HK1121419A

HK1121419A - Iontophoresis apparatus

Info

Publication number: HK1121419A
Application number: HK09101805.4A
Authority: HK
Inventors: 金村圣志; 松村健彦; 中山鸠夫; 秋山英郎; 松村昭彦
Original assignee: Tti优而美株式会社
Priority date: 2005-08-08
Filing date: 2006-08-08
Publication date: 2009-04-24

Description

Iontophoresis device

Technical Field

The present invention relates to an iontophoresis device, and more particularly, to an iontophoresis device capable of suppressing or suppressing an undesirable electrode reaction in an electrode structure.

Background

Iontophoresis is a method of driving a drug that is dissociated into positive or negative ions in a solution by a voltage to transcutaneously move the drug into a living body, and has advantages of a small burden on a patient, excellent controllability of the amount of drug administered, and the like.

FIG. 10 is an explanatory view showing a basic configuration of an iontophoresis device as a device for performing the aforementioned iontophoresis.

As shown in the figure, the iontophoresis device has: an action-side electrode structure 110 having an electrode 111 and a chemical solution holding portion 114, the chemical solution holding portion 114 holding a chemical solution (chemical solution) dissociated into positive or negative chemical ions; a non-operation side electrode structure body 120 having an electrode 121 and an electrolyte holding portion 122 for holding an electrolyte; and a power supply 130 connected to the electrodes 111 and 121 at both ends. The drug ions are introduced into the living body by applying a voltage of the same conductivity type as the drug ions to the electrode 111 and a voltage of the opposite conductivity type to the drug ions to the electrode 121 in a state where the drug solution holding portion 114 and the electrolyte solution holding portion 122 are in contact with the living body skin.

One of the problems to be solved by such an iontophoresis device is various electrode reactions occurring in the electrode structures 110 and 120.

For example, in the case of a cationic drug in which the drug is dissociated into positive drug ions, hydrogen ions and oxygen gas may be generated on the electrode 111 and hydroxide ions and hydrogen gas may be generated on the electrode 121 by electrolysis of water, and depending on the type of the drug and the condition of energization, the drug may be chemically changed by reaction near the electrode 111 during energization, and in the case where the drug solution holding portion 114 contains chloride ions, chlorine gas and hypochlorous acid may be generated.

Similarly, in the case of an anionic drug in which the drug is dissociated into negative drug ions, there are cases where hydroxide ions and hydrogen gas are generated at the electrode 111 and hydrogen ions and oxygen gas are generated at the electrode 121 by electrolysis of water, and depending on the type of the drug and the condition of energization, the drug undergoes a chemical reaction near the electrode 111 and changes its quality during energization, and there are cases where chlorine gas and hypochlorous acid are generated when the electrolyte retaining portion 122 contains chloride ions.

When the electrode structures 110 and 120 generate the gas as described above, the current flow from the electrodes 111 and 121 to the chemical solution and the electrolyte is inhibited, and when hydrogen ions, hydroxide ions, and hypochlorous acid are generated, they move to the biological interface, which may adversely affect the living body. Further, if the drug is deteriorated, undesirable conditions such as failure to obtain a desired drug effect or generation of toxic substances may occur.

As an iontophoresis device that can solve the above-described problems, patent document 1 discloses an iontophoresis device in which a silver electrode is used as an anode and a silver chloride electrode is used as a cathode.

In this iontophoresis device, the silver at the anode is oxidized to insoluble silver chloride by energization, and the reaction in which the silver chloride is reduced to metallic silver preferentially occurs at the cathode, so that the generation of various gases and the generation of various ions due to the electrode reaction as described above can be suppressed.

However, in this iontophoresis device, it is difficult to prevent dissolution of the silver electrode during storage of the device, and particularly in the case of a device into which a cationic drug is injected, the type of drug to which the iontophoresis device is applicable is greatly limited. Further, since the morphological change in the production of silver chloride by the silver electrode is large, it is necessary to consider particularly such morphological change as not to affect the device characteristics, and for example, there is a problem that a structure of adhesion cannot be adopted and a large restriction is imposed on the form of the device. In addition, this iontophoresis device cannot solve the problem of drug deterioration during energization.

As another iontophoresis device that can solve the above-described problems, patent document 2 discloses an iontophoresis device shown in fig. 11.

As shown in the figure, the iontophoresis device is composed of: a working electrode structure 210 including an electrode 211, an electrolyte holding portion 212 holding an electrolyte in contact with the electrode 211, a 2 nd conductivity type ion exchange membrane 213 disposed on the front side of the electrolyte holding portion 212, a chemical solution holding portion 214 holding a chemical solution containing 1 st conductivity type chemical ions disposed on the front side of the ion exchange membrane 213, and a 1 st conductivity type ion exchange membrane 215 disposed on the front side of the chemical solution holding portion 214; the same non-active side electrode structure 220 as in fig. 10; a power supply 230.

In this iontophoresis device, since the electrolyte solution and the drug solution are partitioned by the 2 nd ion exchange membrane 213 of the 2 nd conductivity type, the composition of the electrolyte solution can be selected independently of the drug solution. Therefore, an electrolytic solution not containing chloride ions can be used, and by selecting an electrolyte having a lower oxidation or reduction potential than the electrolysis of water as the electrolyte in the electrolytic solution, the generation of oxygen gas, hydrogen ions, and hydroxide ions due to the electrolysis of water can be suppressed. Or by using a buffer electrolyte solution obtained by dissolving a plurality of electrolytes, a change in pH due to the generation of hydrogen ions or hydroxide ions can be suppressed. In addition, in this iontophoresis device, since the movement of the drug ions to the electrolyte retaining portion is blocked by the 2 nd ion exchange membrane, the problem of the drug being deteriorated by the chemical reaction at the time of energization is also solved.

On the other hand, the iontophoresis device in patent document 2 has a problem that it is difficult to automate the manufacturing process, mass-produce the product, or reduce the manufacturing cost because the number of components constituting the device is large, and the electrolyte solution holding portion 212 and the chemical solution holding portion 214 need to be handled in a wet state (a state with a high water content).

Patent document 1: U.S. Pat. No. 4744787 publication

Patent document 2: japanese patent No. 3040517

Non-patent document 1: an end-square straight section (braille) tip-a-KS chemical-tip tip-a-flexible polymer, lecture society, published in 1990 for 1 month

Non-patent document 2: "New Material シリ - ズ particle" related to Xiaolingzhen (Chinese character) "today's Structure technology, シ - エムシ publishing & gt, published 2004, 7 months

Disclosure of Invention

Problems to be solved by the invention

An object of the present invention is to provide an iontophoresis device that can suppress or suppress: generation of oxygen, chlorine or hydrogen in the electrode structure.

It is another object of the present invention to provide an iontophoresis device that can inhibit or suppress: generation of hydrogen ions, hydroxide ions, or hypochlorous acid in the electrode structure.

It is another object of the present invention to provide an iontophoresis device that can inhibit or suppress: the chemical agent is deteriorated by a chemical reaction when the current is applied.

It is another object of the present invention to provide an iontophoresis device that can inhibit or suppress: the generation of gas or ions or the alteration of the chemical as described above does not cause a large morphological change in the electrode by the energization.

It is another object of the present invention to provide an iontophoresis device that can inhibit or suppress: the above-described generation of gas or ions, or the deterioration of the chemical, and the simplification of the structure.

It is another object of the present invention to provide an iontophoresis device that can inhibit or suppress: the generation of gas or ions and the alteration of the chemical as described above facilitate automation of production and mass production.

The present invention addresses the problem of providing an iontophoresis device that can prevent or suppress: the production cost can be reduced by the generation of gas or ions or the deterioration of the chemical agent.

Means for solving the problems

The present invention is an iontophoresis device characterized by having at least one electrode structure body having an electrode formed with a doped layer formed of a substance that generates an electrochemical reaction by doping or dedoping ions.

In the present invention, the electrode provided in the electrode structure has a doped layer which is a layer of a substance that generates an electrochemical reaction by ion doping or dedoping (hereinafter, an electrode having such a doped layer may be referred to as a "doped electrode").

Accordingly, the doping or dedoping of ions into the doped layer causes the current to be applied from the power source to all or most of the electrolyte solution and the chemical solution, and as a result, the generation of gas such as oxygen, chlorine, or hydrogen, or the electrode reaction that generates undesirable ions such as hydrogen ions, hydroxyl ions, or hypochlorous acid, can be suppressed or at least reduced.

The term "electrochemical reaction by ion doping" as used herein means: when a positive or negative charge is applied to the doped layer, ions charged to the opposite charge are extracted from an electrolyte solution, a chemical solution, or the like in contact with the doped layer and doped (combined with a substance constituting the doped layer), thereby compensating for the applied charge; by "electrochemical reaction by dedoping of ions" is meant: in the case where positive charges are applied to the doped layer, the applied charges are compensated for by dedoping positive ions doped into the doped layer and being discharged from the doped layer, or in the case where negative charges are applied to the doped layer, the applied charges are compensated for by dedoping negative ions doped into the doped layer and being discharged from the doped layer.

As a material of the doped layer of the present invention, polyaniline, polypyrrole, polythiophene, polyacetylene, a derivative thereof, or a mixture thereof, which is a representative conductive polymer, is used, and among them, polyaniline is most preferably used. Non-patent documents 1 and 2 describe in detail derivatives of polyaniline, polypyrrole, polythiophene, or polyacetylene which can be used in the doped layer of the present invention.

There are various known methods for forming a conductive polymer or for forming a film of a conductive polymer, for example, a method of compressing a powdery conductive polymer chemically synthesized by an oxidative polymerization method; a method of forming an ink-like conductive polymer using a polar organic solvent such as N-methylpyrrolidone, molding the ink-like conductive polymer, and removing the solvent; or a method of forming a conductive polymer layer on a substrate by immersing an appropriate conductive substrate in a monomer solution for forming a conductive polymer to perform electrolytic polymerization. The doped layer of the present invention can be formed by any of these methods.

In this case, the entire doped layer may be composed of only the conductive polymer, or may contain a component other than the conductive polymer. For example, in order to provide mechanical strength against tearing, cracking, or the like to the doped layer, a conductive polymer may be impregnated into an appropriate woven fabric or nonwoven fabric, or a mixture of a conductive polymer and an appropriate polymer binder may be used, or a conductive filler such as carbon may be blended into a conductive polymer in order to improve the conductivity of the conductive polymer.

As described later, the conductive polymer may be doped with a drug ion to be injected into a living body or an ion to replace the drug ion doped in the 1 st ion exchange membrane, or may be doped with an ion serving as an electron acceptor or an electron donor in order to improve the conductivity of the conductive polymer.

In addition to the conductive polymer, examples of a material that can be used as the doped layer in the present invention include carbon materials such as black smoke and graphite.

As will be described later, the invention according to claim 14 can be used as an electrode structure having a doped electrode as it is as a non-operation side electrode structure, and can also be used as an operation side electrode structure when a doped layer is doped with a chemical ion before use.

That is, the dopant ions can be doped in the doped layer by applying a voltage of a conductivity type opposite to that of the drug ions to the doping electrode and applying current in a state where the doped layer is immersed in the drug solution containing the drug ions at an appropriate concentration.

Further, the drug ions can be introduced into the living body by applying a voltage of the same conductivity type as the drug ions to the doped electrode in a state where the doped layer doped with the drug ions is brought into contact with the living body skin.

In this case, since the chemical ions in the doped layer are dedoped and move to the living body, and the current is applied from the doped electrode to all or a part of the living body, the generation of the gas or the undesirable ions is suppressed or at least reduced.

The doped layer doped with the drug ions functions as an ion exchange membrane having the same conductivity type as the drug ions. That is, by doping the doped layer with positive agent ions, the doped layer is provided with an ion exchange function of allowing positive ions to pass therethrough and blocking negative ions from passing therethrough. Similarly, by doping the doped layer with negative agent ions, the doped layer is provided with an ion exchange function of allowing negative ions to pass therethrough and blocking positive ions from passing therethrough.

Therefore, when the drug ions are administered to a living body, the movement of counter ions (ions existing on the surface of or in the living body and charged in a conductivity type opposite to that of the drug ions) to the doped layer is blocked, and the amount of current consumed by the counter ions can be reduced, thereby improving the efficiency of drug administration.

In addition, when the electrode structure having the doped electrode is used as the operation-side electrode structure in the above-described state, the doping of the drug ions into the doped layer may be performed at any time from the stage of manufacturing the iontophoresis device or the operation-side electrode structure to the stage immediately before use (administration of the drug into the living body).

As described above, the iontophoresis device generally includes: in this case, the iontophoresis device of the present invention may be configured such that at least one of the active-side electrode structure and the non-active-side electrode structure is an electrode structure having a doped electrode, and preferably both of them are electrode structures having a doped electrode.

Depending on the type of the iontophoresis device, the agent to be administered to the living body may be held in both of two electrode structures connected to both poles of the power supply (in this case, both of the electrode structures are active side electrode structures and also non-active side electrode structures), or a plurality of electrode structures may be connected to each pole of the power supply.

Since the electrode structure having the doped electrode has an extremely simple structure, the electrode structure having the doped electrode can be easily automated and mass-produced as an iontophoresis device having an active-side electrode structure and/or a non-active-side electrode structure, and the production cost can be greatly reduced.

In the invention according to claims 1 to 3, the electrode structure further includes a chemical solution holding portion (claim 4) which is disposed on the front surface side of the doped layer and holds a chemical solution containing the 1 st conductivity type chemical ions.

Such an electrode structure can be used as an electrode structure on the action side of an iontophoresis device, and by applying a voltage of the 1 st conductivity type to the doped electrode in a state where the drug solution holding portion is in contact with the skin of a living body, drug ions in the drug solution holding portion are introduced into the living body.

In this case, since the doping layer takes in and dopes the 2 nd conductivity type ions in the chemical solution holding portion, the conduction from the doping electrode to the chemical solution holding portion occurs, and therefore, the generation of the gas and the undesirable ions can be suppressed.

In this case, the doping of the doped layer with the ions of the 1 st conductivity type and the dedoping of the ions of the 1 st conductivity type in the doped layer may cause the conduction of current from the doped electrode to the chemical solution holding portion. This aspect is also the same as in the invention of claim 7 and the like.

The doping of the 1 st conductivity type ions into the doped layer may be performed by: a voltage of the 2 nd conductivity type is applied to the doped electrode in a state where the doped layer is immersed in the electrolyte containing the 1 st conductivity type ions at an appropriate concentration.

In the invention according to claim 4, the electrode structure preferably further includes a 1 st ion exchange membrane of the 1 st conductivity type disposed on the front surface side of the chemical solution holding portion (claim 5).

In the electrode structure having such a configuration, the 1 st ion exchange membrane is brought into contact with the living skin, and a voltage of the 1 st conductivity type is applied to the doped electrode, whereby the drug ions in the drug solution holding portion are introduced into the living body through the 1 st ion exchange membrane.

In this case, since the 1 st ion exchange membrane blocks the movement of the living body counter ions to the drug solution holding portion, an additional effect of improving the drug ion administration efficiency can be obtained.

In the invention according to claim 4 or 5, it is preferable that the electrode structure further includes a 2 nd ion exchange membrane of the 2 nd conductivity type disposed on the front surface side of the doped layer, and the chemical solution retaining portion is disposed on the front surface side of the 2 nd ion exchange membrane (claim 6).

In the electrode structure having such a configuration, not only the administration of the chemical to the living body is performed in the same state as described above, but also the 2 nd ion exchange membrane blocks the movement of the chemical ions toward the doped electrode side, and therefore, the chemical in the vicinity of the doped electrode during the energization is prevented or suppressed from being deteriorated.

In this case, it is preferable that the 2 nd ion exchange membrane and the dope layer are integrally joined, whereby the energization properties between the dope layer and the 2 nd ion exchange membrane can be improved, and the assembly work of the electrode structure can be simplified. Therefore, automation and mass production of the electrode structure can be facilitated, and reduction in production cost can be achieved.

The 2 nd ion exchange membrane and the doped layer may be bonded by thermocompression bonding or the like, or by forming the doped layer on the 2 nd ion exchange membrane by the above-described various methods.

In the invention according to claims 1 to 3, the electrode structure may further include: an electrolyte retaining part which is arranged on the front side of the doped layer and retains electrolyte; and a 1 st ion exchange membrane of the 1 st conductivity type, the 1 st ion exchange membrane being disposed on the front surface side of the electrolyte retaining part and doped with the 1 st conductivity type chemical ions (claim 7).

Such an electrode structure can be used as an electrode structure on the action side of an iontophoresis device, and the drug ions doped in the 1 st ion exchange membrane can be injected into a living body by applying a voltage of the 1 st conductivity type to the doped electrode in a state where the 1 st ion exchange membrane is in contact with the skin of the living body.

Here, the electrolyte solution in the electrolyte solution holding portion has a function of supplying 1 st conductivity type ions for replacing the chemical ions in the 1 st ion exchange membrane (hereinafter, the 1 st conductivity type ions in the electrolyte solution are referred to as "1 st electrolytic ions") and a function of supplying 2 nd conductivity type ions for doping the doped layer (hereinafter, the 2 nd conductivity type ions in the electrolyte solution are referred to as "2 nd electrolytic ions").

That is, when the 2 nd electrolytic ions are taken into the dope layer and doped, the energization from the dope electrode to the electrolyte holding portion is generated, and the 1 st ion exchange membrane moves to the living body by being replaced with the 1 st electrolytic ions from the electrolyte holding portion.

The doping of the 1 st ion exchange membrane with the drug ions in the present invention can be performed by immersing the 1 st ion exchange membrane in a drug solution containing drug ions at an appropriate concentration for a predetermined time, and the amount of the drug ions to be doped into the 1 st ion exchange membrane can be controlled by adjusting the concentration of the drug ions, the immersion time, and the number of times of immersion in this case.

Further, when the mobility of the 1 st electrolytic ion is larger than that of the drug ion, the 1 st electrolytic ion may preferentially move to the living body than the drug ion, and the drug administration efficiency may be lowered, and therefore, it is preferable to select a composition in which the mobility of the 1 st electrolytic ion is approximately the same as or smaller than that of the drug ion in the electrolyte of the electrolyte retaining portion. Alternatively, the 1 st electrolytic ion in the electrolyte retaining part may be converted to a drug ion to prevent the above-described decrease in administration efficiency.

In the present invention, since the 1 st ion exchange membrane blocks the movement of the living body counter ions to the electrolyte retaining part, the administration efficiency of the drug ions can be improved, and since the 1 st ion exchange membrane, which is a member directly contacting the living body skin, holds the drug ions, the administration efficiency of the drug ions can be further improved.

Further, since the drug ions are doped into the 1 st ion-exchange membrane (in a state of being bonded to the ion-exchange groups in the ion-exchange membrane), the stability of the drug ions during storage is increased, and the amount of the stabilizer, the antibacterial agent, the preservative, and the like to be used can be reduced or the shelf life of the device can be prolonged. In addition, since the doping amount of the drug ions can be strictly adjusted, the safety of drug administration can be improved. Further, since the 1 st ion exchange membrane doped with the chemical ions is used instead of the chemical liquid holding portion which has conventionally been required to be handled in a wet state, the assembly operation of the electrode structure can be facilitated, and therefore, automation and mass production of the electrode structure can be facilitated, and the manufacturing cost can be reduced.

In the invention according to claim 7, it is preferable that the electrode structure further includes a 2 nd ion exchange membrane of the 2 nd conductivity type disposed on the front surface side of the electrolyte retaining portion, and the 1 st ion exchange membrane is disposed on the front surface side of the 2 nd ion exchange membrane (claim 8).

In such an electrode structure, not only the drug is administered to the living body in the same state as described above, but also the movement of the drug ions to the electrolyte retaining portion is blocked by the 2 nd ion exchange membrane, so that an additional effect of preventing the drug from being deteriorated at the time of energization is achieved.

However, since the 1 st electrolytic ions cannot move to the 1 st ion exchange membrane to replace the drug ions when the transport number of the 2 nd ion exchange membrane is 1, the 2 nd ion exchange membrane of the present invention uses an ion exchange membrane having a somewhat low transport number (for example, the transport number is 0.7 to 0.95), and even when such a 2 nd ion exchange membrane having a low transport number is used, the movement of the drug ions to the electrolyte retaining part can be sufficiently suppressed.

The migration number here is defined as: when a voltage of the 1 st conductivity type is applied to the electrolyte side in a state where the 2 nd ion exchange membrane is disposed between the electrolyte held in the electrolyte holding portion and the drug solution containing the drug ions and the drug counter ions at an appropriate concentration (for example, the drug solution for doping the 1 st ion exchange membrane with the drug ions), the drug counter ions are transported through the 2 nd ion exchange membrane in the total charge transported through the 2 nd ion exchange membrane in proportion to the amount of charge transported through the 2 nd ion exchange membrane.

In the invention of claim 8, since water may be electrolyzed at the interface between the 1 st and 2 nd ion exchange membranes depending on the conditions of energization and the like, a semipermeable membrane that allows at least the 1 st electrolytic ion to pass therethrough may be interposed between the 1 st and 2 nd ion exchange membranes in order to prevent such electrolysis.

The 2 nd ion exchange membrane of claim 8 may be replaced with a semipermeable membrane, and the same effect as that of the invention of claim 8 can be achieved by using a membrane having a molecular weight cut-off property that can block the passage of the drug ions and allows the passage of the 1 st electrolytic ions as the semipermeable membrane.

The interface of the 2 nd ion-exchange membrane/1 st ion-exchange membrane, the interface of the 2 nd ion-exchange membrane/semipermeable membrane/1 st ion-exchange membrane, and/or the interface of the semipermeable membrane/1 st ion-exchange membrane may be integrally joined by thermocompression bonding or the like, whereby the same effects as those described in claim 6 can be achieved.

In the invention according to claim 7, it is preferable that the electrode structure further includes a 2 nd ion exchange membrane of the 2 nd conductivity type disposed on the front surface side of the doped layer, and the electrolyte retaining portion is disposed on the front surface side of the 2 nd ion exchange membrane (claim 9).

In such an electrode structure, not only the administration of the drug to the living body is performed in the same state as the invention of claim 7, but also the movement of the drug ions to the doped layer electrode is blocked by the 2 nd ion exchange membrane, so that an additional effect of preventing the drug from being deteriorated at the time of energization is achieved.

The 2 nd ion exchange membrane of claim 9 may be replaced with a semipermeable membrane, and the same effect as that of the invention of claim 9 can be obtained by using, as the semipermeable membrane, a membrane having a molecular weight cut-off property which blocks passage of ions of the medicinal agent and allows passage of ions of the 1 st electrolyte on the other hand.

The interface between the doped electrode and the 2 nd ion exchange membrane or the interface between the doped electrode and the semipermeable membrane may be integrally joined as described in claim 6, whereby the same effects as described in claim 6 can be obtained.

In the invention according to claims 1 to 3, it is preferable that the electrode structure further includes a 1 st ion exchange membrane of the 1 st conductivity type, which is disposed on the front surface side of the doped layer, and is doped with the chemical ions of the 1 st conductivity type, and the doped layer is doped with the ions of the 1 st conductivity type (claim 10).

Such an electrode structure can be used as an electrode structure on the action side of an iontophoresis device, and by applying a voltage of the 1 st conductivity type to the doped electrode in a state where the 1 st ion exchange membrane is brought into contact with the skin of a living body, the 1 st conductivity type ions in the doped layer move to the 1 st ion exchange membrane, and the drug ions in the 1 st ion exchange membrane replaced with the ions move to the living body.

In this case, since the 1 st conductivity type ions in the doped layer move to the 1 st ion exchange membrane to generate the current from the doped electrode to the 1 st ion exchange membrane, the generation of the gas and the undesirable ions can be suppressed.

In the present invention, since the drug ions are introduced into the living body from the 1 st conductivity type ion exchange membrane doped with the drug ions, the effects of improving the drug administration efficiency and improving the stability of the drug ions are achieved as in the invention of claim 7.

In the present invention, since the doped layer is doped with the 1 st conductivity type ions for replacing the chemical ions, the electrolyte holding portion in the invention according to claim 7 can be omitted, and it is not necessary to treat a wet member at all when the electrode structure is assembled. In addition, the components necessary for assembly are only two of the doped electrode and the 1 st ion exchange membrane. Therefore, in the present invention, the assembly work of the electrode structure can be simplified, automation and mass production of the electrode structure can be facilitated, and the manufacturing cost can be reduced significantly.

In the present invention, doping of the doped layer with ions of the 1 st conductivity type can be performed in the same state as described in claim 4, and doping of the doped layer with ions of the chemical agent into the 1 st ion exchange membrane can be performed in the same state as described in claim 7.

Further, for the same reason as described in claim 7, the 1 st conductivity type ions doped in the doped layer are preferably ions having a mobility that is about the same as or smaller than that of the chemical ions.

The interface between the doped electrode and the 1 st ion exchange membrane can be integrally bonded by thermocompression bonding or the like, whereby the same effects as those described in claim 6 can be obtained.

In the invention according to claim 10, it is preferable that the electrode structure further includes a 2 nd ion exchange membrane of the 2 nd conductivity type disposed on the front surface side of the doped layer, and the 1 st ion exchange membrane is disposed on the front surface side of the 2 nd ion exchange membrane (claim 11).

In such an electrode structure, not only the same effect as the invention of claim 10 is achieved, but also the 2 nd ion exchange membrane blocks the movement of the chemical ions to the doped layer, so that an additional effect of preventing the chemical from being changed in quality at the time of energization is achieved.

Further, for the same reason as described in claim 7, the ion exchange membrane of the 2 nd aspect of the present invention is an ion exchange membrane having a somewhat lower transport number (for example, a transport number of 0.7 to 0.95) as in the case of claim 7.

The 2 nd ion exchange membrane of the invention of claim 10 may be replaced with a semipermeable membrane, and the same effect as that of the invention of claim 10 can be achieved by using, as the semipermeable membrane, a membrane having a molecular weight cut-off property that blocks passage of ions of the drug and allows passage of ions of the 1 st electrolyte.

The interface between the doped electrode and the 2 nd ion exchange membrane or the semipermeable membrane and/or the interface between the 2 nd ion exchange membrane or the semipermeable membrane and the 1 st ion exchange membrane may be integrally bonded by thermocompression bonding or the like, whereby the same effects as those described in claim 6 can be achieved.

In the invention according to claims 1 to 3, the doped layer may be doped with a chemical ion of the 1 st conductivity type (claim 12).

Such an electrode structure can be used as an electrode structure on the action side of an iontophoresis device, and the drug ions in the doped layer can be injected into a living body by applying a voltage of the 1 st conductivity type to the doped electrode in a state where the doped layer is in contact with the skin of the living body.

In this case, since the chemical ions doped in the doped layer move to the living body by dedoping and generate current conduction from the doped electrode to the living body skin, the generation of the gas or the undesirable ions can be suppressed.

In such a configuration, the working-side electrode structure can be constituted by a single member (doped electrode), and the manufacturing process can be greatly simplified, thereby facilitating mass production and reducing the manufacturing cost.

Further, since the doped layer doped with the 1 st conductivity type drug ions functions as an ion exchange membrane of the 1 st conductivity type, the movement of biological counter ions to the doped layer at the time of drug administration is blocked, and excellent characteristics can be obtained also in the drug administration efficiency.

Doping of the dopant ions into the doped layer may be performed by: the second conductivity type voltage is applied to the doped electrode in a state where the doped layer is immersed in a chemical solution containing chemical ions at an appropriate concentration to conduct energization.

In the invention according to claims 1 to 3, the electrode structure may further include a 1 st ion exchange membrane of the 1 st conductivity type disposed on the front surface side of the doped layer (claim 13).

Such an electrode structure can be used as an electrode structure on the action side of an iontophoresis device by doping the 1 st ion exchange membrane, or the 1 st ion exchange membrane and the doped layer with drug ions, and by applying a voltage of the 1 st conductivity type to the doped electrode in a state where the 1 st ion exchange membrane is brought into contact with the skin of a living body, the drug ions doped in the 1 st ion exchange membrane, or the 1 st ion exchange membrane and the doped layer can be injected into the living body.

The doping of the 1 st ion exchange membrane with the agent ions can be performed by: the second conductivity type voltage is applied to the doped electrode in a state where the doped layer is immersed in a chemical solution containing chemical ions at an appropriate concentration to conduct energization.

In this case, the positive ions bonded to the ion exchange groups in the 1 st ion exchange membrane, which are replaced with the chemical ions from the chemical solution, move to the doped layer and are doped. Alternatively, the chemical ions in the chemical solution are also doped into the doped layer according to the conditions for performing the doping.

Since the positive ions or the drug ions doped in the doped layer move to the 1 st ion exchange membrane to cause the energization from the doped electrode to the 1 st ion exchange membrane at the time of drug administration, the generation of the gas or the undesirable ions can be suppressed. The drug ions doped in the 1 st ion exchange membrane are replaced with the ions transferred from the doped layer and transferred to the living body.

In addition, the 1 st ion exchange membrane blocks the movement of the biological counter ions to the doped layer, so that the drug delivery efficiency can be improved.

In addition, unlike the invention according to claim 12, since the doped layer is not in direct contact with the living body skin, the drug can be safely administered even when the doped layer which is not preferable to be in direct contact with the living body skin is used.

In the present invention, the electrode structure body is constituted only by two members of the doped electrode and the 1 st ion exchange membrane, and it is not necessary to handle a wet member when assembling the action-side electrode structure body. Therefore, in the present invention, the assembly work of the electrode structure can be simplified, automation and mass production of the electrode structure can be facilitated, and the manufacturing cost can be reduced significantly.

The doping of the 1 st ion exchange membrane with the drug ions may be performed at any time from the stage of manufacturing the iontophoresis device to the stage immediately before use (administration of the drug to the living body).

The present invention may also be an iontophoresis device, comprising:

a working-side electrode structure that holds a drug ion of the 1 st conductivity type;

a non-working side electrode structure as a counter electrode of the working side electrode structure,

the inactive-side electrode structure has an electrode in which a doped layer is formed of a substance that generates an electrochemical reaction by ion doping or dedoping (claim 14).

In such an iontophoresis device, when a drug is administered, a voltage of the 2 nd conductivity type is applied to the doped electrode of the non-operation-side electrode structure, and generation of a gas such as hydrogen gas, oxygen gas, or chlorine gas, or generation of undesirable ions such as hydrogen ions, hydroxyl ions, or hypochlorous acid, in the non-operation-side electrode structure at that time, can be suppressed.

That is, when the doping layer is not doped with the 2 nd conductivity type ions, the conduction of the non-operation side electrode structure occurs by the movement and doping of the 1 st conductivity type ions on the skin or in the living body into the doping layer, and when the doping layer is doped with the 2 nd conductivity type ions, the conduction occurs by the movement and dedoping of the 2 nd conductivity type ions of the doping layer into the living body side.

The working-side electrode structure of the present invention may be such that the drug solution holding portion holding the drug solution holds the drug ions as in the invention of claim 4 or the like, or the drug ions may be doped into the 1 st ion exchange membrane or the doped layer and held as in the invention of claims 7, 10, 12 or the like. In addition, the active-side electrode structure of the present invention does not necessarily have to have a doped electrode.

In the invention according to claim 14, it is preferable that the inactive-side electrode structure further includes a 1 st conductivity type 3 rd ion exchange membrane disposed on the front surface side of the doped layer (claim 15).

In such an electrode structure, since the 3 rd ion exchange membrane is energized in a state of being in contact with the living body skin, an iontophoresis device is realized in which drug ions are administered without the impurity layer being in direct contact with the skin.

The conduction of the non-operation side electrode structure occurs mainly by the movement and doping of the 1 st conductivity type ions on or in the living body skin into the doped layer.

In the invention according to claim 14, it is preferable that the inactive-side electrode structure further includes a 3 nd ion exchange membrane of the 2 nd conductivity type disposed on the front surface side of the doped layer, and the doped layer is doped with ions of the 2 nd conductivity type (claim 16).

In such an electrode structure, an iontophoresis device in which drug ions can be administered without directly contacting the skin by the doped layer is realized, as in the invention according to claim 15.

Further, the ions of the second conductivity type 2 mainly in the doped layer are dedoped and moved to the living body side, and the current is applied to the non-operation side electrode structure.

The doped electrode/3 rd ion exchange membrane interface of the inventions of claims 15 and 16 can be integrally bonded by thermocompression bonding or the like, whereby the same effects as those described in claim 6 can be obtained.

In the invention according to claim 14, the non-active electrode structure may further include a 2 nd electrolyte retaining portion disposed on a front surface side of the doped layer and retaining an electrolyte, and in this case, the current is generated by movement of the 1 st electrolytic ion in the 2 nd electrolyte retaining portion to the doped layer for doping, movement of the 2 nd electrolytic ion to the living body, and the like.

The doped electrode according to any one of claims 1 to 16, preferably further comprising a conductive substrate, wherein the doped layer is laminated on the conductive substrate (claim 17).

As described above, the doped layer can improve its conductivity by doping ions as an electron acceptor or an electron donor, but by providing the doped layer on the conductive substrate, the surface resistance of the doped electrode is reduced, and conduction of a uniform current density from the doped layer is generated, whereby an iontophoresis device that can administer a drug more efficiently can be realized.

In addition, the formation of the doped layer on the conductive substrate may be performed by: for example, a substance obtained by blending a suitable binder polymer into a powdery conductive polymer, a substance obtained by dissolving a conductive polymer in a suitable polar organic solvent, and the like are applied to a conductive substrate and cured, and the solvent is removed; or by immersing the conductive substrate in a monomer solution for forming a conductive polymer to perform electrolytic polymerization.

In the invention of claim 17, the conductive substrate is preferably a conductive sheet formed of carbon fiber or carbon fiber paper (claim 18).

In this case, since the doped electrode can be formed without using a metal member, it is possible to prevent metal ions eluted from such a metal member from moving to the living body and causing health damage to the living body, since the carbon fiber or the carbon fiber paper is a material having a low sheet resistance, it is possible to generate energization of a uniform current density from the doped layer, and since the carbon fiber or the carbon fiber paper is a material having high flexibility, it is possible to provide an iontophoresis device having a flexible electrode structure which can follow the unevenness of the living body skin and the movement of the living body.

In this case, the electrodes described in Japanese patent application No. 2004-317317 and Japanese patent application No. 2005-222892 of the applicant of the present application can be used.

That is, in the invention of claim 18, the electrode may have a terminal member in which carbon is mixed in a polymer matrix, and the terminal member is attached to the conductive sheet (claim 19), or the electrode may have an extension portion formed of carbon fiber or carbon fiber paper integrally with the conductive sheet.

In the present specification, the term "drug" refers to a substance that has a certain pharmacological or medicinal effect and is applied to a living body for the purpose of treatment, recovery, prevention, promotion of health, maintenance, and the like of a disease, regardless of whether or not the drug is prepared.

In the present specification, "drug ion" refers to an ion generated by ionic dissociation of a drug, and refers to an ion that plays a pharmacological or pharmacological role, and "drug counter ion" refers to a counter ion of the drug ion. Dissociation of the drug into the drug ion may be caused by dissolving the drug in a solvent such as water, alcohol, acid, or alkali, or may be caused by applying a voltage and adding an ionizing agent.

The term "skin" as used herein refers to a surface of a living body to which a medicament can be administered by an iontophoresis device, and includes, for example, mucous membranes in the oral cavity. "organism" refers to a human or an animal.

In the present invention, "1 st conductivity type" means positive or negative electric polarity, and "2 nd conductivity type" means a conductivity type (negative or positive) opposite to the 1 st conductivity type.

The 1 st electrolytic ion and the 2 nd electrolytic ion contained in the electrolytic solution holding part of the present invention need not be of a single type, and may be of a plurality of types. Similarly, the chemical ions contained in the chemical liquid retaining portion or the chemical ions doped in the 1 st ion exchange membrane or the doped layer do not necessarily have to be a single type, and may be a plurality of types.

Ion exchange membranes are known to have various membranes, such as the following, in addition to the membrane-like ion exchange resin: a heterogeneous ion-exchange membrane obtained by dispersing an ion-exchange resin in a binder polymer, and heating and molding the dispersion to form a membrane; a homogeneous ion exchange membrane obtained by dissolving a composition containing a monomer capable of introducing an ion exchange group, a crosslinkable monomer, a polymerization initiator, or the like, or a resin having a functional group capable of introducing an ion exchange group in a solvent, impregnating and filling the resulting solution in a base material such as a cloth, a net, or a porous film, polymerizing or removing the solvent, and then conducting an ion exchange group introduction treatment. The ion-exchange membrane of the present invention can be any of these ion-exchange membranes, but among these, it is particularly preferable to use an ion-exchange membrane of a type in which pores of a porous film are filled with an ion-exchange resin.

More specifically, as the cation exchange membrane, an ion exchange membrane having a cation exchange group introduced thereto such as NEOSEPTA CM-1, CM-2, CMX, CMS, CMB manufactured by Tokuyama Corporation can be used, and as the anion exchange membrane, an ion exchange membrane having an anion exchange group introduced thereto such as NEOSEPTAAM-1, AM-3, AMX, AHA, ACH, ACS manufactured by Tokuyama Corporation can be used.

The "ion exchange membrane of the 1 st conductivity type" in the present specification refers to an ion exchange membrane having a function of selectively passing ions of the 1 st conductivity type. That is, when the 1 st conductivity type is positive, the "1 st conductivity type ion exchange membrane" is a cation exchange membrane, and when the 1 st conductivity type is negative, the "1 st conductivity type ion exchange membrane" is an anion exchange membrane.

Similarly, the "ion exchange membrane of the 2 nd conductivity type" refers to an ion exchange membrane having a function of selectively passing ions of the 2 nd conductivity type. That is, when the 2 nd conductivity type is positive, the "2 nd conductivity type ion exchange membrane" is a cation exchange membrane, and when the 2 nd conductivity type is negative, the "2 nd conductivity type ion exchange membrane" is an anion exchange membrane.

Examples of the cation exchange group introduced into the cation exchange membrane include a sulfonic acid group, a carbonic acid group, a phosphoric acid group, and the like, and by using a sulfonic acid group as a strongly acidic group, a cation exchange membrane having a high transport number can be obtained, and the transport number of the ion exchange membrane can be controlled depending on the kind of the cation exchange group introduced.

Examples of the anion exchange group that can be introduced into the anion exchange membrane include a primary amino group, a secondary amino group, a tertiary amino group, a quaternary ammonium group, a pyridyl group, an imidazolyl group, a quaternary pyridinium salt (quaternary pyridinium salt) group, a quaternary imidazolium salt (quaternary imidazolium) group, and the like.

Various methods such as sulfonation, chlorosulfonation, phosphating, hydrolysis and the like are known as treatments for introducing cation exchange groups, and various methods such as amination and alkylation are known as treatments for introducing anion exchange groups, and the transport number of the ion exchange membrane can be adjusted by adjusting the conditions of the treatments for introducing ion exchange groups.

The transport number of the ion-exchange membrane can be adjusted by the amount of the ion-exchange resin in the ion-exchange membrane, the pore size of the membrane, and the like. For example, in the case of an ion-exchange membrane of the type in which an ion-exchange resin is filled in a porous film, an ion exchange membrane obtained by filling an ion exchange resin with a porous film having a film thickness of 5 to 140 μm, more preferably 10 to 120 μm, and most preferably 15 to 55 μm, and a filling rate of 5 to 95 mass%, more preferably 10 to 90 mass%, and particularly preferably 20 to 60 mass%, using a porous film having a plurality of pores with an average pore diameter (average flow pore diameter measured by the bubble point method (JIS K3832-1990)) of 0.005 to 5.0 μm, more preferably 0.01 to 2.0 μm, and most preferably 0.02 to 0.2 μm and a porosity of 20 to 95%, more preferably 30 to 90%, and most preferably 30 to 60%, and an ion exchange resin, and the migration number of the ion exchange membrane can be adjusted according to the average pore diameter, porosity, and filling rate of the ion exchange resin of the porous film.

In the present specification, the phrase "blocking the passage of ions" as used in relation to an ion exchange membrane of the 1 st conductivity type or the 2 nd conductivity type does not necessarily mean that all ions are not allowed to pass through at all, and includes, for example, a case where the passage of biological counter ions is suppressed to such an extent that: even if ions pass at a certain speed, the degree of the ions is small, so that even if the device is stored for a practically sufficient time, the drug does not deteriorate near the electrodes during energization; or, the passage of biological counter ions is suppressed to such an extent that the efficiency of drug administration can be sufficiently improved.

Similarly, the phrase "allow ions to pass through" as used herein with respect to an ion exchange membrane of the 1 st conductivity type or the 2 nd conductivity type does not mean that there is no restriction on the passage of ions at all, and includes a case where ions pass through at a sufficiently high speed or in a high amount as compared with ions of the opposite conductivity type even when the passage of ions is restricted to some extent.

In the present specification, the terms "block ion passage" and "allow ion passage" as used with respect to the semipermeable membrane are the same as those described above, and do not mean that ions are not allowed to pass at all, and that no limitation is imposed on the passage of ions at all.

Drawings

Fig. 1 is an explanatory view schematically showing the configuration of an iontophoresis device according to an embodiment of the present invention.

Fig. 2(a) to (D) are cross-sectional explanatory views showing the structure of the working electrode structure of the iontophoresis device according to the embodiment of the present invention.

Fig. 3(a) is an explanatory view showing the structure of a measurement cell used for evaluating the characteristics of an electrode used in the iontophoresis device of the present invention, and (B) and (C) are explanatory views showing the measurement results of a chronopotentiometry and a cyclic voltammogram using the same measurement cell.

Fig. 4(a) to (D) are cross-sectional explanatory views showing the structure of the working electrode structure of the iontophoresis device according to the embodiment of the present invention.

Fig. 5(a) and (B) are sectional explanatory views showing the structure of the working electrode structure of the iontophoresis device according to the embodiment of the present invention.

Fig. 6(a) and (B) are sectional explanatory views showing the structure of the working electrode structure of the iontophoresis device according to the embodiment of the present invention.

Fig. 7(a) to (D) are cross-sectional explanatory views showing the structure of the non-operation side electrode structure of the iontophoresis device according to the embodiment of the present invention.

Fig. 8(a) is a plan view of an electrode used in the iontophoresis device according to the embodiment of the present invention. (B) Is a cross-sectional view taken along line A-A. (C) A cross-sectional view showing a modification thereof.

Fig. 9(a) is a plan view of another type of electrode used in the iontophoresis device according to the embodiment of the present invention. (B) Is a cross-sectional view taken along line A-A. (C) A cross-sectional view showing a state where the electrode is accommodated in the container is shown.

Fig. 10 is an explanatory view showing the structure of a conventional iontophoresis device.

Fig. 11 is an explanatory view showing the structure of another conventional iontophoresis device.

Detailed Description

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

Fig. 1 is an explanatory view showing a schematic configuration of an iontophoresis device X of the present invention.

For convenience of explanation, an iontophoresis device for administering a drug (e.g., lidocaine hydrochloride, morphine hydrochloride, etc.) in which a drug effective component is dissociated into positive drug ions will be described below as an example, and in the case of an iontophoresis device for administering a drug (e.g., ascorbic acid, etc.) in which a drug effective component is dissociated into negative drug ions, an electrode of a power source, conductivity of each ion exchange membrane, and conductivity of ions doped in a doped layer or a cation exchange membrane in the following description may be reversed to constitute an iontophoresis device capable of achieving substantially the same effects as those in the following embodiments.

As shown in the figure, the iontophoresis device X includes a power supply 30, an active-side electrode structure 10 connected to a positive electrode of the power supply 30 via a power supply line 31, and a non-active-side electrode structure 20 connected to a negative electrode of the power supply 30 via a power supply line 32.

The active-side electrode structure 10 and the non-active-side electrode structure 20 have containers 16 and 26 having open lower surfaces 16b and 26b, the container 16 is composed of an upper wall 16u and an outer peripheral wall 16s, and the container 26 is composed of an upper wall 26u and an outer peripheral wall 26s, and a space capable of accommodating various structures described below is formed inside the container.

The containers 16 and 26 may be made of any material such as plastic, but are preferably made of a soft material that can prevent evaporation of water from inside and intrusion of foreign matter from outside, and can follow the unevenness of the skin and the movement of the living body. In addition, a detachable liner made of an appropriate material for preventing evaporation of water and contamination of foreign substances during storage of the iontophoresis device X may be attached to the lower surfaces 16b and 26b of the containers 16 and 26, and an adhesive layer for improving adhesion to the skin at the time of administration of the drug may be provided at the lower end portions 16e and 26e of the outer peripheral walls 16s and 26 s.

In addition, when there is no wet member (member having a high water content) such as a chemical liquid holding portion or an electrolyte liquid holding portion, as in the working-side electrode structures 10H to 10K and the non-working-side electrode structures 20A to 20C described later, the containers 16 and 26 are not necessarily provided.

As the power source 30, a battery, a constant voltage device, a constant current device, a constant voltage/constant current device, or the like can be used, and the following constant current device is preferable: the device can be controlled at 0.01-1.0 mA/cm²Preferably 0.01 to 0.5mA/cm²The current is adjusted within the range of (1) and the operation is performed under a safe voltage condition of 50V or less, preferably 30V or less.

Fig. 2(a) to (D) are cross-sectional explanatory views showing the structures of the operation-side electrode structures 10A to 10D that can be used as the operation-side electrode structure 10 of the iontophoresis device X.

The working-side electrode structure 10A includes: an electrode 11 having a conductive base material 11a connected to the power supply line 31 and a doped layer 11b formed on one surface of the base material 11 a; and a chemical liquid holding portion 14 that holds the chemical liquid in contact with the doped layer 11 b.

The electrode 11 may be composed of, for example, a base material 11a and a doped layer 11b, the base material 11a may be composed of a carbon sheet, and the doped layer 11b may be formed by applying a polyaniline solution in which polyaniline salt is mixed with a PVDF (polyvinylidene fluoride) solution in NMP (N-methylpyrrolidone) and drying the polyaniline solution on the base material 11 a.

Polyaniline salt obtained by adding 1N hydrochloric acid to polyaniline in an intermediate oxidation state, followed by filtration and drying was applied to a carbon sheet 300 μm thick and 17mm in diameter in a weight ratio of polyaniline salt to PVDF to NMP of 200mg, and the carbon sheet was vacuum-dried at 100 ℃ for 1 hour to prepare an electrode 11, and a chronopotentiometry and cyclic voltammogram were measured using a measurement cell shown in FIG. 3 (A).

FIG. 3(B) is a graph showing a curve at 0.3mA/cm²The result of measuring the capacitor capacity of the electrode 11 by a non-constant electrochemical method under the constant current condition of (2) confirms that the electrode 11 has an extremely large capacitor capacity.

Fig. 3C shows the measurement results of cyclic voltammograms in the case (a) where a nonwoven fabric impregnated with a 0.9% NaCl + 2% HPC (hydroxypropyl cellulose) aqueous solution was used as the electrolyte layer of the measurement cell, and in the case (b) where a nonwoven fabric impregnated with a 10% lidocaine hydrochloride + 2% HPC aqueous solution was used as the electrolyte layer of the measurement cell. The potential sweep range of (a) was set to-1.2 to +1.2V, the potential sweep range of (b) was set to-0.8 to +0.8V, and the potential sweep rates (a) and (b) were both measured at 10 mV/sec. As can be seen from fig. 3 (C): the electrode 11 has excellent charge/discharge characteristics and is resistant to deterioration due to oxidation-reduction cycles.

The drug solution is a drug solution in which a drug effective component is dissociated into positive drug ions, and the drug solution holding unit 14 may hold the drug solution in a liquid state or may hold the drug solution by immersing the drug solution in an appropriate absorbent carrier such as gauze, filter paper, or gel.

In the operation-side electrode assembly 10A, the drug ions in the drug solution holding portion 14 are introduced into the living body by applying a positive voltage to the electrode 11 in a state where the drug solution holding portion 14 is in contact with the living skin. When the negative ions in the chemical solution move to the doped layer 11b and are doped, the electrode 11 is energized to all or part of the chemical solution holding portion 14. Therefore, the generation of oxygen and chlorine gas, the generation of hydrogen ions, and the generation of hypochlorous acid due to the energization are prevented or at least reduced.

The thickness of the doped layer 11b is typically about 10nm to 100 μm, and particularly preferably 1 to 10 μm.

The working-side electrode assembly 10B has the same electrode 11 and chemical solution holding portion 14 as the working-side electrode assembly 10A, and a cation exchange membrane 15 is provided on the front surface side of the chemical solution holding portion 14.

The working-side electrode structure 10B achieves the same effect as the working-side electrode structure 10A in that not only the generation of gas and the generation of undesirable ions during energization are suppressed, but also the migration of biological counter ions to the chemical solution holding portion 14 is blocked by the cation exchange membrane 15, thereby achieving an additional effect of improving the administration efficiency of chemical ions.

The working-side electrode assembly 10C has the same electrode 11 and chemical solution holding portion 14 as the working-side electrode assembly 10A, and an anion exchange membrane 13 is further provided between the electrode 11 and the chemical solution holding portion 14.

In the working-side electrode structure 10C, the negative ions in the chemical solution holding portion 14 migrate through the anion exchange membrane 13 to the doped layer 11b and are doped, thereby causing the current to flow from the electrode 11 to the chemical solution holding portion 14. Therefore, the same effect as that of the working-side electrode structure 10A is achieved in terms of suppressing the generation of gas and the generation of undesirable ions during energization.

In addition, in the working-side electrode structure 10C, the movement of the drug ions in the drug solution holding portion 14 to the doped layer 11b is blocked by the anion exchange membrane 13, and therefore, an additional effect of preventing decomposition and alteration of the drug at the time of energization is achieved.

The working-side electrode assembly 10D has the same electrode 11 and chemical solution holding portion 14 as the working-side electrode assembly 10A, and further has an anion exchange membrane 13 between the electrode 11 and the chemical solution holding portion 14, and a cation exchange membrane 15 on the front side of the chemical solution holding portion 14.

Therefore, in the working-side electrode assembly 10D, not only the same effect as that of the working-side electrode assembly 10A is achieved in terms of suppressing the generation of gas and the generation of undesirable ions at the time of energization, but also additional effects of preventing the decomposition and alteration of the chemical at the time of energization and improving the administration efficiency of the chemical are achieved in the same manner as the working-side electrode assemblies 10B and 10C.

In the working-side electrode structures 10C and 10D, the electrode 11 and the anion exchange membrane 13 can be joined and integrated by a method such as thermocompression bonding, whereby the state of current flow from the electrode 11 to the anion exchange membrane 13 can be improved, and the assembly work of the working-side electrode structures 10C and 10D can be facilitated.

Fig. 4(a) to (C) are cross-sectional explanatory views showing the structures of operation-side electrode structures 10E to 10G of another form that can be used as the operation-side electrode structure 10 of the iontophoresis device X.

The working-side electrode structure 10E has: an electrode 11 similar to the working-side electrode structure 10A; an electrolyte holding unit 12 for holding an electrolyte in contact with the doped layer 11 b; and a cation exchange membrane 15 which is disposed on the front surface side of the electrolyte retaining part 12 and is doped with positive chemical ions.

In the working-side electrode assembly 10E, the drug ions doped in the cation exchange membrane 15 are introduced into the living body by applying a positive voltage to the electrode 11 in a state where the cation exchange membrane 15 is in contact with the living body skin.

In this case, the cation exchange membrane 15 blocks the movement of the biological counter ions to the electrolyte retaining part 12, and therefore, the drug can be administered efficiently.

The current flowing from the electrode 11 to all or part of the electrolyte retaining portion 12 is generated by doping the electrolyte through the movement of negative ions in the electrolyte to the doped layer 11 b. Therefore, the generation of oxygen and chlorine gas, the generation of hydrogen ions, and the generation of hypochlorous acid due to the energization are prevented or at least reduced.

The positive ions in the electrolyte retaining part 12 are transferred to the cation exchange membrane 15, and the positive ions are replaced with the chemical ions transferred to the living body and are bonded to the ion exchange groups in the cation exchange membrane 15, and electric current is applied from the electrolyte retaining part 12 to the cation exchange membrane 15.

The electrolyte retaining portion 12 of the working-side electrode structure 10E may retain the electrolyte in a liquid state, or may retain the electrolyte by immersing it in an absorbent carrier such as gauze, filter paper, or gel.

When the positive ions in the electrolyte retaining part 12 have a higher mobility than the drug ions, the positive ions preferentially move to the living body, and the drug administration efficiency may be lowered, and therefore, the electrolyte in the electrolyte retaining part 12 preferably has a composition that does not include positive ions having a mobility equal to or higher than that of the drug ions.

The doping of the cation exchange membrane 15 with the drug ions can be performed by immersing the cation exchange membrane 15 in a drug solution containing the drug ions at an appropriate concentration.

The working-side electrode assembly 10F has the same electrode 11, electrolyte retaining section 12, and cation-exchange membrane 15 as the working-side electrode assembly 10E, and further has an anion-exchange membrane 13 between the electrolyte retaining section 12 and the cation-exchange membrane 15.

In the working-side electrode assembly 10F, not only the same effect as that of the working-side electrode assembly 10E is achieved in terms of suppressing the generation of gas and undesirable ion generation at the time of energization, but also the movement of the chemical ions doped in the cation exchange membrane 15 to the electrolyte retaining portion 12 is blocked by the anion exchange membrane 13, so that an additional effect of preventing the chemical in the vicinity of the electrode 11 at the time of energization is achieved.

In the working-side electrode assembly 10F, in order to generate the current from the electrolyte retaining part 12 to the cation exchange membrane 15, it is necessary that the positive ions in the electrolyte retaining part 12 move to the cation exchange membrane 15 through the anion exchange membrane 13, and therefore, an anion exchange membrane having a somewhat low migration number is used for the anion exchange membrane 13.

In the working-side electrode assembly 10F, depending on the energization conditions and the like, electrolysis of water may occur at the interface between the anion-exchange membrane 13 and the cation-exchange membrane 15, and therefore, in order to prevent such electrolysis, a semipermeable membrane that allows at least the positive ions of the electrolyte solution retaining portion 12 to pass therethrough may be disposed between the anion-exchange membrane 13 and the cation-exchange membrane 15. By bonding the interface between the anion-exchange membrane 13 and the cation-exchange membrane 15 or the interfaces of the anion-exchange membrane 13/semipermeable membrane/cation-exchange membrane 15 by a method such as thermocompression bonding, the electrical conductivity and the handling properties between these members can be improved.

The anion exchange membrane 13 of the working-side electrode assembly 10F allows cations in the electrolyte retaining part 12 to pass therethrough, but can achieve the same effect as described above even if it is replaced with a semipermeable membrane that blocks the passage of drug ions.

The working-side electrode assembly 10G includes the same electrode 11, electrolyte retaining portion 12, and cation-exchange membrane 15 as the working-side electrode assembly 10E, and further includes an anion-exchange membrane 13 between the electrode 11 and the electrolyte retaining portion 12.

In the working-side electrode structure 10G, the negative ions in the electrolyte solution holding portion 12 migrate through the anion exchange membrane to the dope layer and dope the layer, thereby causing the current to flow from the electrode 11 to the electrolyte solution holding portion 12. Therefore, the same effect as that of the working-side electrode structure 10E is achieved in terms of suppressing the generation of gas and the generation of undesirable ions during energization.

Similarly to the working-side electrode assembly 10E, current is passed from the electrolyte retaining portion 12 to the cation exchange membrane 15. Further, since the movement of the drug ions doped in the cation exchange membrane 15 to the doped layer 11b is blocked by the anion exchange membrane 13, an additional effect of preventing decomposition and alteration of the drug at the time of energization is achieved.

The electrode 11 and the anion exchange membrane 13 may be joined and integrated by a method such as thermocompression bonding to improve the electrical conductivity and handling property between the two.

Fig. 5(a) and (B) are cross-sectional explanatory views showing the structures of another type of operation-side electrode structures 10H and 10I that can be used as the operation-side electrode structure 10 of the iontophoresis device X.

The active-side electrode structure 10H includes an electrode 11 and a cation exchange membrane 15, the electrode 11 includes a conductive base material 11a connected to the power supply line 31, and a doped layer 11b formed on one surface of the base material 11a and doped with positive ions, and the cation exchange membrane 15 is disposed on the front surface side of the doped layer 11b and doped with chemical ions.

In the action-side electrode structure 10H, since the drug ions doped in the cation exchange membrane 15 are administered to the living body by applying a positive voltage to the electrode 11 in a state where the cation exchange membrane 15 is in contact with the living body skin, drug administration can be performed with high efficiency in the same manner as in the action-side electrode structure 10E.

In the working-side electrode structure 10H, the positive ions doped in the doped layer 11b move to the cation exchange membrane 15, and thus the current flow from the electrode 11 to the cation exchange membrane 15 is generated, and therefore, the generation of oxygen and chlorine, the generation of hydrogen ions, and the generation of hypochlorous acid due to the current flow are prevented or at least reduced. The positive ions that have migrated from doped layer 11b into cation exchange membrane 15 are replaced with drug ions that have migrated into the living body and are bonded to the ion exchange groups of cation exchange membrane 15.

As shown in the drawing, the operation-side electrode structure 10H has an extremely simple structure including the electrode 11 and the cation exchange membrane 15, and since no wet member needs to be handled when assembling the operation-side electrode structure 10H, automation and mass production of the operation-side electrode structure 10H are extremely easy, and the manufacturing cost of the operation-side electrode structure 10 can be significantly reduced.

The electrode 11 and the cation exchange membrane 15 may be joined and integrated by a method such as thermocompression bonding, thereby improving the electrical conductivity and operability between the two.

Doping of positive ions into the doped layer 11b of the working-side electrode structure 10H can be performed by applying current to the electrode 11 as a negative electrode in a state where the doped layer 11b is immersed in an appropriate electrolyte, and doping of chemical ions into the cation exchange membrane 15 can be performed for the working-side electrode structure 10E by the same method as described above.

For the same reasons as described for the working-side electrode structure 10E, it is preferable that the doped layer 11b is doped with positive ions having a mobility lower than that of the chemical ions, and the chemical ions that are the same as or different from the chemical ions doped in the cation exchange membrane 15 may be doped as the positive ions.

The working-side electrode structure 10I has the same electrode 11 and cation exchange membrane as the working-side electrode structure 10H, and further has an anion exchange membrane 13 between the electrode 11 and the cation exchange membrane 15.

In the working-side electrode structure 10I, as in the working-side electrode structure 10H, generation of oxygen gas and chlorine gas, generation of hydrogen ions and hypochlorous acid at the time of drug administration are prevented, and a wet member does not need to be handled at the time of assembly. Further, the movement of the drug ions doped in the cation exchange membrane 15 to the electrolyte retaining part 12 is blocked by the anion exchange membrane 13, and therefore, an additional effect of preventing decomposition and alteration of the drug at the time of energization is achieved.

In the working-side electrode structure 10I, in order to generate the current from the electrode 11 to the cation exchange membrane 15, the positive ions doped in the doped layer 11b need to move to the cation exchange membrane 15 through the anion exchange membrane 13, and therefore, an anion exchange membrane having a somewhat low migration number is used as the anion exchange membrane 13.

The electrode 11, the anion-exchange membrane 13, and the cation-exchange membrane may be joined and integrated by a method such as thermocompression bonding, thereby improving the electrical conductivity and operability between these members.

The anion exchange membrane 13 of the working-side electrode assembly 10I allows positive ions in the electrolyte retaining part 12 to pass therethrough, but can achieve the same effects as described above even if it is replaced with a semipermeable membrane that blocks the passage of drug ions.

Fig. 6(a) and (B) are cross-sectional explanatory views showing the structures of different types of operation-side electrode structures 10J and 10K that can be used as the operation-side electrode structure 10 of the iontophoresis device X.

The working-side electrode structure 10J has an electrode 11, and the electrode 11 includes a conductive base material 11a connected to the power supply line 31 and a doped layer 11b formed on one surface of the base material 11 a.

In the operation-side electrode structure 10J, the doped layer 11b is doped with drug ions, and then, a positive voltage is applied to the electrode 11 in a state where the doped layer 11b is in contact with the living skin, whereby the drug ions doped in the doped layer 11b are introduced into the living body.

Since the aforementioned movement of the drug ions causes the conduction of electricity from the doped layer 11b to the living body skin, the generation of oxygen and chlorine gas, the generation of hydrogen ions, and hypochlorous acid due to the conduction of electricity are prevented or at least reduced.

Further, since the doped layer 11b doped with the drug ions as positive ions has a cation exchange function, the drug can be administered efficiently by blocking the movement of biological counter ions from the skin side to the doped layer 11b at the time of administration of the drug.

As shown in the drawing, the working-side electrode structure 10J has a very simple structure constituted only by the electrode 11, and it is possible to make automation and mass production of the working-side electrode structure 10J extremely easy and to significantly reduce the production cost of the working-side electrode structure.

The doping of the doped layer 11b with the chemical ions can be performed by applying current to the electrode 11 as a negative electrode in a state where the doped layer 11b is immersed in the chemical solution containing the chemical ions at an appropriate concentration. The doping may be performed at the stage of manufacturing the iontophoresis device X or the operation-side electrode structure 10J, or may be performed immediately before the administration of the drug.

The working-side electrode structure 10K includes an electrode 11 and a cation-exchange membrane 15 disposed on the front surface side of the electrode 11, and the electrode 11 includes a conductive base material 11a connected to a power supply line 31 and a doped layer 11b formed on one surface of the base material 11 a.

In the working-side electrode structure 10K, the cation exchange membrane 15, or the cation exchange membrane 15 and the doped layer 11b are doped with the drug ions, and then, by applying a positive voltage to the electrode 11 in a state where the cation exchange membrane 15 is brought into contact with the living body skin, the drug ions doped in the cation exchange membrane 15, or the cation exchange membrane 15 and the doped layer 11b are introduced into the living body through the cation exchange membrane 15.

In the working-side electrode structure 10K, the current flow from the electrode 11 to the cation exchange membrane 15 is generated by the movement of the ions doped in the doped layer 11b to the cation exchange membrane, and therefore, the generation of oxygen and chlorine, the generation of hydrogen ions, and the generation of hypochlorous acid due to the current flow are prevented or at least reduced.

Further, the movement of biological counter ions from the biological body to doped layer 11b is blocked by cation exchange membrane 15, and thus drug administration can be performed efficiently.

Since the operation-side electrode structure 10K has a very simple structure composed of only the electrode 11 and the cation exchange membrane 15, automation and mass production of the operation-side electrode structure 10K can be facilitated, and the manufacturing cost of the operation-side electrode structure can be significantly reduced.

Further, since the active-side electrode structure 10K has a structure in which the doped layer 11b is not in direct contact with the skin, even when the doped layer 11b formed of a substance that is not preferable to be in contact with a living body is used, it is possible to administer a drug without fear of health damage or the like to the living body.

The doping of the cation exchange membrane 15 or the cation exchange membrane 15 and the doped layer 11b can be performed by applying current to the electrode 11 as a negative electrode in a state where the cation exchange membrane 15 is immersed in a chemical solution containing chemical ions at an appropriate concentration. The doping may be performed at the stage of manufacturing the iontophoresis device X or the operation-side electrode structure 10K, or may be performed immediately before the administration of the drug.

Further, by bonding and integrating the electrode 11 and the cation exchange membrane 15 by a method such as thermocompression bonding, the electrical conductivity and the handling property between the two can be improved.

Fig. 7(a) to (D) are cross-sectional explanatory views showing the structures of the non-operation side electrode structures 20A to 20D that can be used as the non-operation side electrode structure 20 of the iontophoresis device X.

The inactive-side electrode structure 20A includes an electrode 21, and the electrode 21 includes a conductive base material 21a connected to the power supply line 32 and a doped layer 21b formed on the base material 21 a.

In the non-operation-side electrode structure 20A, when a negative voltage is applied to the electrode 21 in a state where the doped layer 21b is in contact with the living body, the positive ions move from the living body skin to the doped layer 21b to generate the electric current, and therefore, the generation of hydrogen gas and the generation of hydroxide ions at the time of the electric current application are prevented or at least reduced.

When a doped layer doped with anions in advance is used as the doped layer 21b of the non-active electrode structure 20A, the negative ions move to the living body skin, and the positive ions move from the living body skin to the doped layer 21b to generate electricity, and at this time, the generation of hydrogen gas and the generation of hydroxide ions are also prevented or at least reduced.

The structure of the non-operation-side electrode structure 20A is the same as that of the operation-side electrode structure 10I. Therefore, the non-operation-side electrode structure 20A and the operation-side electrode structure 10J can be manufactured in the same process, so that the manufacturing process of the iontophoresis device is greatly simplified, the manufacturing automation and mass production are facilitated, and the manufacturing cost is greatly reduced.

The non-active side electrode structure 20B includes the same electrode 21 as the non-active side electrode structure 20A, and a cation exchange membrane 25C disposed on the front side of the doped layer 21B.

In the non-operation side electrode structure 20B, since the positive ions migrate from the living body skin through the cation exchange membrane 25C to the doped layer 21B and are doped, the generation of hydrogen gas and the generation of hydroxide ions at the time of energization are prevented or at least reduced.

Further, since the inactive-side electrode structure 20B has a structure in which the doped layer 21B is not in direct contact with the skin, even when the doped layer 21B formed of a substance that is not preferable to be in contact with a living body is used, drug administration can be performed safely.

The electrode 21 and the cation exchange membrane 25C can be bonded and integrated by a method such as thermocompression bonding, whereby the electrical conductivity and the operability between the two can be improved.

The structure of the non-operation-side electrode structure 20B is the same as that of the operation-side electrode structure 10K. Therefore, the non-operation-side electrode structure 20B and the operation-side electrode structure 10K can be manufactured in the same process, so that the manufacturing process of the iontophoresis device is greatly simplified, the manufacturing automation and mass production are facilitated, and the manufacturing cost is greatly reduced.

The inactive-side electrode structure 20C includes: an electrode 21 and an anion exchange membrane 25A, the electrode 21 has a conductive base material 21a connected to the power supply line 32, and a doped layer 21b formed on the base material 21a and doped with negative ions, and the anion exchange membrane 25A is disposed on the front side of the doped layer 21 b.

In the non-action-side electrode structure 20C, when a negative voltage is applied to the electrode 21 in a state where the anion exchange membrane 25A is in contact with the living body, the negative ions doped in the doped layer 21b move to the anion exchange membrane 25A and further move to the living body to generate the current, or the counter ions, which are replaced by the negative ions and originally bonded to the ion exchange groups in the anion exchange membrane 25A, move to the living body to generate the current. Therefore, generation of hydrogen gas and generation of hydroxide ions at the time of energization are suppressed.

By bonding and integrating the electrode 21 and the anion exchange membrane 25A by a method such as thermocompression bonding, the electrical conductivity and the handling property between the two can be improved.

The non-operation side electrode structure 20D has the same electrode 21 as the non-operation side electrode structure 20A, and further has an electrolyte holding portion 22 for holding the electrolyte in contact with the doped layer 21b, and an anion exchange membrane 25A disposed on the front side of the electrolyte holding portion 22.

In the non-operation-side electrode structure 20D, when a negative voltage is applied to the electrode 21 in a state where the anion exchange membrane 25A is in contact with the living body, the positive ions of the electrolyte retaining portion 22 move to the doped layer 21b and are doped, and thus, the energization is generated, and therefore, the generation of hydrogen gas and the generation of hydroxide ions are suppressed at the time of energization.

Between the electrolyte retaining part 22 and the living body skin, the negative ions passing through the electrolyte retaining part 22 move to the living body skin through the anion exchange membrane 25A to generate the current.

Fig. 8(a) is a plan view of an electrode 40 particularly preferably used as the electrode 11 of the working-side electrode structures 10A to 10K or the electrode 21 of the non-working-side electrode structures 20A to 20D, and fig. 8(B) is a cross-sectional view thereof taken along line a-a.

In the drawing, 41 denotes a conductive substrate made of carbon fibers, a doped layer 42 made of a conductive polymer or the like is formed on one surface of the substrate 41, and a terminal member 43 is attached to the opposite surface thereof, and the terminal member 43 is constituted by a male fitting portion 43a, a main body portion 43b, and a joining portion 43 c.

The terminal member 43 is made as follows: the mold disposed on the substrate 41 is heated and vulcanized to a composition in which a carbon filler such as graphite (graphite), black lead, carbon black, or fine powder of glassy carbon, or short fibers obtained by cutting carbon fibers is blended in a polymer matrix such as silicone rubber, and the composition is cured. The base material 41 and the terminal member 43 are integrated at the joint portion 43c by curing the composition in a state of being impregnated into the carbon fibers constituting the base material 41.

Since the carbon fibers have high conductivity and flexibility, the electrode 40 can be energized at a uniform current density from the doped layer 42, and the active-side electrode structures 10A to 10K and the inactive-side electrode structures 20A to 20D having flexibility capable of following the unevenness of the living skin and the movement of the living body can be realized.

Further, the connection from the power supply 30 to the power supply lines 31 and 32 can be performed using a connector having a female fitting portion to be fitted to the male fitting portion 43a, and even when a metal material is used for the female fitting portion, since the male fitting portion 43a is separated from the base material 41 by the body portion 43b, the metal of the connector is prevented from being eluted and moved to the living body.

The method of attaching the terminal member 43 to the base material 41 is arbitrary, and for example, as shown in fig. 8(C), the terminal member 43 may be provided with the locking portions 43d and 43e, or the terminal member may be attached by inserting the locking portion 43e through a small hole provided in the base material 41.

Fig. 9(a) is a plan view of another electrode 50 particularly preferably used as the electrode 11 of the working-side electrode structures 10A to 10K or the electrode 21 of the non-working-side electrode structures 20A to 20D, and fig. 9(B) is a cross-sectional view thereof taken along line a-a.

In the figure, 51 is a base material formed of carbon fibers having a circular conductive sheet portion 51a and an elongated extension portion 51b extending from the conductive sheet portion 51 a. A doped layer 52 is formed on one surface of the conductive sheet portion 51 a.

Like the electrode 40, the electrode 50 can be energized at a uniform current density from the doped layer 52, and can realize the active-side electrode structures 10A to 10K and the inactive-side electrode structures 20A to 20D having flexibility that can follow the unevenness of the living skin and the movement of the living body.

As shown in fig. 9(C), the electrode 50 is used in combination with the containers 16 and 26 having the openings 16h and 26h formed in the outer peripheral walls 16s and 26s or the upper walls 16u and 26u, and is accommodated in the containers 16 and 26 in a state where the extension 51b is drawn out from the openings 16h and 26 h.

The connection from the power supply 30 to the power supply lines 31 and 32 can be performed by using a connector such as an alligator clip attached to the leading ends of the power supply lines 31 and 32 in the extended portion 51 b.

In the case of an iontophoresis device in which members having high water content, such as the electrolyte solution holders 12, 22 and the drug solution holder 14, are accommodated, like the working-side electrode structures 10A to 10E and the non-working electrode structure 20D, by providing the water-repellent portions 51c on the extended portions 51b positioned in the openings 16h, 26h, the water-repellent portions 51c are impregnated with a fluorine-based resin, a silicone-based resin, a silane-based resin, or the like to impart water repellency thereto, or by using a metallic member as a connector such as the alligator clip, metal ions eluted from the member can be prevented from entering the working-side electrode structure and the non-working electrode structure.

The substrates 41 and 51 of the electrodes 40 and 50 may be formed of carbon fiber paper, and the same effects as described above may be obtained, and a soft polymer such as silicone rubber or thermoplastic polyurethane may be impregnated into the carbon fibers or the carbon fiber paper of the substrates 41 and 51, thereby preventing the quality of the electrodes from being deteriorated due to the falling of the carbon fibers and improving the operability of the electrodes 40 and 50.

The present invention has been described above based on several embodiments, but the present invention is not limited to these embodiments and can be variously modified within the scope of the claims.

For example, specific shapes and dimensions of the electrode structures, electrodes, and the like shown in the embodiments are merely examples, and the present invention is not limited to the shapes, dimensions, and the like shown in the embodiments.

In the above-described embodiments, the case where the doped layer is formed on the conductive substrate is used as the electrode, but the substrate does not necessarily have to be conductive, and the electrode may be formed only by the doped layer without using the substrate.

In addition, while any 1 or more of the action-side electrode structures 10A to 10K and any 1 or more of the non-action-side electrode structures 20A to 20D may be combined to constitute the iontophoresis device of the present invention, any 1 or more of the action-side electrode structures 10A to 10K and the non-action-side electrode structures 120 and 210 shown in fig. 10 and 11, or any 1 or more of the non-action-side electrode structures 20A to 20D and the action-side electrode structures 110 and 210 shown in fig. 10 and 11 may be combined to constitute the iontophoresis device of the present invention.

Alternatively, any 1 of the active-side electrode structures 10A to 10K may be used, and on the other hand, the iontophoresis device itself may not be provided with an inactive-side electrode structure, and for example, in the case where the active-side electrode structure is brought into contact with the skin of a living body and a voltage is applied to the active-side electrode structure in a state where a part of the living body is brought into contact with a member that is grounded, and the administration of the drug is performed, the basic effect of the present invention of suppressing the generation of oxygen, hydrogen, chlorine, or the like, or the generation of hydrogen ions, hydroxide ions, and hypochlorous acid in the active-side electrode structure at the time of energization is also achieved, and such an iontophoresis device is included in the scope of the present invention.

In the above-described embodiment, the case where the operation-side electrode structure, the non-operation-side electrode structure, and the power supply are each configured as an independent unit has been described, but an iontophoresis device in which these elements are incorporated into a separate case or the entire device assembled from them is formed into a sheet or a patch to improve the operability thereof is also included in the scope of the present invention.

Claims

1. An iontophoresis device characterized by having at least one electrode structure body having an electrode formed with a doped layer formed of a substance that generates an electrochemical reaction by doping or dedoping ions.

2. The iontophoresis device of claim 1, wherein the doped layer comprises a conductive polymer.

3. The iontophoresis device of claim 2, wherein the conductive polymer is polyaniline, polypyrrole, polythiophene, or polyacetylene, or a derivative thereof, or a mixture thereof.

4. The iontophoresis device according to any one of claims 1 to 3, wherein the electrode structure further comprises a chemical solution holding portion which is disposed on a front surface side of the doped layer and holds a chemical solution containing a 1 st conductivity type chemical ion.

5. The iontophoresis device according to claim 4, wherein the electrode structure further comprises a 1 st ion exchange membrane of the 1 st conductivity type disposed on a front surface side of the chemical solution holding portion.

6. The iontophoresis device of claim 4 or 5,

the electrode structure further comprises a 2 nd ion exchange membrane of the 2 nd conductivity type disposed on the front surface side of the doped layer,

the chemical liquid retaining part is disposed on the front side of the 2 nd ion exchange membrane.

7. The iontophoresis device according to any one of claims 1 to 3,

the electrode structure further includes:

an electrolyte retaining part which is arranged on the front side of the doped layer and retains electrolyte; and

and a 1 st ion exchange membrane of the 1 st conductivity type, which is disposed on the front surface side of the electrolyte retaining part and doped with the 1 st conductivity type chemical ions.

8. The iontophoresis device of claim 7,

the electrode structure further comprises a 2 nd ion exchange membrane of the 2 nd conductivity type disposed on the front surface side of the electrolyte retaining part,

the 1 st ion exchange membrane is disposed on the front side of the 2 nd ion exchange membrane.

9. The iontophoresis device of claim 7,

the electrolyte retaining part is disposed on the front side of the 2 nd ion exchange membrane.

10. The iontophoresis device according to any one of claims 1 to 3,

the electrode structure further comprises a 1 st ion exchange membrane of the 1 st conductivity type, which is disposed on the front side of the doped layer and doped with the 1 st conductivity type chemical ions,

the doped layer is doped with ions of the 1 st conductivity type.

11. The iontophoresis device of claim 10,

12. The iontophoresis device according to any one of claims 1 to 3, wherein the doped layer is doped with drug ions of the 1 st conductivity type.

13. The iontophoresis device according to any one of claims 1 to 3,

the electrode structure further includes a 1 st ion exchange membrane of the 1 st conductivity type disposed on the front surface side of the doped layer.

14. An iontophoresis device, comprising:

the inactive-side electrode structure has an electrode formed with a doped layer formed of a substance that generates an electrochemical reaction by ion doping or dedoping.

15. The iontophoresis device according to claim 14, wherein the non-active-side electrode structure further comprises a 1 st conductivity type 3 rd ion exchange membrane disposed on a front surface side of the doped layer.

16. The iontophoresis device according to claim 14, wherein the non-active-side electrode structure further comprises a 3 nd ion exchange membrane of a 2 nd conductivity type disposed on a front surface side of the doped layer,

the doped layer is doped with ions of the 2 nd conductivity type.

17. The iontophoresis device of any one of claims 1 to 16,

the electrode further comprises a conductive base material,

the doped layer is laminated on the conductive substrate.

18. The iontophoresis device of claim 17, wherein the conductive substrate is a conductive sheet formed of carbon fibers or carbon fiber paper.

19. The iontophoresis device of claim 18,

the electrode further includes a terminal member in which carbon is mixed into the polymer base, and the terminal member is attached to the conductive sheet.

20. The iontophoresis device of claim 18, wherein the electrode further comprises an extension portion formed integrally with the conductive sheet and formed of carbon fiber or carbon fiber paper.