JPH02243168A - Device for iontophoresis - Google Patents

Abstract

PURPOSE:To obtain a device for an iontophoresis, which is safe and without fears of burn, flush, etc., by installing a depolarization device consisting of a pulse oscillation mechanism of outputting pulse components in an inverse direction to therapeutic pulses for the sake of depolarizing a polarized potential between both electrodes at OFF-times of the therapeutic pulse voltages from the pulse oscillation mechanism. CONSTITUTION:A pulse oscillation mechanism 3 is so constructed as not only to output therapeutic pulse voltages 12, 12,... at 10,000Hz level for example, but also to output pulse voltage components 13, 13,... in an inverse direction to the former for the sake of depolarizing a polarized potential between both electrodes 4, 5 as soon as the therapeutic pulse voltages 12, 12,... are stopped. By these inverse pulse voltage components 13, 13,..., residual charged (polarization), which have been charged during ON-times of the therapeutic pulse voltages 12, 12,... at a part of skin S in contact with both electrodes 4, 5 of a human body 6, are forced to be discharged (depolarized) and currents flow through the skin of the human body 6 as soon as the therapeutic pulse voltages 12, 12,... are stopped. An ionic drug contained in the electrode 4 is percutaneously absorbed through a resistance part of the skin by these currents.

Description

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

Iontophoresis has recently received increasing attention as an effective topical administration method for promoting transdermal absorption of ionic drugs (Glas James et al., International Journal of Dermatology).
s JM et al. .

Ir+t. J, Dermatol. )l 9
5 1 9 (1 9 80); Nolesso G.I.
, American Journal of Hospital Pharmacy (Russ.

J. , Am. J. Hosp. Pharm. )
37 843 (1980); Gangarosa L.P. et al. , Journal of Pharmacological Experiments and Therapy (Gangarosa
LPet al. , J,' Pharma
col. F, xp. Ther. )212 377(
1980); Kwambies et al.6.

Journal of Infectious Diseases (K
won BS et al. , J. In
fect. Dis,) 140 1014 (19
79); Hill GM et al., Annual of
New York University of Science (Hill)
JM etal, Ann, NY, Acad
, Sci.) 284 604 (1977) and Tanfubaum M. 2. Physical therapy (Tanne
Baum M,, Phys.

Ther, ) 60 792 (1980), etc.).

The iontophoresis in these prior art is usually
An output terminal of a continuous plain generator or an intermittent flow generator;
It is quite complicated to implement because it is made by connecting a conductor such as a metal plate made of a conductor such as a metal plate with absorbent cotton impregnated with a chemical solution, and a similar structure, so it is quite complicated to implement, but it is extremely effective as a medication method. Despite its popularity, its spread had to be limited. In addition, this iontophoresis is used using continuous normal temperature or intermittent normal temperature that has the same polarity as the drug to be administered. Resistance (Rs)
have. This resistance (Rs) is extremely high when using sustained normal temperature, so in order to administer the amount of drug necessary for treatment, a high voltage must be applied to the skin. It was highly irritating and could cause burns, redness, etc. Furthermore, it has been extremely difficult to administer the required amount when using low voltage to prevent damage to the skin.

Furthermore, it is known that the resistance (Rs) of the skin (S) changes depending on the frequency of the applied power source.

((Shiraki et al., Mesocal and Biological Engineering and Computation (Ya
mamoto, at al,, Mad, &B
iol.

Eng, & Comput, Xi 978) 16
．． 592-594; Shiraki et al., Medical Electronics and Bioengineering (1971) Vol. 11 No. 5 337-342, )) The trajectory of this change is roughly as shown in FIG. 2. That is, in the figure, the vertical axis shows the resistance Rs [KΩ1] of the skin (S), and the horizontal axis shows the frequency [Hz] of the applied power source. As is clear from this figure, the skin resistance (Rs) has a characteristic that it decreases as the power frequency increases. Skin resistance (Rs) varies greatly from person to person, and changes with temporal oscillations and diurnal cycles, so it is difficult to display an absolute value. [K
When Ω is about 1, loO [HzJ is about 70 [KΩ].

Approximately 20 [KΩ] mallo at 1000 [Hzl], 00
At 0 [Hzl], it decreases to about 8 [KΩ]. When such high frequency power is applied to the human body, skin resistance (Rs
) decreases, making it possible to perform iontophoresis at low voltages, but the skin (S) is a parallel circuit with a resistor (Rs) and a capacitor (Cs) as shown in the skin equivalent circuit diagram in Figure 1. Since it is represented by a circuit, simply applying a DC pulse voltage as shown in Figure 3(a) will cause the capacitor (Cs
) repeats charging and discharging, and when the pulse output is stopped, the residual charge (polarization) is discharged (depolarization) very slowly through the resistor (Rs), as shown in Figure 3 (b). The current associated with drug introduction was essentially the same as when continuous normal temperature was used, and the skin resistance could not be reduced simply by applying a high frequency DC pulse voltage. In other words, the resistance (Rs) and capacitor (Cs) of the skin are usually about 501% each, although there are individual differences.
Ω] and O,l [μF]. Therefore, the time constant is O,lX10-'X100XIO3-1O-'', which is on the order of several m5ec.

This is several + wsec even though the current value decreases to about 1/3.
, and for this reason, a pulse of several hundred [H2] or more was substantially the same as the current waveform when using continuous normal temperature, and therefore no decrease in skin resistance could occur.

In addition, as shown in No. 31 El (c), the output time of the DC pulse voltage is shortened, and even if residual charge (polarization) occurs due to the capacitor (Cs), the interval of the pulse rest time is increased until the current value becomes sufficiently low. It is possible to lower the skin impedance by widening it, that is, by reducing the duty ratio, but this is problematic in terms of introduction efficiency because residual charge (polarization) is a charge that remains on the skin and is not involved in drug administration. It had a

The present invention solves the above-mentioned drawbacks, and can sufficiently reduce the skin resistance, thereby making it possible to use low voltage and high current, and as a result of depolarization, there is less irritation to the skin, causing burns and redness. The purpose of the present invention is to provide a safe device for iontophoresis that is free from such risks.

A further 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.

Hereinafter, a first embodiment of the present invention will be described in detail with reference to FIGS. 4 and 5 of the drawings.

In FIG. 4, (lO) is a device for iontophoresis shown in a block diagram. (2) is the power source, for example 6 [
(3) is the pulse oscillation mechanism. (4
) is a Guan inductor containing an ionic drug, and (5) is an inkan inductor. (6) is the above-mentioned Seki Deiko (4) and Inkan Deiko (
5) is a human body connected to The pulse oscillation mechanism (1
1) is, for example, 10.00 as shown in Figure 5(a).
Therapeutic pulse voltage (12), (12) on the order of 0 [Hzl]
(12), . . . and this treatment pulse voltage (12), (12).

When the pulse voltage component (1) is stopped, the pulse voltage component (1
3), (13), (+3), . . . This pulse voltage component in the opposite direction (13),
Treatment pulse voltage (12) of the skin (S) of the human body (6) with which both grooves (4) and (5) come into contact due to (13), .
The residual charge (polarization) charged during the output time of , (12), . . . is the therapeutic pulse voltage (12), (12).

・A forced discharge (depolarization) occurs at the same time as the human body (
6) The current shown in FIG. 5(b) flows through the skin (S). Due to this current, the ionic drug contained in the conductor (4) is absorbed through the skin through the skin resistance (Rs) shown in the skin equivalent circuit diagram of FIG.

For example, as in the example, if the power supply voltage is 6 [Vl, lo,
When a therapeutic pulse voltage of about ooo [Hzl] is applied to the human body (6), the human body (6) has 1O Several times the current flows.

In the above embodiment, a configuration was described in which the treatment pulse voltage and the forced discharge pulse voltage component are outputted by one pulse oscillation mechanism, but the configuration is not limited to this, and for example, each pulse may be oscillated independently. It may be configured such that the signal is output and applied to the human body by synchronizing both.

Furthermore, a mechanism may be provided to arbitrarily or automatically control the time and voltage of the forced discharge pulse component in order to depolarize between both conductors.

In addition, in the above embodiment, a configuration was described in which a pulse in the opposite direction is output in order to depolarize between both conductors, but it is not limited to this means, and a means having a similar effect may be provided. Any configuration may be used as long as it is possible.

Furthermore, the power supply voltage, the voltage waveform of the therapeutic pulse, the pulse width, the oscillation frequency, etc. may be arbitrarily changed depending on the characteristics and application of the drug to be introduced, but the duty ratio is usually 0.2 to 0.7. , repetition frequency IKHz ~ 200K
A value on the order of H2 may be adopted.

In other words, since the present invention only needs to be capable of pulse treatment as a result of depolarization, various pulse modes commonly used in the field of electrotherapy can be suitably selected and implemented within this scope. It is clear that there is.

In addition, the degree of depolarization referred to in the present invention is sufficient as long as the residual polarization voltage that is constantly applied to the skin does not cause skin irritation (stimulation), and the degree of depolarization that is used is sufficient as long as the residual polarization voltage that is constantly applied to the skin does not cause skin irritation. Although it can be appropriately determined depending on the conditions, it is usually particularly preferable to fall within a range in which the depolarization current value becomes a steady value substantially close to the zero level, as shown in each example.

On the other hand, as will be shown in the usage example below, it will be clear that a constant steady bias voltage or the like may be further applied at the same time as the pulse voltage, as long as it is within a range where skin irritation (stimulation) does not occur. That is, pulsed iontophoresis and weak normal temperature iontophoresis (Gal
vanizat (10 mouthfuls) may be used in combination within the above range.

Further, in the above embodiments, a general example of the skin equivalent circuit has been described, but substantially the same can be said when considering the electrical characteristics of the conductor.

As is clear from the above description, according to the iontophoresis device of the present invention, when the same power supply voltage is applied, the device for iontophoresis of the present invention is approximately several times the number of IO to several times the amount of IO when the same power supply voltage is applied, compared to the device using a continuous plain or a nested intermittent plain. A current of
Even if you take into account the loss of current charged in
Several tens of ionic drug introduction effects can be obtained. In addition, because the required amount of drug can be administered at a low voltage, or as a result of depolarization, irritation to the skin is extremely weak, and there is little risk of burns or redness. An iontophoresis device suitable for use over time can be obtained.

In particular, if the configuration is such that a pulse component in the opposite direction is output during the pause period of the treatment pulse voltage as in the embodiment, the influence of the above time constant due to the resistance component of the circuit is extremely small, and the pause of the treatment pulse voltage is relatively short. Since the area between both conductors is depolarized during this period, a high frequency DC pulse can be used, and a device capable of iontophoresis with lower skin impedance can be obtained.

Although periodic pulses have been described above from a practical standpoint, it goes without saying that essentially the same effect can be obtained even with non-periodic pulses.

Furthermore, the circuit is configured by combining a booster circuit such as a charge pump type and an output current limiting circuit with a circuit designed to depolarize between both conductors by outputting a pulse component in the opposite direction at the same time as the treatment pulse pauses. It may be. Alternatively, the booster circuit and the current limiter circuit may be provided with only one of them, or may be provided with neither the booster circuit nor the current limiter circuit.

In addition, as an example of a power supply voltage boosting mechanism, a one using a charge pump type booster circuit has been described, but the invention is not limited to this. For example, boosting by a transformer, DC
- Any configuration may be used as long as it has a similar effect, such as boosting the voltage using a DC converter.

As is clear from the above description, according to the iontophoresis device according to this embodiment, a boosting mechanism is provided in the pulse oscillation mechanism, so that good therapeutic effects can be obtained even when a low voltage power source is used.

In particular, if a button-shaped battery of about several [V] is used as in the example, and a charge pump type booster circuit is used as the booster mechanism, the volume can be made extremely small. It can be extremely suitable as a circuit for a device for tophoresis.

In addition, if an output current limiting circuit is provided as in the embodiment, a device can be obtained that can significantly reduce the current flowing through the human body at the rise and fall of the treatment pulse. Furthermore, by inserting a variable resistor into the output current limiting circuit and configuring the output current to be controlled, a device can be obtained that can perform treatment with membrane overcurrent regardless of individual differences in impedance.

Next, an embodiment of the overall structure of the iontophoresis denomination chair of the present invention will be described in detail below.

FIGS. 6 and 7 show a first embodiment. In the figure (
30) is a denocent chair for iontophoresis that is integrated into the skin, that is, configured in the form of a plaster.
) and an indifferent conductor (32). Said Deiko Seki (3
1) consists of a conductive gel layer (33) containing an ionic drug formed in the form of a flexible sheet or film, and a metal foil such as aluminum foil, a conductive rubber or resin film, a carbon film, a conductive paint, etc. The current dispersion conductive member layer (34) is laminated and integrally formed. Further, the indifferent conductor (32) is integrally formed by laminating a flexible sheet or a current dispersion conductive member layer (36) formed of aluminum foil or the like as described above. A power supply unit (37) is installed approximately at the center of the upper surface of the conductor (31). This power supply unit (37) includes a power source, for example, a so-called button-shaped battery, a pulse oscillation mechanism, and means for depolarizing the grooves (31') and (32) when the treatment pulse of this pulse oscillation mechanism is stopped. and one of the output terminals, for example, the (-) terminal, is a current dispersion conductive material layer (34).
It is installed so that it comes into contact with the 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). (3
9) 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, and
and the indifferent conductor (32) are connected to this insulating backing layer (39).
) are spaced apart and fixed. In other words, Deiko Seki (
31), the insulating conductor (32) and the power supply unit (37) are integrally supported and connected by an insulating backing layer (39).

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, and pulse oscillation is started in the ionic drug-containing conductive gel layer (33) of the Seki inductor (31). Transdermal penetration of ionic drugs is accelerated.

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. 8 and 9, 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 conductive member layers (43) and (44) for current dispersion of the Seki conductor (41) and the Seki conductor (42) are arranged at a distance of about 5 mm, and the lower surface thereof has a layer of about 0.3 mm, for example. An ultra-thin conductive gel layer (45) containing an ionic drug is adhered integrally. 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 attached to these terminals (47).

(48) and 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, in addition to the effects of the first embodiment, the manufacturing process is 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, and mass production is considered. It has a very useful effect in some 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. 10 of the drawings. In the figure, (51) is an iontophoresis device, and (52)
) indicates an indifferent conductor. (54) is a power supply, its (-) terminal is connected to the conductive material layer (55) for current dispersion of the seki conductor (52), and its (+) terminal is connected to the lead wire (55).
6) 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 easily on surfaces such as 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. 11 of the drawings. In the figure, (61) is an iontophoresis device, and (62) is a device for iontophoresis.
) indicates its kan-doyo, and (63) indicates its non-kan-doji. 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 four single-dose dry 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-lightweight pieces, 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 example, a conductive gel containing an ionic drug was used as the conductor.
These include, but are not limited to, paper materials such as water supply paper, cloth materials such as gauze, fiber materials such as absorbent cotton, sponges or porous materials such as synthetic resin open foam or water-absorbing resin, etc., ionic drugs or electrolytes. Any material may be used as long as it can impregnate and retain the liquid. 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 condition of the living body changes depending on the amount of drug administered, or when it is necessary to control the amount of drug administered depending on the situation of the living body, the output current may 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,
In particular, when it is necessary to control the dose based on the blood sugar level, such as when administering Inyulin, 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 not possible with conventional administration methods.

Each component of the plaster structure of this example will be explained in more detail as follows.

Conductive gel layer This layer is preferably made of natural resin polysaccharides such as karaya gum, tragacanth gum, xanthan gum or their corbolima, vinyl resins such as polyvinylpyrrolidone, polyvinyl methacrylate, polyacrylic acid and its sodium salt, polyacrylamide and parts thereof. Various hydrophilic natural or synthetic resins such as hydrolysates, partially saponified polyacrylic esters, and acrylic resins such as poly(acrylic acid-acrylamide) are mixed with water and/or alcohols such as ethylene glycol and glycerin. It is provided as a flexible film or sheet-like gel that is soft and plasticized and has self-shape retention and skin adhesion.

On the other hand, an electrolyte such as sodium chloride, sodium carbonate, potassium citrate, etc. is added in a required amount (usually about 10,000 to 150,000) to provide sufficient conductivity. 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 the entire structure can be attached to the skin without the need for other skin adhesive 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, the preferred conductive gel layer in this example, as well as some more specific examples, are as follows: 1. By a conventional method, the average molecular weight is 440,000, and the degree of saponification is about 60%.
30 g of polyvinyl alcohol powder was prepared, and 40 g of distilled water containing IO% NaCl preheated to 80°C was added to the powder.
g and 30 g of glycerin were added and stirred, and then the resulting mixture was heated and pressed at a pressure of 0 and 6 kg/cm2 for about 20 minutes using a hot press machine heated to 80°C to form a flexible sheet with a thickness of 3 mm. Obtained. This soft autumn clothing had sufficient skin adhesion and had a direct current resistivity (hereinafter the same) of 0.8 Ω·cm.

2. A flexible sheet-like conductive gel layer was manufactured using the following composition in the same manner as in 1 above.

(Composition Example A) Polyvinylpyrrolidone (PVPK90. manufactured by G AF).
Average molecular weight: 360,000)...20g Distilled water containing 10% NaC1...40g Glycerin...
...40 g of the obtained sheet had strong skin adhesion and a specific resistance of 0.2 Ω·cm.

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

Formalization degree 15%: Raw material polyvinyl alcohol (1Jlt60%)... 15g 5% NaCl
Distilled water: 70 g Propylene glycol: 15 g The obtained sheet had sufficient skin adhesion, and its specific resistance was I, 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% NaCl・・・
...50g ethylene glycol... ...lo
It has sufficient skin adhesion and has a specific resistance of 75Ω.
cm.

A sheet was similarly created by pressing. Specific resistance 0゜65K Ω
' cmo 5, sodium polyacrylate (Aronbis S manufactured by Nippon Tsumugi Co., Ltd.
; average molecular weight 3-5 million) 20g with 7% NaC
Contains 1! 4. Mixed with 80 g of ice cubes, heated and pressurized to prepare a sheet in the same manner. Specific resistance 0.47Ω' cm.

3. Sodium polyacrylate (Aronbis S manufactured by Nippon Tsumugi Co., 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 1 day and night.

4. 30g of karaya gum and 30g of distilled water containing 5% NaCl
and 40 g of glycerin and heated.Also, especially from an electrochemical point of view, this is globulaflor. Basic drugs such as insulin, lidocaine, and 7-stain are prepared using polyacrylic acid, methyl vinyl ether/maleic anhydride copolymer (G, A, F, manufactured by GANTREZ AN-169)
etc.), carboxypolyethylene (CARBOPOL manufactured by GOODRICH, etc.), ascorbic acid, salicylic acid, nitrous acid, riboflavin phosphate, betamethacin phosphate, tretinoin (trans-
It will be appreciated that acidic drugs such as retinoicacid can achieve high efficiency transfer of target drugs by using basic polymers such as polyacrylamide as gel bases.

For example, one of the gel compositions for propranolol is 41AN-16.
930 parts by weight glycerin 45 parts by weight water
15 parts by weight Propranolol I
O parts by weight of this gel composition is further added to a thickness of about 0.1-0.5
As mentioned above, a self-adhesive film with a thickness of about mm is extremely suitable for use as a film electrode integrated with a Seki conductor and a Seki conductor.

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 improve 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 arranging the skin-adhesive and conductive gel layer around the periphery or end 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 noidrogels 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, a skin-adhesive fixing means such as adhesive tape may be optionally added to the outer extension of the structure in this example. Of course.

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.

Various skin vitamins such as vitamin B, B, B, C,
histamine, sodium salicylate, dexamethacin,
Betamethacin phosphate, epinepherin, hydrocordisone, idoctulidine.

Propranolol, nitrites, pleomycin.

undecylene hydrochloride 9, etc.

Examples of use Examples and usage examples of the Kan inductor and Inkan inductor of the iontophoresis device of the present invention will be described in more detail below.

In other words, the conductive gel layer of both grooves is the same as that of the aforementioned Carpopol.
491 20% by weight, 30% by weight of distilled water and 40% by weight of glycerin, thickness 1.5mm, area 43cm2
It is a viscoelastic gel, and the ionic drug-containing conductive gel layer of Seki Doko is further added with 5% by weight of sodium salicylate, and the conductive gel layer of Sekidoko contains approximately 3% by weight of sodium chloride. is added.

This is used by integrally laminating and pasting a power supply connected to a 6V power supply that outputs 4KHz therapeutic pulses.

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 that 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 will also be 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
Cl-containing distilled water 15% by weight and glycerin 65% by weight
It is made of a skin-adhesive viscoelastic gel with a thickness of 1.5 mm and an area of about 12 cm, and when used, an aqueous solution containing 3% vitamin C (stored in ampoules) is applied to the conductive gel layer of the seki conductor. One to several roQ is dripped and impregnated, and the entire structure is then attached to the affected area to 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, JP-A No. 95895 of 1972 and JP-A No. 77489 of 1974.

No. 52742, 1955.

No. 81635, 1955.

No. 129035, 1955.

No. 15728, 1956.

No. 36939, 1956.

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.

No. 131428, 1957.

No. 160439, 1957.

No. 164064, 1957.

No. 166142, 1957.

No. 168675, 1957.

No. 4569, 1957.

No. 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.

[Brief explanation of drawings]

Fig. 1 is an explanatory diagram of replacing the skin with an equal number of circuits, Fig. 2 is a resistance drop characteristic diagram showing the relationship between frequency and skin resistance, and Fig. 3 shows waveforms in conventional iontophoresis. (a)
is a diagram of the pulse voltage waveform, (b) is a diagram of the current waveform flowing through the human body when the waveform in (a) is applied, and (C) is a diagram of the current waveform when the pulse with a smaller duty ratio is applied as in (a). show. FIG. 4 is a block circuit diagram showing an embodiment of the iontophoresis device of the present invention, and FIG. 5 shows its waveform.
) shows a pulse voltage waveform diagram, and (b) shows a current waveform diagram flowing through the human body when the waveform of (a) is applied. 6 and 7 show a first embodiment of the overall configuration of the iontophoresis device of the present invention, and FIG.
A sectional view taken along the line 11, and FIG. 7 shows a bottom view. FIGS. 8 and 9 show the second embodiment, and FIG.
A sectional view taken along the line -XIV, and FIG. 9 a perspective view. 10 and 11 show the third and fourth embodiments, FIG. 10 is a sectional view thereof, and FIG. 11 is a perspective view thereof. (10)...Device for iontophoresis. (2)・・・・・Power supply. (3) Pulse oscillation mechanism. (4)・・・・・Deiko Seki. (5)・・・・・・・・・Inkandoiko. (6)... Human body. (12)...Treatment pulse. (13)・・・・・・Pulse component in the opposite direction. (30), (40), (51), (61)...
・Device for iontophoresis (31), (41),
(52), (62)... Deiko Seki. (32), (42), (53), (63)...Indifferent conductor. (33), (45)...Ionic drug-containing conductive gel layer. (35)... - Conductive gel layer. (37), (49), (54), (65) Power supply unit Rs [KQ,] Fig. 1 Fig. 2 Fig. 5 Fig. 3 Fig. 7 Fig. 8 Fig. 10 Fig. 11

Claims (3)

[Claims] (1) In an iontophoresis device having a power source, a pulse oscillation mechanism, and an inductor and an inductor, for depolarizing between the two inductors during a rest period of the therapeutic pulse voltage from the pulse oscillation mechanism. An iontophoresis device characterized by having a depolarization means comprising a pulse oscillation mechanism that outputs a pulse component in the opposite direction to a treatment pulse. (2) The iontophoresis device according to claim 1, further comprising a pulse oscillation mechanism having a voltage boosting mechanism for boosting the power supply voltage. (3) The iontophoresis device according to any one of claims 1 to 2, further comprising a pulse oscillation mechanism having an output current control circuit.