30 minutes and washed with deionized water for 20 minutes. Freeze-drying at-70 deg.C for 24 hr to obtain nanofiber artificial blood vessel with inner layer containing amino group.

Example 4

Preparation of heparin-coated nanofiber vascular prostheses according to example 2

0.2 g MES is dissolved in 20 ml deionized water to prepare MES buffer solution, and 0.2 g EDC, 0.26 g NHS and 0.66 g heparin are added in turn to be protected from light and treated for 15 minutes at the constant temperature of 37 ℃. The artificial blood vessel in theembodiment 2 is soaked and soaked in the heparin buffer solution, reacts for 24 hours at 37 ℃, is taken out and washed by deionized water for three times, and is frozen and dried for 24 hours at-70 ℃ to prepare the nano-fiber artificial blood vessel with the heparin coating. The coating structure is shown in fig. 3.

Example 5

Preparation of heparin-coated nanofiber vascular prostheses based on example 3

Dissolving 5 g of heparin in 100ml of 6% acetic acid solution, adding 0.2 g of sodium nitrite, adjusting the pH value to 2-4, heating in a water bath at 25 ℃, reacting for 2-4h, adjusting the pH value to 8-10 to stop the reaction, dialyzing for 48h by a 3500MWCO dialysis bag, and freeze-drying to obtain powdered aldehyde heparin. The nanofiber-modified blood vessel obtained in example 3 was immersed in an aqueous solution of 0.5% polyethyleneimine at a pH of 8 to 10 for 15 minutes, then rinsed with deionized water at a pH of 8 to 10 for 30 minutes, further immersed in a solution of 0.05% glutaraldehyde at a pH of 8 to 10 for 15 minutes, then immersed in a solution of 0.5% polyethyleneimine at a pH of 8 to 10 for 15 minutes, and then removed and rinsed with deionized water at a pH of 9.6 for 15 minutes. Soaking in a solution of sodium cyanoborohydride with pH of 8-10 for 15 minutes, and rinsing with deionized water for 30 minutes. The above steps are repeated once more. Immersing the treated material in a dextran sulfate solution with the pH value of 2-4, carrying out constant temperature treatment at 60 ℃ for 90 minutes, then washing with deionized water for three times, immersing in 0.5 percent polyethyleneimine with the pH value of 8-10, carrying out treatment for 45 minutes, and then washing with deionized water for 20 minutes. Immersing the treated tube into an aldehyde heparin solution, treating at 40-60 ℃ for 2h, then adding a small amount of sodium cyanoborohydride solution with the pH value of 3-4, washing with deionized water, covalently grafting aldehyde heparin onto the inner layer of the nanofiber artificial blood vessel, and freeze-drying at-70 ℃ for 24 h to prepare the nanofiber artificial blood vessel coated with heparin. Sterilizing and storing the epoxy ethane. The coating structure is shown in fig. 4.

Example 6

Nanofiber artificial blood vessel and expanded polytetrafluoroethylene blood vessel in-vitro puncture experiment prepared based on example 2

The nanofiber artificial blood vessel prepared in example 2 and a commercially available expanded polytetrafluoroethylene blood vessel were repeatedly punctured with a 16-gauge puncture needle, and the morphology of the puncture hole of the fiberscope tube was electronically scanned. As shown in fig. 5A, 5B. Fig. 5A shows that the nanofiber vascular prosthesis of the present invention achieves self-healing at the puncture site; fig. 5B shows that the surface of the blood vessel of commercially available expanded polytetrafluoroethylene leaves a non-healing puncture. It can be concluded that the nanofiber vascular prosthesis can reduce bleeding at the puncture site after implantation.

In summary, the above embodiments are only preferred embodiments of the present invention, and are not intended to limit the scope of the present invention, and any modifications, equivalent replacements, improvements, etc. made within the spirit and principle of the present invention should be included in the scope of the present invention.

Claims (8)

1. An immediate puncture dialysis type nanofiber artificial blood vessel is characterized in that the wall of the vessel is provided with an inner layer, an outer layer and a non-porous compact coating positioned between the inner layer and the outer layer;

the inner layer is of an electrostatic spinning nanofiber structure; an anticoagulant coating is fixed on the inner wall of the inner layer;

the outer layer is of an electrostatic spinning nanofiber structure;

the nonporous compact coating is internally wrapped with a bending-resistant fold ring, the bending-resistant fold ring is a spiral winding wire with a spiral structure, and the spiral winding wire is spirally wound on the inner layer.

2. The prosthesis of claim 1, wherein the prosthesis has an inner diameter of 2-8 mm.

3. The prosthesis of claim 1, wherein the nanofiber of the inner layer has a thickness of 100-600 microns.

4. The artificial blood vessel of claim 1, wherein the anticoagulant coating is formed by grafting an anticoagulant substance onto the inner wall of the inner layer by means of covalent grafting.

5. The prosthesis of claim 1, wherein the non-porous dense coating has a thickness of 10 to 1000 microns.

6. The prosthesis according to claim 1, wherein the spiral-wound wire has a diameter of 0.1 to 1 mm, a pitch of 1 to 6 mm, and a length of 40 to 5000 mm.

7. The prosthesis of claim 1, wherein the partial section of the prosthesis is provided with bending-resistant loops forming a bending region of the prosthesis.

8. The artificial blood vessel of claim 1, wherein the outer layer of nanofibers has a thickness of 100-500 microns.

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