JP5184193B2 - Medical detachable embolic wire - Google Patents

Description

  The present invention relates to a medical wire, and more particularly to a medical detachable embolic wire for placing an indwelling member at a predetermined site of a tubular organ.

  At present, as a less invasive treatment method for an aneurysm or the like, a vascular embolization method in which an in-vivo indwelling member is placed in the aneurysm is known. In this method, a delivery wire having a living body indwelling member connected to the distal end portion via a connecting member is passed through a catheter placed in the living body, and the wire is manipulated under fluoroscopy with an X-ray contrast apparatus. The in-vivo indwelling member is guided to a desired position in the living body so that the in-vivo indwelling member reaches a target location, and the in-vivo indwelling member is detached in that state.

  As a method for removing the in-vivo indwelling member, mechanical means and electrical means are known. For example, the electric means disclosed in Patent Document 1 supplies electric power from the outside between a conductive wire and a counter electrode connected to a living body, and connects a connecting member between the in-vivo indwelling member and the delivery wire. It decomposes and blows.

Patent Document 2 discloses a blood vessel occlusion device using a water-swellable heat-dissolvable connecting member made of a polyvinyl alcohol molded body as a connecting member between a conductive wire and an in-vivo indwelling member. Yes. According to this medical device, when a high-frequency current is supplied between the conductive wire and the counter electrode, the distal end portion of the conductive wire functions as a heating electrode, and the connection member instantaneously heat-dissolves. Since the indwelling member is separated from the conductive wire, the advantage is that the time required for the operation is short and the burden on the patient or doctor is small. Furthermore, Patent Document 3 describes a medical wire characterized in that a relatively large single or plural grooves are formed on the surface of a connecting member.
Japanese translation of PCT publication No. 8-501015 JP-A-7-265431 JP 2007-301172 A

  In the medical device described in Patent Document 2, it is necessary to use the water-swellable heat-soluble connecting member after it is swollen with water or the like in advance. It is done using. That is, the operator draws physiological saline into a syringe, injects it into the sheath of the exterior where the above-described medical device is arranged, presses the sheath tip against the catheter port at the proximal end portion of the microcatheter, Push the device into the microcatheter. Then, after the medical device is delivered to the affected part through the microcatheter, an operation is performed in which a high-frequency power supply device supplies current when the in-vivo indwelling member is placed at an appropriate position of the affected part to dissolve the heat-soluble connecting member. Is called. During this series of operations, the connecting member absorbs and swells the physiological saline injected into the sheath, the blood in the microcatheter, and the water component of the physiological saline.

  However, it takes about 2 to 5 minutes to complete the swelling of the connecting member, and until the swelling is completed, the connecting member is unlikely to melt even if a current is supplied from the heating power supply device. Even if the medical device reaches an appropriate position of the affected part due to a quick operation by the person, the detachment operation cannot be performed and it is necessary to wait for a predetermined time. Therefore, the heating method has a problem that the original advantage that it is possible to detach instantly hardly appears, and it is difficult to use in an emergency case. In addition, when a current is supplied from the heating power supply device in a state where the swelling state is insufficient, the amount of dissolution of the connecting member is small, so the current must be supplied multiple times, and eventually the operation time is reduced. There was a problem that required. Further, even when one or a plurality of grooves are formed on the surface of a connection member such as the medical wire described in Patent Document 3, the connection member may not be instantaneously dissolved.

  In view of the above problems, the object of the present invention is to provide a medical detachable embolic wire that can shorten the time until the connecting member becomes detachable, and further burden on the operator and the patient. It is an object of the present invention to provide a medical detachable embolic wire that can be reduced.

  As a result of intensive studies in view of the above problems, the present inventor has found that a conductive wire, a connecting member connected to the tip of the conductive wire, and an in vivo body connected to the conductive wire via the connecting member There is provided an indwelling member, and the connection member has a surface having an arithmetic average roughness Ra of 1.0 or more. According to this, the swelling of the connection member is particularly promoted, and the change in the dissolution characteristics, the melting characteristics, the decomposition characteristics, etc. of the connection member is accelerated, and as a result, the time until the separation becomes possible, and further the time required for the separation. It can be shortened.

  In addition, the medical detachable embolic wire is characterized in that the surface of the connecting member is hydrophilic. Swelling can be accelerated at a specific surface roughness with a hydrophilic surface.

  In addition, the medical detachable embolization wire is characterized in that the contact angle of the surface of the connecting member to water is 60 degrees or less. According to this, it becomes possible to further promote swelling.

  Further, the medical detachable embolic wire is provided, wherein the connecting member is formed containing a water-soluble or water-absorbing polymer. According to this, it becomes possible to easily form a hydrophilic surface.

  In addition, the medical detachable embolic wire is provided, wherein the polymer is a polyvinyl alcohol polymer. As the polymer, in particular, a polyvinyl alcohol-based polymer is used, and by containing this to form a connection member, the swelling is accelerated at a specific surface roughness, and in a relatively mild condition. The in-vivo indwelling member can be detached more quickly and safely.

  In addition, the medical detachable embolic wire is provided, wherein the connecting member is heat-soluble. According to this, when the in-vivo indwelling member is detached, it is difficult to generate decomposition products and the like, and the in-vivo indwelling member can be detached more safely.

  Further, the medical detachable embolization wire, wherein the connecting member is obtained through a step a for obtaining a gelled product, a step b1 for performing dehydration after stretching the gelled product, and a step c for performing a drying treatment. Provided. According to this, it is possible to suitably form a connecting member having a specific surface roughness, and further, the medical detachable embolic wire.

  Further, in the step b1, the gelled product is dehydrated by immersing the gelled product in a liquid having a solidifying ability with respect to the gelled product, and further, the medical detachable embolic wire, and further the gelled product The liquid having a solidifying ability is a solution containing a compound selected from the group consisting of alcohols, ketones and fatty acid esters, and the concentration of the compound is 95 to 100 vol% A medical detachable embolic wire was provided. According to this, the connecting member having a specific surface roughness, and further, the medical detachable embolic wire can be suitably and more easily formed.

  Moreover, the said detachable embolic wire for medical use characterized by extending | stretching the gelled material in the process b1 in the solvent used at the process a which obtains a gelled material was provided. According to this, it is possible to more easily form the specific connection member and further the medical detachable embolization wire.

  In the step c, the medical detachable embolization wire is characterized in that the drying process is performed in an environment having an average ambient humidity of 30% RH or less. According to this, it is possible to more suitably form the specific connecting member and further the medical detachable embolic wire.

  In addition, the medical detachable embolization wire is provided in which the connecting member is obtained through a step a for obtaining a gelled product and a step b2 for performing stretching after dehydrating the gelled product. According to this, it is possible to suitably form a connecting member having a specific surface roughness, and further, the medical detachable embolic wire.

  In addition, the medical detachable embolic wire is characterized in that in step b2, the gelled product is dehydrated by freeze-drying. According to this, the connecting member having a specific surface roughness, and further, the medical detachable embolic wire can be suitably and more easily formed.

  According to the medical detachable embolization wire of the present invention, the in-vivo indwelling member is more quickly removed by disposing a portion having an arithmetic average roughness Ra of 1.0 or more on the surface of the connecting member. It becomes possible. In particular, in the swelling treatment of the connecting member, a sufficiently swollen state is achieved in a very short time, and the time required for the swelling treatment is greatly reduced. Therefore, when the in-vivo indwelling member is accommodated at an appropriate position in the affected area, it is possible to immediately flow current with a high-frequency power supply device or the like, so that the connecting member can be reliably dissolved, blown, or disassembled. The member can be removed in a short time. For this reason, the burden on the operator and the patient can be further reduced.

  Moreover, the surface of the connecting member may be hydrophilic, or the contact angle of the surface may be 60 degrees or less. In particular, by setting the arithmetic average roughness Ra of the surface of the connecting member to 1.0 or more and further making the surface hydrophilic, the time required for the swelling treatment can be dramatically shortened. Moreover, it becomes possible to form the said hydrophilic surface simply by comprising the said connection member containing a water absorbing polymer, More preferably, a polyvinyl alcohol-type polymer.

Moreover, the surface which has the said specific surface can be formed more suitably and simply by forming the said connection member through a predetermined | prescribed process.

Hereinafter, an embodiment of the present invention will be described with reference to an example of the drawings.
FIG. 1A shows a conductive wire 1, a heat-soluble connection member 2 connected to the tip of the conductive wire 1, and an in-vivo indwelling member connected to the conductive wire 1 via the connection member 2. 1 is a schematic view showing a medical detachable embolic wire 10 according to the present invention, and FIG. 1 (b) is a catheter 4 combined therewith, and the wire 10 and the catheter 4 are combined in a medical device. Is configured.

  As shown in FIG. 1, the conductive wire 1 includes, for example, a conductive metal wire portion 1f and a distal end portion 1a connected to the distal end portion and formed by forming a conductive metal wire into a coil shape. . Furthermore, it is preferable that the portions other than the electrode portion 1e and the base end portion 1b are electrically insulated by a fluororesin coating 1c or the like. The wire portion 1f and the distal end portion 1a are appropriately connected by an existing method. For example, the distal end portion of the wire portion 1f is inserted into the lumen portion of the proximal end portion of the coiled distal end portion 1a, and an adhesive or the like is used. Can be fixed and connected. The fluororesin coating 1c can be formed by an existing method, but can be formed by using, for example, a heat shrinkable tube or dipping in a coating solution.

  Examples of the shape of the wire portion 1f include a coil shape and a rod shape. Further, the outer diameter may be different between the distal end side and the proximal end side. For example, as shown in FIG. 1, a taper structure in which the outer diameter on the base end side is larger than that on the front end side and the diameter gradually decreases at the transition portion is exemplified. Further, the conductive metal material constituting the wire portion 1f is not particularly limited, and examples thereof include stainless steel alloys and superelastic alloys.

  As described above, the distal end portion 1a is made of, for example, a coiled wire. The shape of the coil is not particularly limited, and a coil whose radius and pitch are appropriately changed may be used. Moreover, the conductive metal material constituting the wire is not particularly limited, and examples thereof include a biocompatible metal such as a stainless alloy. Moreover, the electrode part 1e which has a function as a heating electrode is provided in the front end side of the front-end | tip part 1a.

  The connecting member 2 in the present invention has a surface with an arithmetic average roughness Ra of 1.0 or more. Note that the entire surface of the connecting member 2 may have the above specified arithmetic average roughness Ra, but it may be formed only on a part of the surface (in this case, it is detached). The position can be controlled to a specific position on the connecting member 2). Further, the connecting member 2 can be suitably and more easily shaped by the manufacturing method described later, but is not limited to those formed by these methods. When the surface of the connecting member 2 has such a structure, the specific surface area of the connecting member 2 is dramatically increased and the contact area with water is increased. As a result, the connecting member 2 is in a swollen state. The time required for this is greatly reduced. In addition, when the swelling of the connection member is promoted, the change in the dissolution characteristics, the melting characteristics, the decomposition characteristics, etc. of the connection member is accelerated, and the time required for the separation and further the time required for the separation can be shortened. It becomes possible.

  On the other hand, the connecting member 2 can be molded into various shapes and used. For example, as shown in FIG. 1, the connecting member 2 is formed in a single rod shape (including a linear shape or a thread shape). Can be used. Further, for the purpose of increasing the contact area with water, it is possible to form notches or various shapes. In this case, however, an extra work is required to form such a shape. In addition, the connecting member needs to be connected to both the conductive wire and the in-vivo indwelling member, which may limit the design of the connecting portion. In addition, since the connecting member has a surface having an arithmetic average roughness Ra of 1.0 or more, more preferably 1.5 or more, connectivity to the conductive wire and the in-vivo indwelling member (anchor effect) There is an effect that it is excellent. The size of the connecting member 2 varies depending on the tubular organ into which the medical wire is inserted. For example, the outer diameter is in the range of 0.07 to 0.25 mm, and / or the length is in the range of 2 to 6 mm. It is preferable to form.

  Moreover, in order to improve the water absorbability of the connection member 2 and to swell more efficiently, the surface of the connection member 2 is made hydrophilic, or the contact angle of the surface with respect to water is further increased. It may be set to 60 degrees or less. In particular, it is possible to dramatically reduce the time required for the swelling treatment by making the surface of the connecting member an arithmetic average roughness Ra of 1.0 or more and further making the surface hydrophilic. (Lotus Effect). Even when the contact angle is 60 degrees or more, the time required for the swelling treatment can be shortened.

  The connecting member 2 can be formed using a water-soluble or water-absorbing polymer as a raw material polymer. According to this, it is possible to form the hydrophilic surface easily and to a high degree. As the water-soluble or water-absorbing polymer, natural product polymers and synthetic polymers can be used. Examples of the natural product polymer include dextran, cellulose polymer, and the like. Synthetic polymers include polyvinyl alcohol polymers such as polyvinyl alcohol, polyvinyl pyrrolidone and polyvinyl methyl ether, sodium polyacrylate, polyethylene oxide, alkali metal salts of acrylic resins, copolymers of acrylic acid and alkyl methacrylate, etc. Can be mentioned. Among these, those having a large amount of absorption or those having a large change in properties when absorbed are preferable. For example, polyvinyl alcohol polymers, dextran, sodium polyacrylate, etc. A polyvinyl alcohol polymer that has a large change in properties over time and can be dissolved under relatively mild conditions can be particularly preferably used.

  In the present invention, various polymers can be used as long as they have even a slight hygroscopic property, such as polyamide resins such as nylon, polyolefin resins such as polypropylene and polyethylene, and polymethyl methacrylate resins. It is also possible to use vinyl polymers such as

  Moreover, the connection member 2 can be heat-soluble. As will be described later, this is suitable when a current is supplied from a heating power supply device to heat and disconnect the connection member 2.

  The in-vivo indwelling member 3 may have a variety of shapes such as a coil shape (including a material whose radius changes), an S shape, and a shape provided with a primary shape and a secondary shape. In the present embodiment, as shown in FIG. 1, a secondary coil shape in which a primary shape is a circular coil shape and a circular secondary spiral shape is further exemplified. Moreover, it is preferable that the in-vivo indwelling member 3 uses a biocompatible metal, for example, platinum, gold | metal | money, a stainless alloy, a superelastic alloy, and those alloys as a wire.

  The connecting member 2, the distal end portion 1a, and the in-vivo indwelling member 3 are connected and fixed by an existing method. For example, the proximal end portion and the distal end portion of the connecting member 2 are each formed into a coil shape. It can be inserted into the lumen of 1a and the in-vivo indwelling member 3, and connected and fixed with an adhesive or the like.

  The connecting member 2 having a surface having an arithmetic average roughness Ra of 1.0 or more is subjected to a step a for obtaining a gelled product, a step b for stretching and dehydrating the gelled product, and a drying treatment if necessary. It can be more suitably and easily produced by the method through step c. In particular, in the dehydration in the step b, the connection member 2 is produced by forcibly removing the material (for example, water) instead of naturally drying the material. preferable.

  The step a is a step of, for example, producing a gelled product (including a hydrogelled product) of a raw material polymer by a predetermined method. As an example, a polyvinyl alcohol solution (gelled product) that has been gelled by a method such as filling a cylindrical mold with a polyvinyl alcohol aqueous solution prepared in advance according to a predetermined formulation and repeatedly performing a freezing process and a thawing process is obtained. (In this case, it is obtained as a rod-shaped molded body). The inner diameter of the cylinder is not particularly limited, and can be appropriately determined in consideration of the outer diameter of the connection member 2 finally obtained. However, in order to have a certain strength, since it is preferable to make the draw ratio 2 times or more in the step b, when the outer diameter of the finally obtained connecting member 2 is 0.07 to 0.25 mm, The inner diameter of the cylinder is preferably 0.40 to 0.75 mm. The freezing / thawing conditions vary depending on the resin used. For example, when a polyvinyl alcohol polymer is used, the temperature is lowered from 5 ° C. to around −45 ° C. (freezing treatment), and further from around −45 ° C. to 5 ° C. It is preferable to repeat the temperature rise (thaw treatment) up to 10 times or more. By performing such treatment, crystallization of the obtained connecting member 2 proceeds, and the strength can be ensured.

  Examples of the step b include two methods: a case where dehydration is performed after stretching (hereinafter referred to as step b1) and a case where stretching is performed after dehydration (hereinafter referred to as step b2).

  In step b2, in particular, a surface having an arithmetic average roughness Ra of 1.0 or more can be easily formed, and the gelled product obtained in step a is dehydrated by lyophilization. It is preferable to stretch. The lyophilization is preferably performed overnight or longer. The gelled product can be stretched until the total length of the gelled product after freeze-drying is usually 6 times at maximum, but preferably 3 to 4 times. If it exceeds 6 times, it tends to break and is often difficult to stretch.

  In step b1, a method in which dehydration is performed by immersing the gelled product in a liquid having a solidifying ability is preferable in that a surface having an arithmetic average roughness Ra of 1.0 or more can be easily formed. Furthermore, after the gelled product obtained in step a is stretched in the solvent used in the preparation of the gelled product in step a, the gelled product is immersed in a liquid having a solidifying ability and dehydrated. Particularly preferred.

  As the liquid having a solidifying ability with respect to the gelled product, for example, a solution containing a compound selected from the group consisting of alcohols, ketones and fatty acid esters can be used. In particular, alcohols, particularly ethanol, can be preferably used because they can be dried relatively easily and are less likely to cause problems when remaining. The concentration of the compound may be 90 vol% or more, but is particularly preferably 95 to 100 vol%. When the concentration is within this range, the gelled product is stably solidified throughout the rod, and the outer diameter is stabilized. Moreover, although it is preferable that immersion time is 1 to 18 hours, it can determine suitably with the composition of a gelatinized material, the kind of the said compound, etc.

  The stretching treatment after the dehydration treatment is preferably performed in water when a polyvinyl alcohol aqueous solution is used in step a. In the case of step b1, the gelled product can be usually stretched until the total length becomes 5 times at most, but preferably 2 to 4 times. When it exceeds 5 times, it tends to break and is often difficult to stretch.

  In step c, it is preferable to subject the product that has undergone step b1 to a drying treatment for 12 hours or more in an environment of 20 to 30 ° C. and a humidity of 30% RH or less.

  Hereinafter, usage examples of the medical detachable embolic wire of the present invention will be shown. As shown in FIG. 2, the terminal 5b of the power supply device 5 for heating is connected to the counter electrode plate 7 set in contact with the body surface of the living body B by the lead wire 8, and in this state, the terminal 5b is previously placed on the living body. The medical detachable embolic wire 10 is inserted through the catheter 4. At this time, the operator grasps the proximal side (proximal side) grasping portion 1d (see FIG. 1) on which the insulating surface is formed by the fluororesin coating while visually recognizing under fluoroscopy. By operating the medical detachable embolization wire 10, the in-vivo indwelling member 3 connected to the conductive wire 1 via the connection member 2 reaches the aneurysm 9. During this time, the connecting member absorbs the physiological saline injected into the catheter 4 and the water component of the blood in the catheter 4 and swells. Then, after confirming that the in-vivo indwelling member 3 is inserted at an appropriate position in the aneurysm 9, the lead wire 6 connects the terminal 5a of the heating power supply device 5 to the conductive wire base end 1b. Then, a current is supplied from the heating power supply device 5 to heat the connecting member 2, and melt or decompose to cut it.

Example 1
After filling an aqueous solution of 20% by weight of polyvinyl alcohol having an average polymerization degree of 2000 and a saponification degree of 98% into a cylindrical mold having an inner diameter of 0.5 mm, freezing treatment and thawing treatment (cooling from 5 ° C. to −35 ° C., The temperature was repeatedly increased from −35 ° C. to 5 ° C. 10 times) to obtain a polyvinyl alcohol gel (PVA gel) (step a). Thereafter, the PVA gel is stretched 2.5 times in water and immersed in a 99 vol% ethanol solution for 3 hours (step b1), and dried in an environment of 20 to 30 ° C. and 10 to 12% RH for 12 hours or more. (Step c), a connecting member having an outer diameter of 0.15 mm was produced.

  When the contact member manufactured as described above was measured for the contact angle against water by a liquid appropriate method using the automatic minimum contact angle meter MCA-2 manufactured by Kyowa Interface Science Co., Ltd., the contact angle was 56.6 degrees. .

  When the connecting member manufactured as described above was measured using Keyence's three-dimensional shape measuring apparatus KS-1100, the measurement conditions were a measurement range of 1000 microns long and a measurement pitch of 2 microns, and its arithmetic average roughness Ra was measured. Was 2.16.

(Example 2)
A PVA gel was formed in the same manner as in Example 1. The PVA gel was dehydrated overnight by freeze-drying and then stretched 3 times in the air, and kept in the stretched state for 12 hours or more in the indoor environment (step b2) to produce a connecting member having an outer diameter of 0.15 mm.

  When the contact angle with respect to water was measured for the connecting member manufactured as described above in the same manner as in Example 1, the contact angle was 86.8 degrees.

  When the arithmetic average roughness Ra of the connecting member manufactured as described above was measured by the same method as in Example 1, Ra was 1.69.

(Comparative example)
A PVA gel was formed in the same manner as in Example 1. Without passing through the dehydration step, the PVA gel was stretched 3 times in the air, and dried for 12 hours or more while maintaining the stretched state, thereby producing a connecting member having an outer diameter of 0.15 mm.

  When the contact angle with respect to water was measured for the connection member manufactured as described above in the same manner as in Example 1, the contact angle was 85.8 degrees.

  When arithmetic average roughness Ra was measured for the connection member manufactured as described above in the same manner as in Example 1, Ra was 0.55.

(Comparative experiment)
(1) Evaluation of swelling characteristics The cylindrical (rod-shaped) connecting members produced in Examples 1 and 2 and Comparative Example 1 are immersed in physiological saline at 25 ° C., and the change with time in the outer diameter is measured from the start of immersion. Thus, the swelling property of the connecting member was evaluated. The outer diameter ratio is defined as follows and plotted against the elapsed time after the start of swelling is shown in FIG.
Outer diameter ratio = (outside diameter of connecting member after each elapsed time from the start of swelling) / (outside diameter of connecting member 10 seconds after the start of swelling)

  From FIG. 3, in Examples 1 and 2, the increase in the outer diameter ratio is faster than in the comparative example, and the time for the outer diameter ratio to reach 1.5 is 105 seconds for the comparative example and 45 seconds for the first embodiment. Example 2 was 55 seconds. That is, it was confirmed that Examples 1 and 2 have higher swelling performance than the comparative example.

(2) Surface observation by SEM In the present invention, the connecting member has a certain arithmetic average roughness Ra, and Ra can be measured as described above, but the surface roughness of the connecting member is visually determined. In addition, the surface of the connection members prepared in Examples 1 and 2 and the comparative example was observed using SEM. The results are shown in FIGS. 4, 5 and 6, respectively. When comparing the SEM photograph of Examples 1 and 2 shown in FIGS. 4 and 5 with the SEM photograph of the comparative example shown in FIG. However, it can be visually confirmed that the surface of the comparative example has almost no unevenness.

  From the above, the connection member according to the present embodiment has a number of grooves or depressions on the surface thereof, that is, has a predetermined arithmetic average surface roughness Ra, and has a single rod shape. It was confirmed that swelling could be promoted. Therefore, when the medical detachable embolic wire using the connection member according to the present embodiment is used, the connection member can be surely blown when a current is supplied by the high frequency power supply device.

(A) It is the schematic which shows one Example of the medical detachable embolic wire concerning this invention. (B) It is the schematic which shows one Example of the catheter used combining with the medical detachable embolic wire concerning this invention. It is the schematic which shows the usage method of the medical device containing the medical detachable embolic wire concerning this invention. It is a graph which shows the relationship between an outer diameter ratio and swelling time. 2 is a SEM photograph of the surface of a connection member produced in Example 1. 4 is a SEM photograph of the surface of a connection member produced in Example 2. It is a SEM photograph of the surface of the connection member produced in the comparative example.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 Conductive wire 1a Tip part 1b Base end part 1c Fluorine resin coating 1d Gripping part 1e Electrode part 1f Wire part 2 Connection member 3 In-vivo indwelling member 4 Catheter 5 Heating power supply device 5a Terminal 5b Terminal 6 Lead wire 7 Counter electrode 8 Lead wire 9 Aneurysm 10 Medical detachable embolic wire B Living body

Claims (12)

A conductive wire, a connecting member connected to the tip of the conductive wire, and an in-vivo indwelling member connected to the conductive wire via the connecting member, wherein the connecting member is an arithmetic average roughness The surface Ra has a surface of 1.0 or more,
Said connecting member, step a, the step b1 perform dehydration after the conducted stretched gelled, drying step c, to that physician Ryoyo detached embolic characterized in that it is obtained through the performing of obtaining a gelled Wire. In the step b1, the gelled product, medical leaving embolic wire according to claim 1, characterized in that dehydration by immersion in a liquid having a solidifying capability with respect to the gelled. The liquid having a solidifying ability with respect to the gelled product is a solution containing a compound selected from the group consisting of alcohols, ketones and fatty acid esters, and the concentration of the compound is 95 to 100 vol%. The medical detachable embolic wire according to claim 2 . The medical detachable embolic wire according to any one of claims 1 to 3 , wherein the gelled product in step b1 is stretched in the solvent used in step a to obtain the gelled product. The medical detachable embolization wire according to any one of claims 1 to 4 , wherein, in the step c, the drying treatment is performed in an environment having an average ambient humidity of 30% RH or less. A conductive wire, a connecting member connected to the tip of the conductive wire, and an in-vivo indwelling member connected to the conductive wire via the connecting member, wherein the connecting member is an arithmetic average roughness The surface Ra has a surface of 1.0 or more,
It said connecting member, obtaining a gelled product a, the gel product, wherein the to that physician Ryoyo detached embolic wire that obtained via step b2, the performing stretching after the dehydration. The medical detachable embolic wire according to claim 6 , wherein in step b2, the gelled product is dehydrated by freeze-drying. The medical detachable embolic wire according to any one of claims 1 to 7, wherein a surface of the connecting member is hydrophilic. The medical detachable embolic wire according to any one of claims 1 to 8, wherein a contact angle of water on the surface of the connection member is 60 degrees or less. The medical detachable embolic wire according to any one of claims 1 to 9, wherein the connecting member is formed by containing a water-soluble or water-absorbing polymer. The medical detachable embolic wire according to claim 10, wherein the polymer is a polyvinyl alcohol polymer . The medical detachable embolic wire according to any one of claims 1 to 11, wherein the connecting member is heat-soluble .