JPH02147065A - Catheter and medical tube - Google Patents

Abstract

PURPOSE:To facilitate the insertion of the catheter into a blood vessel and to lessen the generation of thrombosis by using a porous tube made of a resin as a catheter base body and admitting a synthetic resin into the narrow pores of the porous tube and fixing a lubricative material onto the surface of the synthetic resin. CONSTITUTION:The catheter 1 is formed by using the porous tube 2 made of the resin as the catheter base body, admitting the synthetic resin 3 having an adhesive property to the resin forming the tube 2 into the narrow pores of the tube 2 and further fixing the water soluble high-polymer material 4 or its deriv. having lubricity at the time of wetting onto the surface of this synthetic resin 3. The resistance between the catheter and the inside wall of the blood vessel is, therefore, low and the insertion is easy at the time of the insertion to the blood vessel. The generation of the thrombosis is lessened and the plasma protein adheres less to the tube even if the tube is held in contact with blood over a long period of time. The increase of the outside diameter and the possibility of clogging of the internal lumen are obviated. The synthetic resin admitted into the narrow pores of the porous tube has a reactive functional group making ion bond or covalent bond with the lubricative material. The resin forming the porous tube is preferably fluoroplastic.

Description

DETAILED DESCRIPTION OF THE INVENTION [Industrial Field of Application] The present invention is used as a catheter for vascular introduction used by being introduced into a blood vessel in the treatment or examination of an affected area within a blood vessel, or as a tube body of such a catheter. Regarding medical tubes.

[Prior Art] Conventionally, vascular introduction catheters have been used to treat affected areas within blood vessels,
In examinations, it is mainly used for the injection of liquid medicines, contrast agents, etc.

Such a catheter includes, for example, a catheter with an expandable body used to treat an intravascular stenosis by expanding the stenosis and improving blood flow on the distal side of the stenosis. Specifically, there are those shown in Japanese Unexamined Patent Publication No. 54-70683 and International Publication No. WO38/6465.

The catheter is made of flexible synthetic resin so that it can be inserted into a blood vessel. As catheters to be inserted into such blood vessels, catheters with smaller diameters that can be easily inserted into highly stenotic areas and more distal blood vessels are also being sought after. However, since flexible resin is used, a certain degree of wall thickness is required in order to provide the necessary physical properties to the catheter, making it difficult to reduce the diameter.

Therefore, a catheter using a partially porous tube composed of a partially solid fleshy part and a porous fleshy part of the tube using PTFE resin has been considered. Publication number 60-51912). In this catheter, by using P i'FE resin, the wall thickness of the catheter can be made thin. However, since the outer surface of the porous portion is not a smooth surface, thrombi are likely to occur, and furthermore, there is a large resistance during insertion, and there is a risk of damaging the 1 m tube wall.

Furthermore, since blood flows into the pores of the porous part, if it comes into contact with the TFN fluid for a long period of time, there is a risk that the outer diameter will increase due to the attachment of FFF1 protein in the blood and the internal lumen may become clogged. It was highly sexual.

Therefore, an object of the present invention is to use a porous tube made of a relatively hard synthetic resin, to make the wall thickness sufficiently thin, and to make it possible to make a catheter with a smaller diameter. , catheters and medical tubes that are easy to insert into blood vessels, are less prone to thrombus formation, have less plasma protein adhesion even when in long-term contact with blood, and do not have an enlarged external shape or blockage of the internal lumen. This is what we provide.

[Means for solving the above problems] The above object is achieved by using a porous resin tube as a catheter base, and having adhesiveness with the resin forming the tube in the pores of the porous tube. It is a catheter into which a synthetic resin flows, and a lubricating substance is further fixed on the surface of the synthetic resin.

The synthetic resin flowing into the pores of the porous tube has, for example, a reactive functional group that forms an ionic or covalent bond with the lubricating substance. Moreover, the synthetic resin flowing into the pores of the porous tube is, for example, +1i? It contains a compound having reactive functionalities J and t that form an ionic or covalent bond with the WE lubricating substance. Furthermore, it is preferable that the synthetic resin flowing into the pores of the porous tube is a soft synthetic resin. Furthermore, it is preferable that the resin forming the porous tube is a fluorine-based synthetic resin.

Furthermore, the tube base is a medical tube body formed of a synthetic resin, and the outer surface of the tube body is exposed, and the tube body has a plurality of tube bodies on the outer surface. The recesses or holes of the tube are filled with a synthetic resin different from the synthetic resin that forms the tube body, and a lubricating substance is fixed to the outer surface of the filled synthetic resin tube. This is a tube for use.

Preferably, the medical tube body is made of antithrombotic material. Furthermore, it is preferable that the tube body is formed of a resin or a fluorine-based synthetic resin.

Embodiments of the catheter of the present invention will be described with reference to the drawings.

FIG. 1 is an enlarged partial side view of an embodiment of the catheter of the present invention, and FIG. 2 is an enlarged side wall sectional view of the catheter of the present invention.

The catheter 1 of the present invention has a porous resin tube 2 as a catheter base, and a synthetic resin 3 having adhesive properties with the resin forming the porous tube 2 flows into the pores of the porous tube 2. Further, on the surface of this synthetic resin 3, a water-soluble polymeric substance 4 or a derivative thereof having lubricating properties when wetted is fixed.

Further, the medical tube of the present invention has a medical tube body made of synthetic resin as a tube base, and the outer surface of the tube body is exposed, and a large number of tubes are present on the outer surface of the tube body. The recess or hole is filled with a synthetic resin different from the synthetic resin forming the tube body, and a lubricating substance is fixed to the filled synthetic resin on the outer surface of the tube.

The porous tube 2 used in the catheter of the present invention differs depending on the catheter, but - for boat fishing, the inner diameter is 0.36 yx to 1.12 x R1 the outer diameter is 0.6
7xm~2.70tay, wall thickness 0.15yx~0.6
It is 01m. As for the hardness of the porous tube base material, the Schizia A hardness is preferably 30 to 80, more preferably 30 to 65. In addition, the porosity of a porous tube is also affected by the hardness of the tube.
It is preferably about 20 to 80%, more preferably 40 to 6
It is 0%.

Further, the tube body used in the medical tube of the present invention is a porous tube as described above, and furthermore, one having a large number of recesses on the surface is used.

The resins used to form the porous tube and tube body include polyolefins such as polyethylene, polypropylene, ethylene-propylene copolymer, ethylene-vinyl acetate copolymer, polyvinyl chloride, cellulose acetate, polyamide, and polytetrafluoroethylene. (P.T.
FE), perfluoroalkoxy fluororesin (PFA)
), tetrafluoroethylene/hexafluoropropylene copolymer (
F E P), ethylene tetrafluoroethylene copolymer (
ETFE), polychlorotrifluoroethylene (PC″r
Fluorine-based synthetic resins such as FE), vinylidene fluoride (PVDF), and vinyl fluoride are used. Preferably, the above-mentioned fluorine-based synthetic resin has high antithrombotic properties, and particularly preferably polytetrafluoroethylene. Then, using these resins, a porous tube or a tube having concave portions on the surface is formed by a known method such as a solid-liquid phase separation method, a liquid-liquid phase separation method, or a stretching method. Particularly preferred porous tubes and tubes with recesses are P
This is a porous PTFE tube with fine porosity formed by stretching a TFE tube. The stretching method may be l-axis stretching or biaxial stretching.

Furthermore, from the viewpoint of physical properties, the porous PTFE tube has an inner diameter of 0.36 to 30mrx and a wall thickness of 0.08mrx.
Particularly preferred are mrp ~ 5.0 cm, pore diameter 0.8 ~ 5.0 μm, and porosity approximately 25 ~ 85%.

In the catheter l of the present invention, the porous tube 2
The synthetic resin 3 is flowing into the pores. This synthetic resin may flow into the inner surface of the pore in a thin (film-like) manner, or may be filled so as to close the pore as shown in FIG. In medical tubes, a large number of recesses or holes on the outer surface of the tube body are filled with a synthetic resin different from the synthetic resin forming the tube body.

The resin to be filled is preferably a flexible, soft synthetic resin. This is because a soft synthetic resin can follow the change in shape of the pores or recesses when the porous tube and tube body are curved. Further, the resin to be filled is preferably one that does not have very high adhesiveness to the resin forming the porous tube and the tube body. The material used for the synthetic resin 3 flowing into the pores or recesses varies depending on the synthetic resin forming the porous tube 2 or the tube body.

For example, when the porous tube and the tube body are made of fluorine-based synthetic resin, polyvinyl chloride, polyurethane, polyurethane-polyvinyl chloride copolymer, polyamide, etc. are used. Particularly preferred is polyvinyl chloride.

Further, when the porous tube and the tube body are formed of polyolefin, polyvinyl chloride, polyurethane, polyurethane polyvinyl chloride compound, polyamide, etc. are used.

When the porous tube and the tube body are made of polyamide, polyvinyl chloride, polyurethane, polyurethane-polyvinyl chloride copolymer, polyamide, etc. are used.

A lubricating substance is fixed on the surface of the synthetic resin 3 flowing into the pores of the porous tube 2 or the recesses or pores of the tube body. Furthermore, if the pores of the lubricating substance 4 are blocked by synthetic resin, the second
As shown in the figure, it may be fixed only to the outer surface side of the porous tube 2, but preferably it is also fixed to the inner surface side.

A lubricating substance refers to a substance that has lubricating properties when wet.

Specifically, there are water-soluble polymer substances or derivatives thereof. The lubricating substance is fixed to the surface of the synthetic resin by covalent bond or ionic bond. This lubricating substance is, in principle, a chain-like, non-crosslinked polymeric substance, consisting of OH, -CON H,, -COOHl-N +-(7
, coo--5o3-. Furthermore, the lubricating substance contains water when wet and exhibits 71η lubricity.

Specifically, natural water-soluble polymer substances include starches such as carboxymethyl starch and dialdehyde starch, cellulose bases such as ) J ruboxymethyl cellulose, methyl cellulose, hydroxyethyl cellulose, and hydroxypropyl cellulose, tannins, lignin system,
Possible materials include polysaccharides such as alginic acid, gum arabic heparin, chitin and chitosan, and proteins such as gelatin and casein. Synthetic water-soluble polymer substances include polyvinyl alcohol, polyalkylene oxide, polyethylene oxide, polyalkylene polycol, polyethylene glycol, acrylic acid, sodium polyacrylate, and maleic anhydride.
Methyl vinyl ether maleic anhydride copolymer, methyl vinyl ether maleic anhydride sodium, methyl vinyl ether maleic anhydride ammonium salt, maleic anhydride ethyl ester copolymer, as a fucuric acid type, polyhydroxyethylphthalate ester, as a water-soluble polyester, Possible examples of polydimethylolpropionate and acrylamide-based materials include polyacrylamide hydrolyzate, polyacrylamide quaternized product, polyvinylpyrrolidone, polyethyleneimine, polyethylenesulfonyl-1, and water-soluble nylon.

In addition, the derivatives of water-soluble polymeric substances are not limited to those that are water-soluble, but may be insolubilized ones as long as they have the water-soluble polymeric substances described in 2 as the basic FM composition. Any material can be used as long as it absorbs water when wet and exhibits lubricity.For example, in the case of the above water-soluble polymer substances, esterified products, salts, amidated products, anhydrides, etc. obtained by addition, substitution, oxidation, reduction reactions, etc. can be used. Haloken compounds, ester compounds, hydrolysates, acetal compounds, formal compounds, alkyl compounds, tetrachlorides, cyanides, hydrazides, sulfonates, nitrates, ionic complexes, and diasonium groups, azide groups, iso/anates Crosslinked products with substances that have two or more G reactive functional groups, such as group, acid chloride group, e J!!t hydride group, imino carbonate group, amine group, carboxyl group, evoquine group, hydroxyl group, aldehyde group, etc. , also vinyl compounds, acrylic acid, methacrylic acid,
Possible examples include diene compounds, copolymers with maleic anhydride, etc.

Furthermore, the synthetic resin flowing into the pores has a reactive functional group that forms an ionic or covalent bond with the lubricating substance, or contains a compound having a reactive functional group, as described below. ing.

The reactive functional groups present or introduced into the synthetic resin that have flowed into the pores or recesses combine with the above-mentioned lubricating substance, making it possible to impart lubricity to the surface of the synthetic resin. As a result, a permanently lubricated surface can be obtained without dissolving in water. Here, explanation will be made based on a covalent bond. The lubricating material is not particularly limited, but the aforementioned cellulose-based, maleic anhydride-based, acrylamide-based, polyethylene oxide-based, water-soluble nylon, and the like are preferably used. Especially hydroxypropyl cellulose, methyl vinyl ether, maleic anhydride co-tf
1 body, polyacrylamide, polyethylene glycol,
Water-soluble nylon (manufactured by Toshi Co., Ltd. AQ-Nylon P
-70) etc. are suitable. The average molecular weight of these lubricating substances is not particularly limited, but it is preferable that the average molecular weight is about 3 to 5 million because it has high lubricity and provides a lubricating layer with an appropriate thickness and a degree of swelling that is not significantly large when it contains water. It is.

In addition to polyvinylpyrrolidone, lubricating substances that are fixed to the surface of synthetic resins by ionic bonds include carboxylates, sulfonates, and ammonium salts of the water-soluble polymer substances mentioned above. Carboxylate salts include sodium salt of methyl vinyl ether maleic anhydride, sodium polyacrylate, polyacrylamide hydrolyzate, sodium carboxymethyl cellulose, sodium alginate, etc. Sulfonate salts include sodium polystyrene sulfonate and sodium polyvinyl sulfonate. Examples of ammonium salts include ammonium salts of methyl vinyl ether maleic anhydride and quaternized polyacrylamide.

There are no particular restrictions on the reactive functional groups present in the synthetic resin that has flowed into the pores or into the recesses, as long as they react with the lubricating substance and fix it by bonding or crosslinking.
Possible examples include diazonium groups, azide groups, isocyanate groups, acid chloride groups, acid anhydride groups, imino carbonic acid ester groups, amine 7 groups, carboxyl groups, epoxy groups, hydroxyl groups, aldehyde groups, and in particular incyanate groups and amine 7 groups. , an aldehyde group, and an epoxy group are preferred.

Therefore, polyurethane, polyamide, etc. are suitable as the reactive functional group-containing synthetic resin.

In addition, examples of substances having reactive functional groups include methylene diisocyanate, ethylene diisocyanate,
Isocyanates such as hexamethylene diisocyanate, xylene diisocyanate, toluene diisocyanate, diphenylmethane diisocyanate, naphthalene diisocyanate, phenylene diisocyanate, and cyclohexylene diisocyanate, and adducts or full polymers of these iso/anates and polyols.

Furthermore, for example, as low molecular polyamines, ethylenediamine, trimethylenediamine, 1.2 diaminopropane,
Tetramethylenediamine, 1,3-diaminobutane, pentamethylenediamine, 2,4-diaminopentane, hexamethylenediamine, N,N-dimethylethylenediamine, N.

N-diethyltrimethylenediamine, N,N-dimethyltrimethylenediamine, N,N-dimethylp-phenylenediamine, diethylenetriamine, triethylenetetramine, tetraethylenetriamine, triethylenetetramine, tetraethylenepentamine, hebutaethyleneoctamine , nonaethylenedecamine, 1,3-bis(2”
Aminoethylamine/)propane, bis(3-aminopropal)amine, 1,3-bis(3°-aminopropylamino)propane, tris(2-aminoethyl)amine,
Tetra(aminomethyl)methane, methyliminobispropylamine, engineered tyliminobisethylamine, N-aminopropyl-2morpholine, N-aminoprivyl-2pipecoline, xylylenediamine, Fugo, nylenediamine, piperazine, N-methylbiperane, Possible examples include N-(2-aminoethyl)ethanolamine and N-aminoethylpiperazine. As a polymeric polyamine [+]
Poly(alkylene polyamine) synthesized from amine and alkylene civalide or epichlorohydrin,
[II] Alkylene imine polymers obtained by ring-opening polymerization of alkylene imines such as ethyleneimine and propylene imine, [[11] Sonoike, polyvinylamine,
Polyamines such as polylysine.

In addition, glutaraldehyde, terephthalaldehyde,
Polyaldehydes such as isophthalaldehyde and dialdehyde.

Furthermore, there are polyevokinds such as ethylene glycol diglycidyl ether and polyethylene glycol diglycidyl ether.

In order to flow the synthetic resin and the above-mentioned compound into the pores of the porous tube or into the recesses or pores of the tube body, a solution containing the synthetic resin and a compound having a reactive functional group as indicated in ``-'' is introduced. This can be done by applying it to a porous tube or tube body and then drying it. Application is carried out by spray coating the solution, dipping the tube into the solution, etc.

The solvent used may be one that does not dissolve the porous tube or the tube body, or one that has some degree of solubility.

The solvent varies depending on the material of the porous tube or tube body, but examples include ketones such as acetone, methyl ethyl ketone, methyl isobutyl ketone, and/or chlorhexanone, butyl acetate, ethyl acetate, carpitol acetate, and butyl carpitol acetate. Ester series such as
Any of ether systems such as methyl cellosolve, ethyl cellosolve, and tetrahydrofuran, aromatic systems such as toluene and quinolene, halogenated alkyl systems such as dichloroethane, and alcohol systems may be used.

When the porous tube or tube body is made of a fluororesin such as PTFE, acetone, methyl ethyl ketone, tetrahydrofuran, etc. are suitable as the solvent.

In addition, in the above explanation, a method was explained in which a compound having a reactive functional group is flowed into the pores together with a synthetic resin, but the method is not limited to this method. A method of attaching a sexual functional group may also be used.

Next, an embodiment in which the catheter of the present invention is applied to a catheter for vascular introduction will be described with reference to the drawings.

FIG. 3 is a side view of an embodiment in which the catheter of the present invention is applied to a catheter for vascular introduction, and FIG. 4 is a sectional view of the catheter for vascular introduction shown in FIG. 3.

This blood vessel introduction catheter IO has a catheter main body 11
and a super-I transverse wire 13 built in along the catheter body 11. Specifically, the catheter body 11 has a lumen 15 that penetrates from the tip to the base end.
The catheter body ■1 has a base HJt:
A hub 12 is fixed.

The distal end of the catheter body 11 is deformed into an arbitrary shape so that it can be easily introduced into a blood vessel. Further, the distal end portion of the catheter body 11 has a small diameter. The hub 12 has a passage communicating with the internal lumen of the catheter body 11, and one end of a neutral wire 23 is fixed inside the hub 12 so as not to block this passage. The other end of the superelastic wire 23 extends to the vicinity of the distal end of the catheter main body 11 to such an extent that it does not protrude or slightly protrudes from the distal end.

The superelastic wire 23 is preferably a metal wire,
Wire diameter 005~1.50m, preferably 010~1,0
It is particularly preferable that the superelastic alloy undergoes plastic deformation of approximately 1 to 10% when stress is applied at a temperature higher than the reverse transformation completion temperature of the superelastic alloy. At the same time, the alloy wire almost completely returns to its original state. As a specific example, Ni: 50.5 to 51. Oat% T1Ni alloy is most preferred, but Ni: 50.3-52. Oat%
It is also possible to use T1Ni alloy. In addition, so-called TiN1X, which is a T1Ni alloy with one or more third elements added
Other alloys can also be used.

This superelastic wire 23 built into the catheter body 11 is
It acts as a substitute for a guide wire, making it possible to easily introduce a catheter for intravascular introduction into a desired site within a blood vessel.

As described above, the catheter body 11 has a porous resin tube as a catheter base, and a synthetic resin having adhesive properties with the resin forming the porous tube flows into the pores of the porous tube. A lubricating substance is fixed on the surface of the synthetic resin. As a porous tube,
Those having an inner diameter of 0.36 to 1.1+u+, a wall thickness of 150 to 3 GOμ, and a length of 800 to 2000Rj+ are used. In this example, a porous PTFE tube (inner diameter 0.55*i+) was used.

Outer diameter 0.97gm, wall thickness 210μ shoulder, average pore diameter 5μ,
A length of 1000 cm and a porosity of 50% were used. Furthermore, vinyl chloride resin was used as the synthetic resin flowing into the pores. Furthermore, as a compound having a reactive functional group,
Methyl diisocyanate (MDI) was used. As the lubricating substance, a maleic anhydride ethyl ester copolymer was used. The catheter body 11 is created by using tetrahydrofuran (THF) as a solvent and adding polyvinyl chloride (
Degree of polymerization L'aQQ, containing 20% DOP) or 9% by weight
It was added and dissolved so that Furthermore, in this solution,
The above methyl diisocyanate was added and dissolved at 6% by weight. Then, the surface of the porous PTFE tube was coated with the above solution, and the solvent was evaporated by air drying. Anything adhering to the outer surface was wiped off with tetrahydrofuran.

The porosity of the porous tube after the above treatment is 0 to 20%, preferably 0 to 5%. The PTFE tube subjected to the above treatment was then coated with a solution of 2% by weight maleic anhydride ethyl ester copolymer dissolved in tetrahydrofuran, and the surface of the synthetic resin flowing into the pores of the PTFE tube was was covalently bonded with methyl diisocyanate to fix the above copolymer.

Tubular catheter body 11 formed as described above
A Luer tapered hub 12 made of synthetic resin (for example, nylon) was fixed to the base end of the hub 12 by fusion or adhesive.

Further, in advance, a diameter 0.0 mm is provided at the center of the passage of the hub 12 so as to extend through the lumen 15 of the catheter body 11 and terminate at the distal end near the distal opening of the catheter body 11. 46m1, length LIOQmm
One end of a superelastic wire 13 made of a Ni-Ti (atomic ratio: 50.3% Ni) alloy was fixed.

The superelastic wire 23 is fixed to the hub 12 by a plurality of protrusions protruding radially from the inner wall surface of the passageway of the hub 12 toward the center, as shown in FIG. 5, which is a sectional view taken along line II in FIG. 16
It was designed to be held from the surroundings by the tip.

When introducing the intravascular introduction catheter of this example into a blood vessel, the introduction needle, introducer catheter, etc. are inserted directly into the indwelling artery without using a guide wire, and the tip of the catheter is inserted by manipulating the hub. While transmitting torque to the catheter, select the 1m tube branch and reach the catheter tip to the target site. Then, a drug solution, contrast medium, etc. can be injected from the proximal end of the hub.

6 and 7 show an embodiment in which the superelastic wire 23 can be inserted into and removed from the catheter body 11. FIG.

That is, as shown in FIG. 6, the superelastic wire 23 has its proximal end fixed to a superelastic wire fixing hub 14 which is detachably connected to the hub 12 of the catheter body 11. The fixing method in this case can be carried out in the same manner as shown in FIG. Therefore, in this embodiment, the superelastic wire 13 is removed from the catheter main body 11 together with the superelastic wire fixing hub 14 after the catheter main body 11 is introduced into the target site in the blood vessel, as shown in FIG. Can be done. As a result, the effective inner diameter of the lumen 15 of the catheter body 11 is increased (the effective inner diameter becomes larger), and the injection speed of the drug solution, contrast medium, etc. from the hub 12 can be increased. Other configurations are shown in FIGS. 2 to 5. Similar to the example shown.

Note that the catheter of the present invention is not limited to the above-mentioned catheter, but also includes, for example, an angiography catheter, a catheter with an expandable body used for treating vascular stenosis, an IVH catheter used for administering high-calorie infusions, etc. It can be applied to various catheters. Furthermore, the medical tube of the present invention can be used for various blood circuits, artificial blood vessels, sensor tubes inserted into the body or blood circuits, and various tubes that come into contact with blood.

[Effects of the Invention] The catheter of the present invention has a porous resin tube as a catheter base, and a synthetic resin having adhesive properties with the resin forming the tube flows into the pores of the porous tube. Furthermore, since a lubricating substance is fixed on the surface of the synthetic resin, there is less resistance between the inner wall of the blood vessel and the inner wall of the blood vessel when it is inserted into the blood vessel, making it easier to introduce and less likely to cause thrombi.
Even if it comes into long-term contact with blood, there is little plasma protein adhesion, and there is little risk of enlargement of the outer diameter or occlusion of the internal lumen. Furthermore, even if it is made of a relatively hard synthetic resin, the base tube of the catheter body is porous, so it can be made to have the necessary flexibility and be made with a sufficiently thin wall thickness. It is possible to apply this method to catheters with smaller diameters.

In addition, the medical tube of the present invention has a medical tube body formed of a synthetic resin as a tube base, and the outer surface of the tube body is exposed, and a large number of The recess or hole is filled with a synthetic resin different from the synthetic resin forming the tube body, and a lubricating substance is fixed to the outer surface of the filled synthetic resin. Even if it comes into contact with blood over a long period of time, there is little plasma protein adhesion and there is little risk of the outer diameter becoming enlarged.

[Brief explanation of the drawing]

FIG. 1 is an enlarged partial side view of an embodiment of the catheter of the present invention, FIG. 2 is an enlarged cross-sectional view of the side wall of the catheter of the present invention, and FIG. A side view of an embodiment applied to a catheter, FIG. 4 is a sectional view of the catheter for intravascular insertion shown in FIG. 3, and FIG.
3 is a cross-sectional view taken along line I, FIG. 6 is an enlarged cross-sectional view of the hub portion of an embodiment in which the catheter of the present invention is applied to an intravascular catheter, and FIG. 7 is a cross-sectional view of the hub portion shown in FIG. 6. FIG. 2 is a side view showing how the intravascular insertion catheter of the embodiment is used.

Claims (8)

[Claims] (1) A porous resin tube is used as the catheter base, a synthetic resin flows into the pores of the porous tube, and a lubricating substance is fixed on the surface of the synthetic resin. catheter. (2) The catheter according to claim 1, wherein the synthetic resin flowing into the pores of the porous tube has a reactive functional group that forms an ionic or covalent bond with the lubricating substance. (3) The catheter according to claim 1, wherein the synthetic resin flowing into the pores of the porous tube contains a compound having a reactive functional group that forms an ionic or covalent bond with the lubricating substance. (4) The catheter according to any one of claims 1 to 3, wherein the synthetic resin flowing into the pores of the porous tube is a soft synthetic resin. (5) The catheter according to any one of claims 1 to 4, wherein the resin forming the porous tube is a fluorine-based synthetic resin. (6) A medical tube body made of synthetic resin is used as the tube base, and the outer surface of the tube body is exposed, and the numerous recesses or holes present on the outer surface of the tube body are A medical tube, characterized in that it is filled with a synthetic resin different from the synthetic resin forming the tube body, and further, a lubricating substance is fixed to the outer surface of the filled synthetic resin. . (7) The medical tube according to claim 6, wherein the medical tube body is made of an antithrombotic material. (8) The medical tube according to claim 6, wherein the resin forming the tube body is a fluorine-based synthetic resin.