JPH02241464A - Device for iontophoresis - Google Patents

Abstract

PURPOSE:To enable promotion of absorption of an ionic drug through a skin by providing a power supply unit, and a depolarizing means to depolarize polarization of an organism to be stimulated after electric energy accumulated in an accumulating means is discharged. CONSTITUTION:When disconnection and connection are effected by switching a transistor 2 by means of an output pulse PA from a signal processor 1, an inductor 3 generates a counter electromotive force, and a voltage is fed to a capacitor 5 through a diode 4 for accumulation. When an output pulse PB from the signal processor 1 is converted from an 'L' level to a 'H' level, a transistor 6 is turned OFF and 7 is turned ON. In this case, a polarizing charge generated when electric energy of the capacitor 5 is applied on a human body load RZ flows through the transistor 7 to perform depolarization. Lamination is made so that a conductor 31 is brought into contact with the position, desired to be medically treated, of a human body. Simultaneously, a closed circuit is formed with the conductor 31 and a non-conductor 32, and oscillation of a pulse is started to promote penetration of an ionic drug in ionic drug- contained porous ceramics 33 of the conductor 31 through a skin.

Description

[Detailed description of the invention] The present invention relates to a device for iontophoresis.

Iontophoresis has recently attracted increasing attention as an effective local administration method for promoting transdermal absorption of ionic drugs (Glass James et al. 9. International Journal of Dermatology 4 (Glass James et al.
JM et al, IntJ, Dera
atol, ) 19 519 (1980; Russo J. 0. American Journal of Hospital Pharmacy (Russo J., Am.

J, Ho5p, Phars, ) 37 843 (1980
); Gangarosa L. p. et al. 0. Journal Obfu 1
- Macological Experiment and Therapy (Gangarosa L P et al.
, J.

Pharmacol, Exp, Ther,)2
1 2 3 7 7 (1980), Kwampies et al. Journal of Infections
Decies (Kvon BS et al, J
, Infect, Dis,) 140 1014 (
1979), Hill JM et al. Annual of the New York Academy of Sciences (Hi
ll JM et al., Ann.

NY, Acad, Sci.) 284 604 (19
77) and Tannebaum M1. Physical therapy (Tannebaum M., Phys.
her,) 60792 (1980), etc.).

The iontophoresis in these prior art is usually
An output terminal of a continuous plain generator or an intermittent plain generator;
Because it is made by connecting a conductor such as a metal plate or the like with a conductor such as a metal plate with absorbent cotton impregnated with a chemical solution, and a similar conductor, it is quite complicated to implement, and is extremely difficult to administer. Despite its lack of effectiveness, its spread had to be limited.

Iontophoresis is disclosed in Japanese Patent Application Laid-open No. 156475 of 1988, Japanese Patent Application Publication No. 188176 of 1988, and Japanese Patent Application Publication No. 31 of 1988.
The above-mentioned problems have been overcome by techniques shown in publications such as No. 169.

Practical use of iontophoretic lasers means practical application of simple drug administration, and by providing an electrical control system, it also means that desired drug solution administration can be realized over a long period of time.

In particular, if it is portable, the scope of its use will be dramatically expanded, as it will become possible to administer medication in daily life.

However, no device has yet been proposed that is compact enough for portability and has sufficient electrical power.

SUMMARY OF THE INVENTION An object of the present invention is to provide a small and lightweight iontophoresis device, particularly an iontophoresis device that is extremely easy to operate and has a lightweight structure that can be directly attached to human skin.

By providing two circuits, a booster circuit and a storage circuit, the present invention makes it possible to store this energy several times to form enough energy for iontophoresis, even if the energy that can be taken out at one time is minute from a small battery. It is. Another major feature is that these booster circuits and storage circuits can be controlled by the pulse interval and pulse width output by the signal processor.

Hereinafter, circuits in embodiments of the present invention will be explained in detail with reference to the drawings.

In Fig. 1, (1) is a signal processor, and the signal processor (1) is a device that outputs variable pulse width and pulse interval, such as a microcomputer, gate array, etc., and is a device that outputs variable pulse width and pulse interval, such as a memory, etc. It is equipped with a storage means that allows input of information, or a fixed storage means. The signal processor (1) outputs pulses according to the algorithm stored in this storage means.

The output pulse (PA) of the signal processor (1) is supplied to the transistor A (2), which performs switching.

Further, the output pulse (PB) of the signal processor (1) is supplied to the transistor B (6) and the transistor C (7), and the transistor B (6) and the transistor C (7) perform switching.

The inductor (3) has one end connected to the power supply voltage +V (V), and the other end connected to the collector of the transistor (2).

A diode (4) is connected to the collector of the transistor (2).
The anode of the diode (4) is connected to the cathode of the diode (4), the other end of which is grounded, and the emitter of the transistor (6).

The collector of the transistor (6) and the collector of the transistor (7) are connected, and the output end (a) is connected through this connection.

The emitter of the transistor (7) is connected to the output terminal (b) and grounded.

The operation shown in FIG. 1 will be explained with reference to FIG. 2.

Output pulse (PA) of signal processor (1) (Fig. 2 (a)
) causes the transistor (2) to perform switching. When the transistor (2) disconnects and connects, the inductor (3) generates a back electromotive force, and a voltage several tens of times higher than the power supply voltage is applied to the capacitor (5) via the diode (4).
). Capacitor (5) performs storage.

The output pulse (PB) of the signal processor (1) is shown in Fig. 2 (C
) is supplied to transistor B (6) and transistor C (7). Transistor B is shown in Figure 2 (
It turns on when the pulse shown in C) is at the "L" (LOW) level. Conversely, transistor C(7) is turned off. At this time, the electrical energy stored in the capacitor (5) (FIG. 2(b)) is applied to the human body load (RZ) connected between the output terminal (a) and the output terminal (c).

The pulse shown in FIG. 2(C) changes from "L" level to "11" level.
'' (IIICll) level, the transistor (6) is turned off and the transistor C (7) is turned on.

At this time, the polarized charge generated when the electrical energy of the capacitor (5) is applied to the human body load (RZ) flows through the transistor C (7) and is depolarized.

Collector of transistor (36) and transistor (38)
) and the collector of the transistor (36) is also connected to the output terminal (a).

The cathode of the diode (34) is connected to the other end of a capacitor (35) whose one end is grounded, and to the transistor (39).
is connected to the emitter of

Collector of transistor (39) and transistor (37)
) are connected, and the collector of the transistor (39) is also connected to the output terminal (b).

The base of the transistor (36) is the transistor (37)
is connected to the collector of the transistor (39
) is connected to the collector of the transistor (38) via a resistor.

Next, another embodiment of the present invention will be described in detail with reference to FIGS. 3 and 4.

The signal processor (1) has the same structure as in FIG. The output pulse (PA) of the signal processor (1) is transmitted through the transistor A (
2), and transistor A(2) performs switching.

Further, the output pulse (PB) of the signal processor (1) is supplied to the transistor (37), and the transistor (37) and the transistor (36) perform switching.

The output pulse (PB'') of the signal processor (1) is supplied to the transistor (38), and the transistor (38) and the transistor (39) perform switching.

The inductor (3) has one end connected to the power supply voltage (V) and the other end connected to the collector of the transistor (2).

A diode (4) is connected to the collector of the transistor (2).
and the anode of the diode (34) are connected.

The cathode of the diode (4) is connected to the emitter of the transistor (36) and the other end of the capacitor whose one end is grounded.

Explain the operation.

In the figure, the output pulse (PA) (Fig. 4 (1)) of the signal processor (1) causes the transistor (2) to perform a switching operation, and when the transistor (2) turns on and off. , the excitation current of the inductor (3) is interrupted or connected, and the back electromotive force generated at the time of this interruption or connection is
It is supplied to a capacitor (5) and a capacitor (35) via a diode (4) and a diode (34), and is stored therein. Charging waveform of capacitor (5) (Fig. 4 (2))
, the charging waveform of the capacitor (35) (Fig. 4 (3)), the output pulse (P B ) of the signal processor (violet) (Fig. 4 (5)
)) causes the transistor (37) to perform a switching operation, and when the transistor (37) turns on, the output terminal (b) becomes a negative electrode and at the same time the transistor (
36) is turned on, the output terminal (a) becomes the positive electrode, and the electrical energy stored in the capacitor (5) is transferred to the human body load (
RZ).

Output pulse (PB) of signal processor (1) (Figure 4 (4)
) falls, the signal processor (1) outputs a pulse (P
B') (Fig. 4 (5)) is output.

The pulse (PB') gives a switching operation to the transistor (38), and when the transistor (38) is turned on, the output terminal (a) becomes negative, and at the same time, the transistor (39)
) is turned on, the output terminal (b) becomes the positive electrode, and the electrical energy of the capacitor (35) is output to the human body load (RZ).

The output waveform diagram between output terminals (a) and (b) is shown in Figure 4 (6).
As shown in the figure, they form an alternating pattern.

In the embodiment shown in FIG. 3, depolarization is effected by applying alternating electrical energy to the human body load (RZ).

Next, another embodiment is shown in FIG.

(40) is a boosting means using a blocking oscillator. A description of the configuration in FIG. 5 has been omitted.

The excitation current of the step-up transformer (4I) changes exponentially by exponentially turning on and off the transistor (42), and the voltage is stepped up according to its turns ratio.

The transistor (42) is turned on and off by a resistor (44),
This is carried out autonomously by charging and discharging the capacitor (43) with a time constant.

Since the output of the step-up transformer (41) is an exponential alternating wave, the positive side is accumulated in the capacitor (5) via the diode (4). The negative electrode side is stored in a capacitor (5) via a diode (4°).

The output pulse (PB) of signal processing B(1) provides switching operation to transistor (6) and transistor (7). The output pulse (PB) is output in the shape shown in FIG. 2(C).

As shown in FIG. 2(C), when the pulse (PB) is at the "L" level, the transistor (6) is turned on and the transistor (6) is turned on.
7) is turned off.

When the transistor (6) is turned on, the stored electrical energy of the capacitor (5) is applied to the human body load (RZ) via the output terminals (a) and (b).

When the pulse (FB) is at the “■1” level, the transistor (
6) is turned off and transistor (7) is turned on.

When the transistor (7) is turned on, the polarized charge of the human body load (RZ) is depolarized via the transistor (7).

Next, FIG. 6 will be explained.

The output terminal (PA) of the signal processor (1) is a transistor (
The other end of the transistor (2) was connected to the base of the transistor (2), and the power supply voltage was supplied to the collector of the transistor (2). Inductor (3
); The emitter of the transistor (2) is grounded. The collector of the transistor (2) is connected to the anode of the diode (4).

The cathode of the diode (4) is connected to the output end (a) and one end of the resistor (51), and the other end of the resistor (51) is connected to the output end (b) and is grounded.

The operation shown in FIG. 5 will be explained.

The output pulse (PA) of the signal processor (1) causes the transistor (2) to perform a switching operation, and this switching operation causes the transistor (2) to intermittent the excitation current flowing to the inductor (3). The back electromotive force generated during this intermittent period is transmitted to the output terminal (
Output between a) and (b). Since the diode (4) is forward-connected, a back electromotive force in the positive direction (unipolar) is output between the output terminals (a) and (b).

As for the signal processor, as mentioned above, it refers to a microcomputer, a gate array, a custom IC, a semi-custom IC, etc., but it may be any type as long as it outputs pulses.

For example, by installing multiple self-propelled multivibrators,
It is also possible to adopt a configuration in which this is selected by a selector and the pulse width and interval are changed. In addition to the structure shown in the above embodiment 1.2 in which the excitation current of the inductor is intermittent to perform high voltage conversion, if relatively low voltage conversion is to be performed, the above embodiment 3 is used.
This can be done by boosting the turns ratio using a transformer-like inductor, as in the blocking oscillator shown in . Further, the boosting means and the like are not limited to a specific circuit, but may be configured as appropriate.

Next, an example of the overall configuration of the iontophoresis device of the present invention will be described in detail below.

7 and 8 show a first embodiment. In the figure (
30) is an iontophoresis device configured in the form of a plaster that can be attached to the skin, and Deiko Seki (31)
and an insensitivity conductor (32). Said Doiko Seki (31
) is an ionic drug-containing porous ceramic (33) formed into a flexible sheet or film, and a metal foil such as aluminum foil.

A conductive member layer for current dispersion (34
) are integrally formed by laminating them. Further, the indifferent conductor (32) includes a conductive gel layer (35) formed in the form of a flexible sheet or film, and a current dispersion conductive member layer (36) formed of aluminum foil or the like as described above. It is integrally formed by laminating layers. Said Doiko Seki (31
) The power supply unit (37) is located in the center of the upper enclosure.
is installed. This power supply unit (37
) is equipped with a power source, for example, a so-called button-shaped battery, a pulse oscillation mechanism, and means for depolarizing both the conductors (31) and (32) when the treatment pulse of this pulse oscillation mechanism is stopped. One of the output terminals, for example, the (-) terminal, is installed so as to be in contact with the current dispersion conductive member layer (34).

Further, the (+) terminal of this power supply unit (37) is connected to a conductive wire (38) made of aluminum foil, for example, whose lower surface except near both ends is coated with an insulating coating, for distributing the current of the indifferent conductor (32). It is connected to the member layer (36). (39) is an insulating backing layer.

This insulating backing layer (39) is made of, for example, a non-conductive synthetic resin in the form of a flexible sheet or film.
The gate conductor (31) and the gate conductor (32) are spaced apart and fixed to the insulating backing layer (39).

That is, the insulating backing layer (3
9) are integrally supported and connected.

Next, the operation and usage of the iontophoresis device constructed as described above will be explained. First, the guide element (31) is attached so as to be in contact with the desired treatment position on the human body. At the same time, the Seki inductor (31) and the Inkan inductor (32) form a closed circuit, pulse oscillation is started, and the ionic drug-containing porous ceramic (33) of the Seki inductor (31) is activated. Transdermal penetration of ionic drugs is promoted.

According to this example, an iontophoresis device can be obtained which is extremely easy to operate and lightweight, and which can be directly attached to the human skin, and which can provide a sufficient drug administration effect.

Next, with reference to FIGS. 9 and 10, a second embodiment in which the iontophoresis device of the present invention is configured to be integrally attached to the skin, that is, in the form of a plaster, will be described in detail. In the figure, (40) is a device for iontophoresis, (41) is a separator, and (42) is a separator. The electrically conductive material layers (43) and (44) for current dispersion of the conductor (41) and the conductor (42) are arranged at a distance of about 5 mm, and the lower surface thereof has a distance of about 0.3 mm. An extremely thin conductive gel layer (45) containing an ionic drug is attached to the body. Furthermore, the non-conductor (42) and the subconductor (43) are integrally supported and connected by an insulating backing layer (46). (47) and (48) are terminals connected to the inductor (41) and inductor (42), respectively. The tops of these terminals (47), (48) protrude through the insulating backing layer (46), and the power supply unit (49) is connected to these terminals (47), (4g
) are electrically connected and mechanically supported and connected.

The method of using the iontophoresis device of this example is the same as that of the first example, so the description thereof will be omitted. According to this embodiment, the conductive gel layers laminated on the Seki conductor (41) and the Seki conductor (42) are the same, that is, one ionic drug-containing conductive gel layer (45) is used to conduct each current dispersion conductor. Sex member layer (4
3) and (44), a slight leakage current occurs between each conductor, but the conductive gel layer itself has resistance and the conductive member layers (43) and (42) Since the distance between them is extremely large compared to the thickness of the conductive gel layer (45), it hardly affects the skin permeation effect of the ionic drug.

According to this embodiment, the manufacturing process becomes extremely simple and efficient. In other words, a device can be obtained by simply attaching terminals and a power supply to a single strip-shaped sheet in which a conductive gel layer, a conductive material layer, and an insulating backing layer are laminated and cut at predetermined intervals, making it suitable for mass production. It has a very useful effect in such cases. Furthermore, if the spacing between both terminals is narrowed and the power supply is placed approximately in the center of the top surface of the device as in the example, the size of the power supply has almost no effect on the entire device, and it can be attached to the curved surface of the human body. It can be used satisfactorily with almost no loss in flexibility even when

Next, a third embodiment of the iontophoresis device of the present invention will be described in detail with reference to FIG. 11 of the drawings. In the figure, (51) is an iontophoresis device; (5
2) indicates an indifferent conductor. (54) is the power supply,
Its (-) terminal is connected to the current dispersion conductive material layer (55) of the Seki conductor (52), and its (+) terminal is connected to the lead wire (
56) to the current dispersion conductive member layer (57) of the indifferent conductor (53).

According to the configuration of this embodiment, the guan conductor and the guan conductor can be attached to the human body at any distance within the length of the lead wire, and when the attachment site is small or has a relatively large curvature. It can also be used without difficulty. Furthermore, even when the skin sweats profusely due to use in hot and humid conditions, a plaster structure can be obtained that is completely unaffected by the current flowing through the epidermis because the conductors are separated from each other.

Next, a fourth embodiment of the iontophoresis device of the present invention will be described in detail with reference to FIG. 12 of the drawings. In the figure, (61) is an iontophoresis device, and (62) is a device for iontophoresis.
) indicates its seki conductor, and (63) indicates its disjunction conductor. Both conductors (62) and (63) are connected to a power supply (65) via a lead wire (64). This power supply (65) includes a power source such as two AA batteries, a pulse oscillation mechanism using a transformer, and a switch such as a switch for depolarizing both conductors (62) and (63) when the treatment pulse is paused. A mechanism is installed internally. Furthermore, this power supply (65) includes an output current variable circuit and a timer circuit.

According to this embodiment, since the power supply is separate from both conductors, the circuit space can be increased and a large capacity dry cell battery can be used. Furthermore, since both conductors are simply film-like ultra-light sheets, it is extremely easy to attach them to the human body. Furthermore, since a variable output current circuit is installed, the amount of output current can be controlled arbitrarily depending on the skin resistance of the user, the type of drug to be introduced, the required amount, etc. Furthermore, since a timer circuit is provided, it has the advantage of being able to prevent excessive administration of drugs.

In the above embodiments, conductive gel containing an ionic agent or porous ceramics was used for the conductor, but the present invention is not limited to this, and paper materials such as water supply paper were used. , cloth materials such as gauze, fiber materials such as absorbent cotton, sponges or porous materials such as open synthetic resin foams or water-absorbing resins, etc., as long as they can be impregnated with and retain ionic drugs or electrolyte solutions. good. In addition, in the examples, the conductive gel layer of the conductor was described as containing an ionic drug in advance, but the ionic drug was applied to the conductor and/or the skin during use. Also good. That is, a conductive gel layer that does not contain an ionic drug is used, and at the start of treatment, an ointment, cream, etc. containing an ionic drug is applied to the conductor and/or the skin to form a film. It may also be an iontophoresis device to which a conductor is attached for treatment. Furthermore, a polarity switching means may be added to the device so that the yin and yang of the conductor can be freely changed depending on the yin and yang of the effective drug ion species.

In addition, especially when the biological condition changes depending on the drug dose, or when the drug dose must be controlled according to the biological condition, the output current can be automatically adjusted while monitoring the biological condition. It may also be configured such that it has an internal feedback mechanism for controlling. for example,
Especially when it is necessary to control the dose based on the blood sugar level, such as when administering insulin, a sensor that monitors the blood sugar level is connected to the power supply, and the output current is automatically adjusted based on the sensor's detection output. And/or a feedback mechanism for controlling the output time and the like may be provided. With this configuration, it is possible to perform optimal drug administration according to the biological condition, which was impossible with conventional administration methods.

A more detailed breakdown of each component of the plaster structure of this example is as follows.

Conductive gel layer This layer is preferably made of a natural resin polysaccharide such as karaya gum, tragacanth gum, or xanthan gum, or a partially saponified polyvinyl alcohol, a vinyl resin such as polyvinyl formal, polyvinyl methyl ether and its cobolima, polyvinylpyrrolidone 5 polyvinyl methacrylate, etc. Various hydrophilic natural or synthetic resins such as polyacrylic acid and its sodium salt, polyacrylamide and its partially hydrolyzed products, partially saponified polyacrylic esters, and acrylic resins such as poly(acrylic acid acrylamide) are mixed with water. And/or it can be softened and plasticized with alcohols such as ethylene glycol and glycerin to provide a flexible film or sheet gel having self-shape retention and skin adhesive properties.

On the other hand, an electrolyte such as sodium chloride, sodium carbonate, potassium citrate, etc. is added in a required amount (usually about 1 to !5%) in order to impart sufficient conductivity to this. The conductive gel layer suitable for the present invention obtained in this way is in the form of a flexible film or sheet and can adhere closely to the skin, so it has low skin contact resistance and is effective for transdermal penetration of drug ions. Not only that, but it also has the advantage of being able to adhere and support the entire structure to the skin without requiring other skin adhesion means such as adhesive tape. In particular, when a natural resin polysaccharide such as the aforementioned Karaya gum is used as a base material for the gel layer, its natural polymeric acid structure provides pH buffering and skin protection properties, extremely high water retention capacity, moderate skin adhesion, etc. Not only can a gel with good electrochemical conductivity be provided, but also suitable skin compatibility can be obtained.

In addition, when formulating the composition of these gel layers, it goes without saying that electrochemical considerations should be made in the same way as in the case of so-called electrophoresis gels, but the main consideration is the type of drug used and the required dose (dose). ), the duration of use of the adhesive, the output of the battery used, the skin contact area, etc., are carried out as appropriate so that the ion mobility or electrical conductivity reaches the required value.

Here, in addition to the preferred conductive gel layer in this example, some more specific details are as follows: 1. By a conventional method, the average molecular weight is 440,000, and the degree of saponification is 60%.
Prepare 30 g of polyvinyl alcohol powder, and add 40 g of distilled water containing 10% NaCl preheated to 80°C.
and 30 g of glycerin were added and stirred, and then the resulting mixture was heated and pressed at a pressure of 0.6 kg/cm for about 20 minutes using a hot press heated to 80°C to form a flexible sheet with a thickness of 3 cm. This flexible sheet-like material had sufficient skin adhesion and its direct current resistivity (hereinafter the same) was 0.8 Ωcm〇2.The following composition was obtained in the same manner as in 1 above. A flexible sheet-like conductive gel layer was manufactured using the following method.

(Composition Example A) Polyvinylpyrrolidone (PVP-90 manufactured by G AF)
; average molecular weight 360,000)・・20g10%NaC1
Distilled water: 40 g Glycerin: 40 g The obtained sheet had strong skin adhesion and its specific resistance was 0.2 Ω·cm.

(Composition example B) Polyvinyl formal (average molecular weight 1.6 million.

Degree of formalization: 15%; Degree of saponification of raw material polyvinyl alcohol: 60%) 15g Distilled water containing 5% NaCl・・・70g Propylene glycol・
The 15g sheet obtained has sufficient skin adhesion and its specific resistance is 1. It was OK Ω・cm.

(Composition Example C) Polyvinyl acetoacetal (average molecular weight 440,000, degree of acetalization 30%; degree of saponification of starting polyvinyl alcohol 70%)・40g Distilled water containing 15% Na1--5
0g ethylene glycol・IOg Has sufficient skin adhesion and has a specific resistance of 0.75 Ω fist
0 3, Sodium polyacrylate (Aronbis S manufactured by Nippon Pure Chemical Industries, Ltd.)
S, average molecular weight 3-5 million) 20g with 5%N
The mixture was uniformly mixed with 12 g of aC1-containing distilled water and 68 g of a glycerin solution, and heated and pressed at 80° C. for 10 minutes to obtain a flexible sheet. This sheet had appropriate skin adhesion and its specific resistance was 0.5 Ω·cm after being left for day and night.

4. 30g of karaya gum and 30g of distilled water containing 5% NaCl
and 40 g of glycerin were mixed and heated and pressed to prepare a sheet in the same manner. Specific resistance 065, Ω-cmo 5, sodium polyacrylate (Aronbis S manufactured by Nippon Pure Chemical Industries, Ltd.)
; average molecular weight 3-5 million) 20g with 7% NaC
A sheet was prepared in the same manner by mixing with 80 g of purified water containing 1 and heating and pressurizing the mixture. Specific resistance is 0.47 and Ω・Cl10 Furthermore, especially from an electrochemical point of view, basic drugs such as propranolol, insulin, lidocaine, cysteine, etc. , F, made by GANTREZ
AN-169, etc.), carboxypolyethylene (GOO
Acidic polymers such as DR [CARBOPOL manufactured by CH Corporation, etc.], ascorbic acid, salicylic acid, nitrous acid, riboflavin phosphate, betamethacin phosphate, tretinoin (
It will be appreciated that highly efficient transfer of target drugs can be achieved by using basic polymers such as polyacrylamide as gel bases for acidic drugs such as trans-retinoicacid.

For example, an example of the gel composition for propranolol is AN-16.
930 parts by weight glycerin 45 parts by weight water
15 parts by weight propranolol
10 parts by weight of this gel composition.
A self-adhesive film with a thickness of about 5 mm is extremely suitable for use as a film electrode integrated with a Seki conductor and a Seki conductor as described above.

Furthermore, it will be appreciated that non-ionic polymers such as polyvinyl alcohol, polyvinylpyrrolidone, etc. may also provide gels with relatively high electrochemical efficiency.

As is clear from the above, the gel base material composition or range of the conductive gel layer of the present invention is not limited to a specific one, and a wide range of hydrophilic polymers can be softened and plasticized with water and/or alcohols. However, in order to have shape retention, the composition is usually selected within the range of 10 to 70% by weight of the hydrophilic polymer and the balance water and/or alcohol. Each of the above-mentioned conductive gel layers has sufficient skin adhesion by itself, but if desired, a pressure-sensitive adhesive component such as an acrylic adhesive or a vinyl acetate emulsion adhesive may be added. It's okay.

In this way, by placing a skin-adhesive and conductive gel layer around the periphery or edge of the structure, the entire structure can be attached to the skin without the need for any other fixing means such as adhesive tape. It is held fixed.

In addition, when the conductive gel layer is the husband of Seki Seki, it is sufficient to add and dissolve the required ionic drug in place of part or all of the electrolyte component, that is, sodium chloride, in each of the above gel compositions. It is.

If necessary, the water-retaining member layer may be made removable, and the member impregnated with a chemical solution may be placed at a predetermined position in the structure during use and used for treatment. Also, instead of the water-absorbing material, agar gel,
It is clear that non-adhesive hydrogels commonly used in the field of electrophoresis, such as gelatin gels, may also be used. An example of an agar water gel composition is as follows.

Agar powder 4.0 parts by weight Purified water
100.0 〃Vitamin C5,0// (ascorbic acid; its Na salt ~l:l) This kind of hydrogel pieces may be stacked and arranged in a structure in advance,
Alternatively, it may be arranged during use as described above.

In addition, when using a non-adhesive hydrogel such as agar gel in this way, it is natural that skin-adhesive fixing means such as adhesive tape may be optionally added to the outer extension of the structure in this example. It is.

Any ionic drug or ion dissociative drug can be used, but some examples of those already widely used in the field of iontophoresis are as follows: iodopotassium, prohydroline hydrochloride, and melicol.

Vitamin Bl+ Various skin vitamins such as Bt, Bs, C, histamine, sodium salicylate, dexamethacin, betamethacin phosphate, epinepherin, hydrocordisone, idoctulidine.

Propranolol, nitrites, pleomycin.

undecylene hydrochloride 9, etc.

Examples of use Examples and use examples of the Kan inductor and Inkan inductor of the device for iontophoresis of the present invention will be explained in more detail as follows.

That is, the conductive gel layers of both parts are made of injected carbo balls.
491 20% by weight, 30% by weight of distilled water and 40% by weight of glycerin, thickness 1.5 am, area 48c+
a'' viscoelastic gel, and the ionic drug-containing conductive gel layer of the Kando conductor has 5% by weight of sodium salicylate added thereto, and the conductive gel layer of the Kankan conductor has about 3% by weight of sodium salicylate added to it. Sodium chloride is added.

This is used by integrally laminating and pasting a power supply that outputs 4KHz pulses connected to a 3V button battery power source.

The plaster structure in this usage example is used as an analgesic and anti-inflammatory agent, but in this case, it is used as a so-called galvanization therapy, which has a vasodilatory effect.
n) will be combined, so neuralgia, joint pain,
It will be understood that it shows a synergistic effect on diseases such as rheumatoid arthritis.

It is also clear that this type of plaster structure is useful for purposes such as the treatment of various skin diseases and the penetration of cosmetic nutrients. For example, the conductive gel layer of both conductors is
ANTREZ AN-16920% by weight, 20%Na
15% by weight of C1-containing distilled water and 65% by weight of glycerin
It is made of a viscoelastic gel that has skin adhesive properties and has a thickness of 1.51all and an area of about 12cm, and when used, an aqueous solution containing 3% vitamin C (stored in ampoules) is applied to the conductive gel layer of the seki conductor. Drop and impregnate ~11 g of the structure, then apply the entire structure to the affected area and begin the treatment.

As is well known, vitamin C (ascorbic acid) and its derivatives (sodium ascorbate, etc.) are effective for pigmentation disorders such as melasma, melasma, and various melasma.
Treatments using iontophoresis are already known to be useful in the field of beauty and dermatology, but as mentioned above, they are not widely used due to the complicated operation. However, this example allows the treatment to be performed with extremely simple operations, and can be said to be revolutionary as a therapeutic or cosmetic plaster.

Other Gel Base Materials Some preferred examples of gel base materials for the conductive gel layer of the present invention are as described above, but various hydrophilic polymer materials known as so-called biological electrode materials may also be selected at will. It is once again pointed out that it can be used. For example, Japanese Patent Publication No. 95895 of 1972.

No. 77489, 1954.

No. 52742, 1955.

No. 81635, 1955.

No. 129035, 1955.

No. 15728, 1956.

1956 36939 No. 8 No. 36940, 1956.

No. 60534 of 1956.

No. 89270, 1956.

No. 143141, 1956.

No. 28505 of 1957.

No. 49431, 1957.

No. 52463 of 1957.

No. 55132 of 1957.

1957 No. 31428.

1957 No. 60439.

1957 No. 64064.

1957 No. 66142.

168675, 1957 No. 4569, 1957.

10066, 1958 Utility Model No. 80689, 1972.

No. 135706, 1956.

No. 138603, 1956.

No. 93305, 1957.

No. 179413, 1957.

No. 185309, 1957.

The various hydrophilic polymer materials disclosed in the above can be used as the gel base material of the conductive gel layer of the present invention by appropriately adjusting the water content and the like.

As described above, the gel base material of the conductive gel layer of the present invention is a hydrophilic polymer which is softened and plasticized with water and/or alcohols to preferably provide a skin-adhesive viscoelastic gel. However, the base material composition is not limited to a specific material, and the composition of the base material is determined in consideration of compatibility with the drug used, skin compatibility, electrical conductivity, etc. Furthermore, these gel layers can be disposable or replaced with other materials.

Porous ceramic layer refers to all porous materials produced in the ceramic industry, such as porous alumina and unglazed ceramics.

The average pore diameter in the porous structure is generally several hundred μl (e.g. 0.4 μm ± 0.1), and the porosity is usually preferably about 30 to 90%, as shown above. It is not particularly limited, and is appropriately selected depending on the usage condition.

In addition to the fact that the conductive gel or porous ceramic layer described above is suitable for containing drugs,
As described in Japanese Patent No. 68248, a drug solution can be efficiently administered by electroosmotic effect.

Furthermore, a structure in which a reservoir is provided as described in Japanese Patent Application No. 25842.25843 of 1999 may also be adopted.

[Brief explanation of drawings]

1, 3, 5, and 6 are circuit diagrams showing embodiments of the present invention, FIG. 2 is an output waveform diagram showing each tapping operation in FIG. 1, and FIG. It is an output waveform diagram of each hitting motion of the figure. 7 and 8 show a first embodiment of the overall configuration of the iontophoresis device of the present invention, FIG. 7 is a cross-sectional view taken along the line ■-■, and FIG. 8 is a bottom view. FIG. 9 and FIG. 1θ show the second embodiment, FIG. 9 is a sectional view taken along the line XIV-XIV, and FIG. 1θ is a perspective view. 11 and 12 show the third and fourth embodiments, FIG. 11 is a sectional view thereof, and FIG. 12 is a perspective view thereof. (°1)... Signal processor, (2) Transistor A1 (3) Inductor, (4) Diode, (5) Capacitor, (6) Transistor B, (7) Transistor C1 (a), (b)... Output end, ((0), (40), (51), (61) - Device for iontophoresis, (31), (41), (52), (62 ) ・Douko Seki, (32), (42), (53), (63) ・・
Inkan conductor, (45) - Conductive gel layer containing ionic drug, (35) - Conductive gel layer, (37), (49), (54), (65), Power supply unit, (33 )・・Porous ceramic layer. Patent applicant Advance Co., Ltd. Figure 5 Figure 6

Claims (1)

[Claims] (1) a power supply unit having a boost pulse generating means for inputting electrical energy from a small power source as a boost pulse to the storage means; and an output means for outputting the electrical energy stored in the storage means; An iontophoresis device comprising a depolarizing means for depolarizing the stimulated living body after releasing electrical energy stored in the storage means.