JPS61238238A - Production of artificial blood vessel - Google Patents

Abstract

(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

DETAILED DESCRIPTION OF THE INVENTION [Field of Industrial Application] The present invention relates to a method for manufacturing an artificial blood vessel having porosity and compliance similar to that of a biological blood vessel, which is made of an elastomer reinforced with a tubular material composed of m. .

[Background Art] In recent years, along with advances in vascular surgery, research on artificial blood vessels has progressed, and a large number of artificial blood vessels have been developed. Currently, artificial blood vessels for medium- or large-diameter arteries with an inner diameter of about 6 m or more are available, such as Dobesky artificial blood vessels made of Dacron knitted fabric manufactured by υSC1 in the US, and expanded polytetrafluoroethylene (hereinafter referred to as EPTFE) manufactured by Boa in the US. ) is used clinically. These artificial blood vessels have a hole that communicates from the inside to the outside of the blood vessel, and after being implanted in a living body, they are immediately covered with pseudoendothelium, and tissue enters from the living tissue side through this hole and stabilizes. It has been transformed into an organ and is fulfilling its mission as an artificial blood vessel. Having communicating pores that are useful for organizing the artificial blood vessel in this way is hereinafter referred to as having porosity. However, since the compliance of these artificial blood vessels is significantly different from that of biological blood vessels, a long period of time after implantation into a living body causes various problems related to incompatibility such as hyperplasia of pannus at the anastomotic site. In addition, when used as a small-diameter artificial blood vessel with an inner diameter of approximately 6M or less, differences in compliance will be noticeable, and patency (resistance to blood vessel clogging) will be poor.
Not for clinical use. Therefore, autologous arteries are used in revascularization surgeries for arteries below the knee, coronary arteries, and the like.

Based on the above, when developing artificial blood vessels, especially small-diameter artificial blood vessels, in addition to improving the porosity of the artificial blood vessels and the blood compatibility of the artificial blood vessel materials, it is necessary to improve the compliance of the artificial blood vessels with the living body. It is said that it is important to approximate blood vessels.

However, the compliance of currently developed artificial blood vessels is limited by the report by Sasashima et al. (Artificial Organs 12[1), 179-1
82.1983), as shown in Table 1.

[See table 1 below for margins] As described above, the compliance of current artificial blood vessels is extremely small compared to the arteries of living organisms, and they are considered to be accessory vessels to the arteries.

In order to resolve this discrepancy in compliance between living blood vessels and artificial blood vessels, US Pat. Disclosures have been made regarding methods of manufacturing vascular grafts with similar compliance. However, this artificial blood vessel has no porosity.

Moreover, the compliance of artificial blood vessels manufactured using this method has only very small pores in the cross section of the vessel wall, and has a relatively dense structure, so although the compliance is greater than that of conventional artificial blood vessels, It still tends to be small compared to that of .

The present inventor has developed a method for manufacturing an artificial blood vessel with a porous structure made of an elastomer that solves the problem of compliance discrepancies and has porosity that is optimal for organization, and has filed a patent application. (Patent application 59-51768
No. Specification).

[Problems to be Solved by the Invention] As shown in Figure 1 (I), the stress-strain curve of the artificial blood vessel manufactured by the method developed by the present inventor exceeds the normal blood pressure range. When a high stress is applied, it becomes different from that of a biological blood vessel (circle and ■ in Fig. 1). Therefore, when abnormally high blood pressure occurs, such as during surgery, there are concerns about rupture or damage, and concerns about maintaining durability over a long period of time. The present invention has been made in order to eliminate the above-mentioned concerns.

[Means for Solving the Problems 1] In view of the above-mentioned circumstances, the present inventors have developed a method that, in addition to having porosity and compliance similar to that of living blood vessels,
After extensive research into a method for manufacturing artificial blood vessels that can withstand abnormally high blood pressure and have excellent long-term durability, we discovered that in a method for manufacturing artificial blood vessels with a porous structure made of elastomer, a tubular material made of fibers was developed. The present invention was completed based on the discovery that the above object can be achieved by combining the following as a reinforcing material.

That is, the present invention provides a method for manufacturing an artificial blood vessel by repeating once or twice an operation of coating a mandrel with an elastomer solution in which a pore-forming agent is dispersed, and then immersing the mandrel in a coagulation solution. The present invention relates to a method for producing an artificial blood vessel, characterized in that a tubular object made of fibers is placed on the mandrel at any stage of the present invention.

(Example) The pore-forming agent used in the present invention is insoluble in the solvent in which the elastomer is dissolved (hereinafter referred to as a good solvent), and can be removed during or after molding of the artificial blood vessel.

When considering use in artificial blood vessels to be implanted in a living body, it is preferable to use a pore-forming agent that is safe for the living body. Therefore, as the pore-forming agent, inorganic salts such as common salt and calcium carbonate, water-soluble saccharides such as glucose and starch, or proteins are preferable. However, inorganic salts such as table salt and water-soluble saccharides are essentially hygroscopic, so making them finer particles increases their surface area and tends to cause secondary aggregation due to moisture in the air. It is necessary to pay sufficient attention to handling. On the other hand, even if proteins are made into fine particles, they do not cause secondary aggregation due to moisture in the air, and can be uniformly and stably dispersed. Therefore, proteins are particularly preferred as pore-forming agents.

Furthermore, when a protein is used, the pore-forming agent can be easily dissolved and removed from the molded artificial blood vessel using an alkaline solution, an acid solution, a solution containing an enzyme, or the like.

Specific examples of such preferred proteins include casein, collagen, gelatin, albumin, etc.
Among these, casein is particularly preferred.

The particle size of the pore-forming agent is preferably 740,000 um or less, more preferably 50 um or less, and particularly preferably 30 um or less. The particle size here refers to the length of one side of the mesh of the sieve, and refers to the particles classified by these sieves. When the particle size is larger than 74 mm, the pores of the porous structure tend to become too large.

The amount of the pore-forming agent used varies depending on the required porosity, the particle size of the pore-forming agent, or the composition of the elastomer solution, and therefore cannot be determined generally, but is preferably between 20 and 500%. (volume % of pore-forming agent/elastomer, the same applies hereinafter), more preferably 50 to 350%, particularly preferably 100 to 300%. The amount of pore forming agent is 500%
If it exceeds this, the porosity tends to become too large and the viscosity of the elastomer solution tends to become too high. On the other hand, when the amount of the pore-forming agent is less than 20%, the porosity tends to become poor.

The elastomer used in the present invention is a thermoplastic elastomer with excellent blood compatibility, that is, it does not contain low-molecular eluates that can cause acute toxicity, inflammation, hemolysis, exothermic reactions, etc., and does not cause serious damage to blood physiological functions. It is a thermoplastic elastomer impregnated with antithrombotic properties. Examples of such elastomers include polystyrene elastomers,
Examples include polyurethane elastomers, polyolefin elastomers, polyester elastomers, etc.
These may be used alone or in combination of two or more. Furthermore, since the elastomer used in the present invention only needs to have properties as an elastomer when molded into an artificial blood vessel, a composition of the above-mentioned elastomer (resin) and a resin that does not have properties as an elastomer may be used. However, if the final molded product has properties as an elastomer, it can be used as the elastomer used in the present invention.

Among the above-mentioned elastomers, polyether-type segmented polyurethane (including segmented polyurethane urea) is used because of its excellent strength, elongation, durability, and antithrombotic properties.

The same applies hereinafter) is more preferable. Further preferred are segmented polyurethanes containing fluorine in the hard or soft segments, and segmented polyurethanes containing polydimethylsiloxane in the main chain as disclosed in JP-A-57-211358. Particularly preferred is polydimethylsiloxane as a part of the soft segment. Alkylene groups such as methylene, alg is 0 to
30 integers, b, c.

e and f are 0 or 1, and d is an integer of 2 or more).

A good solvent for preparing the elastomer solution used in the present invention varies depending on the type of elastomer and cannot be determined unconditionally, but examples include N,N-dimethylacetamide, N,N-formamide, N-methyl-2 Examples include solvents such as -pyrrolidone, dioxane, and tetrahydrofuran, and these may be used alone or as a mixed solvent.

The elastomer solution used in the present invention has a pore-forming agent, an elastomer, and a good solvent as essential components, but if necessary, a solvent that does not dissolve the elastomer (hereinafter referred to as a "poor solvent") may be added to the extent that the elastomer does not undergo a phase change. You may.

The solidification rate of the elastomer solution can be increased by adding a poor solvent.
Appearance shape, porosity, etc. can be adjusted.

Examples of such poor solvents include water, lower alcohols, ethylene glycol, propylene glycol,
．． Examples include 4-butanediol and glycerin, and one or more of these can be used.

The coagulating liquid used in the present invention may be substantially a poor solvent. Examples include water, lower alcohols, ethylene glycol, propylene glycol, 1,4-butanediol, glycerin, etc., and these may be used alone or in combination of two or more. Among these, preferred are water, ethylene glycol, propylene glycol, or poor solvents containing these as main components, and more preferred are 99 to 50 volume % of the poor solvent and 1 to 50 volume % of a good solvent. This is the mixed solvent added. This is because, by adding a good solvent to the coagulation liquid, porosity can be easily obtained, probably because the coagulation rate of the elastomer solution in the coagulation liquid is slowed down.

The mandrel used in the present invention is not particularly limited as long as it is not dissolved in the elastomer solution.

For example, glass rods with smooth surfaces, Teflon rods, or stainless steel rods are suitable. It goes without saying that by using a mold of any shape in place of the mandrel, various medical molded objects other than tubular molded objects can be manufactured by the method of the present invention. For example, if a flat plate is used as a mold, a film-like molded product can be obtained, which can be used for things such as artificial skin.

The fibers used in the present invention are used to make threads, nets, ropes, woven fabrics, knitted fabrics, braided fabrics, nonwoven fabrics, etc.
It is a slender and long object more than twice as long.

The fibers are particularly limited, regardless of whether they are organic or inorganic, as long as they are safe for living organisms, have negligible deterioration in vivo, can withstand sterilization, and can be processed into desired tubular products. It can be used without any problems. In terms of processability, ease of availability, flexibility, uniformity, etc., recycled artificial Il fibers, semi-synthetic fibers, and synthetic fibers are preferred. Specific examples of these include cellulose, protein, polyamide, polyester, polyurethane, polyethylene, polystyrene, polyvinyl chloride, polyvinylidene chloride, polyfluoroethylene, polyacrylic, and polyvinyl. Examples include alcohol-based m-fibers. Among these, stretchable fibers are more preferable,
Specific examples include those in which the TM fiber itself is stretchable, such as rubber-based, polyurethane elastic-based, and polyester elastic-based fibers, and stretchable bulky yarns such as woolly nylon and woolly detron. and covered yarn, which is a yarn made by stretching rubber or spandex filaments and wrapping them around other spun yarns or filaments.

The tubular material made of fibers used in the present invention refers to the above-mentioned l!
woven fabrics, knitted fabrics, braided fabrics, nonwoven fabrics, and combinations of these; A tubular product made of a sponge-like material such as polyurethane foam. When the tubular object is combined with a porous structure made of elastomer, there is no particular limitation as long as the tubular object has a compliance similar to that of a living blood vessel, but the stress-strain curve will be similar to that of a living blood vessel (Fig. 1). It is preferable to use one that approximates l and ■). Such properties of the tubular article can be achieved, for example, by the following two methods alone or in combination. The first method is to loosely adjust the frequency and combination points of fibers.

The second method is to use stretchable fibers. The tubular material is made of fiber or mr! ! It may be formed into a tubular structure by itself, or it may be combined with a porous structure part made of an elastomer to form a tubular structure when it is made into an artificial blood vessel. From the viewpoint of processability, workability, and obtaining compliance and stress-strain curves similar to biological blood vessels, it is preferable to use a tubular product made of knitted fibers, and preferably a tubular product made of stockinette knitted stretchable fibers. is even more preferable.

Next, the method for manufacturing an artificial blood vessel of the present invention will be explained based on one embodiment.

After coating the mandrel with an elastomer solution in which a pore-forming agent is dispersed, the mandrel is repeatedly immersed in a coagulation solution once or twice or more to precipitate the elastomer. A tubing is present on the mandrel.

Once a tubular product having a predetermined thickness is obtained, an artificial blood vessel can be obtained by sufficiently removing the solvent, extracting the mandrel, and removing the pore-forming agent.

Among the manufacturing methods of the present invention, the most typical method of placing a tubular object made of fibers on the mandrel is a method of covering the mandrel with a tubular material having a tubular structure made of fibers, or a method of covering the mandrel with a tubular material having a tubular structure made of fibers, or a method made of fibers or au. This is a method in which a strip or the like is wrapped around a mandrel to form a tubular structure. The tubular material made of the fibers may be placed directly on the mandrel, or may be provided on the mandrel on which the elastomer has been deposited, but after the tubular material is present on the mandrel on which the elastomer has been deposited, , coating of the elastomer solution and precipitation of the elastomer are preferably repeated one or more times.

The inside of the artificial blood vessel manufactured by the method of the present invention, that is, the blood contact surface, is composed of an elastomer soaked in blood compatibility, and although it has good blood compatibility, it is difficult to implant it into a living body. In order to further improve the initial antithrombotic properties, albumin, gelatin, and chondroitin tiiH! are added to the inner surface of the artificial blood vessel. , heparinized material, etc. may be coated.

The wall of the artificial blood vessel manufactured by the method of the present invention explained above has a porous structure made of elastomer! It consists of a tubular moving part consisting of lll1. In the porous structure made of the elastomer, pores exist over the entire thickness from the inside to the outside of the tube wall. At least a portion of the eye hole communicates with each other, and at least a portion of the eye hole opens outward on the inner surface and the outer surface, and has a porous property. The septum forming the eye opening is made of elastomer and is continuous. Further, the partition wall itself contains a large number of minute pores and pores formed therein as the good solvent and coagulating liquid are replaced. Such a partition wall has a sparse structure, which is preferable for obtaining an artificial blood vessel having a compliance and stress-strain curve similar to that of a living blood vessel. Although it is difficult to manufacture partition walls having such a sparse structure by drying a solution coating or from a molten state, it can be easily manufactured by the manufacturing method of the present invention.

The artificial blood vessel manufactured by the method of the present invention can have a compliance that matches that of a living blood vessel when the inner diameter of the pipe and the thickness of the wall of the pipe are matched to that of the living blood vessel.

Compliance as referred to herein means formula (1): C=
Δv×100(1) (In the formula, C is compliance, vO is internal pressure 50mmH
The internal volume of the measured blood vessel when g, ΔP is the internal pressure 50 imHg
10 (lolfllH) from to internal pressure 150ma+Ha
! II, ΔV is from internal pressure 50118O to internal pressure 150111
H1) is the internal volume of the measured blood vessel that increases during the period up to H1). For specific measurements, a measurement blood vessel is inserted into a closed circuit, a liquid is injected into this circuit using a constant-motion pump, and the amount of injected liquid and the change in pressure within the circuit are measured.
Obtain compliance from equation (1).

However, when measuring a porous artificial blood vessel, it is necessary to close the communicating holes in the vessel wall by preclotting or the like.

The compliance of living blood vessels varies depending on the diameter of the artery, vein, blood vessel, etc. Therefore, the preferable compliance for an artificial blood vessel varies depending on the caliber of the artificial blood vessel, the site of use, etc. - Although it cannot be determined generally, the artificial blood vessel of the present invention can be manufactured to have a compliance similar to each biological blood vessel. . Compliance of living blood vessels where normal revascularization surgery is performed is 01-08
Since it is about 8, it is considered that it is more preferable to set it in such a range. The compliance of the artificial blood vessel of the present invention can be adjusted as described above,
Any product within the range of ~038 can be manufactured.

Artificial blood vessels with a compliance of 0.1 to 0.8 are suitable for applications such as arterial blood vessels, depending on their thickness, and those with an inner diameter of 1 to 6 #IIl and compliance of 0.1 to 0.8.
0.5 is suitably used as an artificial blood vessel for small ostium arteries.

The artificial blood vessel manufactured by the method of the present invention is porous,
Compliance approximates that of biological blood vessels. Furthermore, since it is reinforced with a tubular material made of fibers, it will not break or damage even if abnormally high blood pressure occurs during surgery or if strong external force is applied, ensuring long-term durability. It is also good for maintaining sex.

In addition to these properties, it also has the following useful properties. First, the blood contact surface is made of an elastomer with excellent antithrombotic properties, and the contact surface has no irregularities that would disturb blood flow, so it has excellent blood compatibility.

Furthermore, since the tube wall is essentially a continuous elastomer structure, the cut end will not fray even if it is cut to an arbitrary length. In addition, because the cross section of the tube wall has a structure with low elastomer density, suture needle penetration is very good, making it easy to suture with living blood vessels, and even if the suture is pulled, the suture will not fray or the suture will come off. Never. Moreover, since the tube wall is made of an elastomer, the suture's penetrability also self-occlusions in the absence of the needle, preventing blood leakage. As a further surprising property, the artificial blood vessel according to the present invention has
Nodules do not form when blood flows inside and pressure is applied. This is considered to be due to the fact that the compliance is similar to that of living blood vessels.

As described above, the method for manufacturing an artificial blood vessel of the present invention has the following features.

■Manufacture and manufacture porous artificial blood vessels.

■Manufacture artificial blood vessels with compliance similar to biological blood vessels.

■It is possible to manufacture artificial blood vessels that can withstand abnormally high blood pressure and have excellent long-term durability.

■An artificial blood vessel that satisfies the following basic properties as an artificial blood vessel can be manufactured.

・Blood contact surface has excellent blood compatibility.

・The suture needle has very good penetrating properties, making suturing easy.

・Even when cut to any length, the cut end will not fray.

・The suture thread will not come undone from the suture area.

・The suture needle's through hole self-closes.

・Nodules are less likely to form under high blood pressure.

Therefore, the artificial blood vessel manufactured by the method of the present invention can be used for revascularization surgery, such as artificial blood vessels, bypass artificial blood vessels,
Can be used for batch materials, and can also be used for blood access, etc. Further 0.1-0.8
It can be used as an arterial artificial blood vessel with a compliance of In particular, the compliance is close to that of biological blood vessels, and the blood contact surface has excellent blood compatibility, so there are currently no artificial blood vessels in clinical use.
．． It has a compliance of 5, and can also be used as a small-caliber arterial artificial blood vessel with an inner diameter of approximately 1 to 6M. In particular, it can be suitably used for revascularization of arteries below the knee and as an artificial blood vessel for aorta-coronary artery bypass.

Furthermore, the artificial blood vessel according to the present invention can be used as a venous artificial blood vessel by covering the outside with a net with low compliance, and can also be used as a substitute for soft tubular objects in living bodies such as ureters. be.

Next, the method for manufacturing an artificial blood vessel of the present invention will be explained based on Examples.

Example 1 4.4′-diphenylmethane diisocyanate 27,3
After synthesizing a prepolymer using 5 parts by weight (the same applies hereinafter) and 54.7 parts of polyoxytetramethylene glycol (molecular weight 2000), 4.7 parts of ethylene glycol
5 parts and both terminal polyethylene glycol polydimethylsiloxane (average molecular weight of polyethylene glycol at both ends 681, average molecular weight of polydimethylsiloxane 11040
) Chain extension was performed using 13.2 parts to synthesize a segmented polyurethane containing polydimethylsiloxane in the main chain.

The tensile strength of the obtained polyurethane is 350Kt/cri,
The elongation was 670x, and the critical surface tension determined from the Zisman plot was 28 dyn/cta.

Dioxane 50d and N,N-dimethylacetamide 3
casein with a particle size of 30J or less in a mixed solvent with 0d.
5SJ was stirred and dispersed using a homogenizer, and then the polyurethane 159 was added and stirred and dissolved. A glass rod with a diameter of 3 m was immersed in this dispersion solution, then taken out, and the dispersion solution was uniformly coated onto the glass rod. This mandrel was immersed in ethylene glycol to precipitate the elastomer.

Next, using covered yarn made by wrapping 70 denier nylon fibers around 20 denier spandex,
A tube approximately 3 m in diameter knitted by a ribbon knitting machine with a needle head was placed over the glass rod on which the elastomer was deposited. After immersing the glass rod in the dispersion solution and taking it out and applying the dispersion solution to the surface,
It was immersed in the coagulation solution. After the elastomer was sufficiently deposited, the mandrel was taken out and the coagulated liquid on the surface was removed.

Furthermore, after depositing the dispersion solution on the mandrel in the same manner as described above, the elastomer was precipitated in the interrogation solution. After that, the glass rod was thoroughly washed with water and the glass rod was removed to obtain a composite tubular product. This composite tubular article was immersed in an aqueous sodium hydroxide solution having a pH of 13.5 to extract and remove casein, and finally thoroughly washed with water to obtain an artificial blood vessel according to the present invention.

The obtained artificial blood vessel had an inner diameter of approximately 3M and an outer diameter of 4.5 mm. When this artificial blood vessel was observed using a scanning electron microscope, it was found that there were about 20 to 30 circular to oval holes on the inner surface, and about 1 to 10 circular to irregularly shaped holes on the outer surface. There were holes. The cross-section of the tube wall contained a tubular material made of fibers in the center, and the remaining elastomer part had a network structure of connected elastomers that formed the partition walls of the pores.

Next, when water was passed through this artificial blood vessel at a water pressure of 120 mmHg, the result was approximately 50 ai per minute per 1 cm of the inner surface of the artificial blood vessel! It was found that water penetrated into the outer surface of the artificial blood vessel, making it porous.

Next, this artificial blood vessel was pre-clotted with live blood, cut into 8 cm lengths, inserted into a closed circuit, and fed with a metering pump that pumped 0.057 ml per stroke of bovine ACD blood into the closed circuit. The change in internal pressure was measured.

From the stroke number of the metering pump and the change in internal pressure, (1)
Compliance was measured using the formula and found to be 0.30.

The stress-strain curve of this artificial blood vessel was calculated using Shimadzu Autograph l52.
000, the graph of (I[) shown in FIG. 1, which approximates a biological blood vessel, was changed.

Next, when this artificial blood vessel was transplanted to a length of approximately 7 cm into the femoral artery of an adult mongrel, it showed a patency of more than 2 months.

Furthermore, even if this artificial blood vessel was cut at any point, the cut portion did not fray, and the sutureability was excellent, and the through hole of the suture needle self-occluded when the needle was removed.

In addition, the artificial blood vessel had a tendency to be less likely to form knots in the presence of an internal pressure of 50 to 15011 H (J).

From the above, it can be seen that this artificial blood vessel is excellent, especially as an artificial blood vessel for small diameter arteries.

Example 2 50 g of calcium carbonate having an average particle size of 4- and the segmented polyurethane 109 of Example 1 were stirred and dissolved in a mixed solvent of dioxane 50Id and N,N-dimethylacetamide 50d. A glass rod with a diameter of 3 #lIm was immersed in this dispersion solution and then taken out, and the solution was uniformly coated onto the glass rod.

This mandrel was immersed in probilin glycol to precipitate the elastomer. After performing this operation again, 5
Diameter: 3 knitted using ribbon knitting with 24 needle heads using 0 denier woolly processed polyester fiber.
A #I tubing was placed over a glass rod with the elastomer deposited on its surface. The glass rod was immersed in the dispersion solution and then taken out, the surface of the glass rod was coated with the dispersion solution, and then immersed in the coagulation solution. After the elastomer was sufficiently deposited, the glass rod was removed to obtain a composite tubular article. After washing this composite tubular article with water, it was immersed in a 1N hydrochloric acid aqueous solution to dissolve and remove calcium carbonate, and finally thoroughly washed with water to obtain an artificial blood vessel according to the present invention.

The obtained artificial blood vessel had an inner diameter of 31I11 and an outer diameter of 4.0mm. When this artificial blood vessel was observed using a scanning electron microscope, it was found that there were about 8 to 10 circular to oval shaped holes on the inner surface, and about 1 to 10 circular to irregularly shaped holes on the outer surface. Were present. A tubular material made of fibers was incorporated in the outer portion of the tube wall cross section, and the remaining elastomer portion had a network structure.

The effectiveness, compliance, and stress-strain curve of this artificial blood vessel were measured in the same manner as in Example 1.

Efficacy was 101 d/cIi in 1 minute and compliance was 0.5. The stress-strain curve was similar to the N graph shown in FIG.

[Brief explanation of the drawing]

Figure 1 shows an artificial blood vessel with a porous structure (graph (I))
, the artificial blood vessel obtained in Example 1 (graph (I)), the thoracic aorta (graph (II)) and the carotid artery (graph (M)).
) is a graph showing each stress-strain curve. 1 year old

Claims (1)

[Claims] 1. When manufacturing an artificial blood vessel by coating the mandrel with an elastomer solution in which a pore-forming agent is dispersed, and then repeating the operation of immersing the mandrel in a coagulation solution once or twice,
A method for manufacturing an artificial blood vessel, characterized in that a tubular object made of fibers is placed on the mandrel at any stage of the operation.