CA1224993A - Applicator for the non-invasive transcutaneous delivery of medicament - Google Patents
Applicator for the non-invasive transcutaneous delivery of medicamentInfo
- Publication number
- CA1224993A CA1224993A CA000461304A CA461304A CA1224993A CA 1224993 A CA1224993 A CA 1224993A CA 000461304 A CA000461304 A CA 000461304A CA 461304 A CA461304 A CA 461304A CA 1224993 A CA1224993 A CA 1224993A
- Authority
- CA
- Canada
- Prior art keywords
- applicator
- skin
- medicament
- reservoir
- battery
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/20—Applying electric currents by contact electrodes continuous direct currents
- A61N1/30—Apparatus for iontophoresis, i.e. transfer of media in ionic state by an electromotoric force into the body, or cataphoresis
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/0404—Electrodes for external use
- A61N1/0408—Use-related aspects
- A61N1/0428—Specially adapted for iontophoresis, e.g. AC, DC or including drug reservoirs
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M37/00—Other apparatus for introducing media into the body; Percutany, i.e. introducing medicines into the body by diffusion through the skin
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/0404—Electrodes for external use
- A61N1/0408—Use-related aspects
- A61N1/0428—Specially adapted for iontophoresis, e.g. AC, DC or including drug reservoirs
- A61N1/0432—Anode and cathode
- A61N1/044—Shape of the electrode
Abstract
ABSTRACT OF THE DISCLOSURE
An applicator for the electrophoretic deposition of a medicament through or on a skin surface. The device consists of layers of a reservoir containing the drug, a battery layer superimposed on the reservoir, and a cover of electrically conductive material fully enclosing the layers and having a lip along its periphery to engage the skin surface. An electrically conductive adhesive bonds thelip of the cover to the skin.
An applicator for the electrophoretic deposition of a medicament through or on a skin surface. The device consists of layers of a reservoir containing the drug, a battery layer superimposed on the reservoir, and a cover of electrically conductive material fully enclosing the layers and having a lip along its periphery to engage the skin surface. An electrically conductive adhesive bonds thelip of the cover to the skin.
Description
BACKGROUI~D o~ THE INVENTION ~L2249~3 This invention reiates ~o an applica~cor for the non-invasi~re transcutaneous delivery of a medicament and more particularly ~o a self-contained electro-phoretic applicator of compac:t and conformable desi~n for the controlled delivery of a medicament.
The delivery of medicament through a person's skin utilizing electrophoresis is well known where the drug is one whose molecules are ionic in solution or sus-pension. The solution or suspension is made subject to an electric field and if the electrode having the same charge as that of the ions is above the solution adja-cent the skin which is the site of administration, the ions will be repelled and migrate through the skin into the blood stream.
A variety of problems associated with this tech-nique haYe limited severely the extent of its use even though in many cases it is highly advantageous to be able to deliver the drug at a controlled rate. E~uip-ment available for the electrophoretic administration of a medicament is generally bulky and expensive thereby largely limiting its use to medical offices requiring the attention of technicians. Reference to or disclosure oE such appara~us is shown in the following U. S. Patents where it will be noted that there is great emphasis in developing electrodes ~hich are disposable and/or more effective-
The delivery of medicament through a person's skin utilizing electrophoresis is well known where the drug is one whose molecules are ionic in solution or sus-pension. The solution or suspension is made subject to an electric field and if the electrode having the same charge as that of the ions is above the solution adja-cent the skin which is the site of administration, the ions will be repelled and migrate through the skin into the blood stream.
A variety of problems associated with this tech-nique haYe limited severely the extent of its use even though in many cases it is highly advantageous to be able to deliver the drug at a controlled rate. E~uip-ment available for the electrophoretic administration of a medicament is generally bulky and expensive thereby largely limiting its use to medical offices requiring the attention of technicians. Reference to or disclosure oE such appara~us is shown in the following U. S. Patents where it will be noted that there is great emphasis in developing electrodes ~hich are disposable and/or more effective-
2,492,155 4,141,359 4,250,878
3,163,166 4,166,457 4,273,135 3,289,671 4,239,052 q,367,745 3,~77,268 4,243,05~
It will be noted from VO S. Patents 3,289,671 and
It will be noted from VO S. Patents 3,289,671 and
4,141,359, in particular, ~chat rate of drug delivery is 9~3 a function of current flow and that control over cur-rent flow is crucial to having the correct amount of medicament appl i ed .
Inasmuch as it is seen that the use of this elec~rotherapy is limited to medical facilities, the costs involved in this mode of trea~ment are a direct function of the time spent using the equipment~ i.e., the time it takes to administer the medicament. Conse-quently there is great emphasis on delivering the drug as quickly as possible, resorting to the highest permissible rate of curren~ flow~ The-most effective application of syste~ic drugs is where it is delivered into the blood stream at a very constant and low rate over a long period of time, iOe., perhaps from one or more hours up to days. In such a situation it is seen that present apparatus and methods for using electro-phoresis ~or the application of medicaments are just not feasible~
There have been attempts to provide apparatus for such electrotherapy which is self-contained, so that the patient can wear the device carrying on normal activities while the drug is being administered.
Devices of this type are disclosed in U. S. Patent Nos.
385,556t 486,902, and 2,784,715. These devices are bulky, expensive, and do not provide for adequate control over the rate of~delivery nor time over which the drug is delivered.
SU1~ RY OF THE PRESENT II`~VENTION
The present invention overcomes or reduces many of the drawbacks of previous devices and methods for utilizing electrophoresis for the non-invasive ~rans-cutaneous delivery of a medicament.
9;~
This is accomplished in accordance with the principles of this inven~ion by enclosin~ a complete electrophoretic drug administration system within an applicator virtually indistinguishable when in place from an adhesive bandage. The applicator is extremely shallow, ca?able of being made with a thickness of only about a tenth of an inch, and its length and width would be determined by the desired rate of drug deliveryO
One preferred embodiment of this invention con-sists of a compact, multilayered appliçator having a first active layer containing medicament in contact with the skin, a second active layer superimposed on the first layer comprising a member to r~ake electrical contact with the skin through the first layer, and a third active layer superimposed on the second layer comprîsing the electrical battery for the applicator in electrical contact with the second layer. Other laye~s may be included to provide other functions to be described. The assembly just described is enclosed within a cover of electrically conductive material having a lip extending outwardly from the first layer and leaving the la~ter exposed and in contact with the skin. ~he underside of the lip is coated with ân electrically conductive adhesive material so that when the a?plicator is mounted on the skin the cover material surrounded ~y ~he lip is in contact with the skin. The lip acts as a return electrode so ~hat the skin completes the elec~rical circuit when the ap~licator is applied causing current to flow and ~,edicament to be moved through the skin into the blood stream.
All of the layers of the applicator may be made from conformable ma~erial so that the applicator is ~224~3 capable of being made large enough to be moun~ed over wide areas regardless of the contour involved.
Features which may be included in the applicator as described above include provision to insure a constant current flow and a device to terminate drug delivery after a predetermined period of time or quantity of drug.
It is thus a principal object of this invention to provide self-contained apparatus and a method for the electrophoretic deposition of a medicament at a con~
trolled rate.
Other objects and advantages of this invention will hereinafter become obvious from ~he following description of preferred embodiments of this invention~
BRIEF DESCRIPTION OF THE FIGURES
Fig~ 1 is an isometric view of an applicator embodyin~ the principles of this invention.
~ ig. 2 is a section view along 2-2 of Fig. 1 showing the applicator mounted on skin.
Fi~. ~ is a schematic of electrical circuitry incorporated in the embodiment shown in ~ig. 1 and 2.
Fig. 4 is an alternative arrangement for the circuit shown in Fig. 3.
DESCRIPTI~ OF T~E PREFERRE~ E~;BODIMEI~TS
~ eferring to Figs. 1 and 2, applicator 10 consists of an outer cover 12 having a raised portion 14 and a lip 16 alon~ the outer periphery. It is understood that applicator 10 can have any convenient shape or size, for example, ~uare~ rectangular, oval, circular, or tailored ~or a specific location on the skin, as 9~3 long as this is a raised central portion to accommodate the rest of the elec~rophoresis unit to be described and the lip along its periphery.
As seen in Fiq. 2, where applicator 10 is mounted on the surface of skin 18 of a patient, enclosed within the raised portion 14 of cover 12 are several layers to be described. The first layer is a microporous or semi-permeable membrane 22 through which the medicament migrates to be deposited on skin 18. As will be noted from the fo~lowing discussion, membrane 22 may not be needed depending on the nature of the reservoir for the medicament.
The second layer consists of a flexible pouch or reservoir 24 containing the drug to be administered.
As is un~erstood in the art, and shown i~ one or more of the Ua 5~ patents identified above, reservoir 24 can be a pouch containing the drug of choice in solution or suspension, the walls of which are sufficiently dense to prevent leakage of the drug under ambient condi-tions, but sufficiently porous to permi~ migration of the charged particles or ions under the influence of the electric field i~posed. It should be noted ~hat i~
would be appropriate to employ the microporous melnbrane 22 when leakage under ambient conditions could occur, for example, as a result of packing of the applicators for shipment or stnrage, fluctuating temperatures, and possibly puncture of the reservoir~ Also, the use of the membrane 22 could deyend in large meas~re on the nat~re of the medicament involved. In the alternative, reservoir 24 can consist of porous material in which the drug ls impregnated rather than a you~h containing the liquid medicament.
The third or next layer above reservoir 24 is an extended contact 26 which could be incorporated as one 9~3 face of battery ~8 which is the next layer~ Contact 26 could be any suitable conductive material, preferably conformable to permit applicator 10 to be curved or bent to conform to the shaped surfaoe of the skin.
Suitable materials of this type are well known in the art and include electrically conductive polymers, preferable non-ionic. Carbon loaded or surface metalized plastics are also available for such use.
Battery 28 comprising the next layer can be made up of a group of cells internally connected in series to obtain the desired voltage necessary ~o obtain the electrophoretic action with the par~icular medicament.
Orientation of battery 28 would depend on whether the charged (ionic) particles of the drug of choice are positive or negative. If the particles are negatively charged in solution or suspension then contact 26 would be connected to the negative side of battery 28 as the skin will then be positive with respect to that contact and will attract the ions. With regard to battery 28, it sh~uld be noted that any conventisnal miniaturized battery cells now generally available can be employed, arranged and connected in series to obtain the desired operating voltage~ In addition, the technology now exists for batteries which are made up ov very thin, flexible sheets of a conductive polymer with high surface areas relative to thickness to provide adequate current densities. One such so-called plastic battery is described in "Batteries Todayn, Autumn 1981, pages 10, 11~ and 24. t~hen such a battery is emyloyed, sheets may be layered to place the cells in series, and an effective compron~ise between number of sheets and surface areas cf sheets is to layer them in a dia~onal as shown somewhat schema~ically in Fig, 2. Of course, battery selection would ultimately depend on such ~ 2 ~ ~ ~ 3 factors as the degree of conformability desired, voltage and current densities required for a specific application~ and time of discharge.
Layered abDve battery 28 would be another contact 32 which could be similar in construction ~o that of contact 26 and connected electrically to the opposite side of battery 28~
Cover 12 which encloses all of the layers of applicator 10 is made from a flexible conductive plastic material such as a polymer impregnated with carbon or surface metalized plastic. .Insulating material 34 fills the space between the side wall of raised portion 14 and the various layers contained therein.
An electrically conductive adhesive material 36 coats the underside of lip 16 so that applicator 10 may be placed on and adhere to skin lB and make good electrical contact.
It will be seen that the above described arrange-ment forms a co~plete electric circuit from one side of battery 28, cover 12, adhesive material 36, skin 18, microporous membrane 22~ liquid reservoir 24, and back to battery 28.
For a more particular description of the elec-trical circuit formed by the arrangement just described, reference is made to Fig. 3 wherein the circuit is shown schematicaly with numerals corre-sponding t~ the structure shown in Figs~ 1 and 2~
~ attery 28 is connected through contact 32, cover 12, and adhesive layer 36 to s~in 180 The other side of bat~ery 28 is connected electrically through contact 26, liquid reservoir 24 and membrane 22 to skin 18 to complete the ci rcuit. Resistor Reff re~resents the effective re~istance of the complete circuit, including ~2~9~9~3 skin 18, the adhesive layer 36, cover 12, battery 28 and its contacts 26 and 32, as well as reservoir 24 and membrane 22, In a system of this type, one of the aimC
is to establish a very low rate of current flow so that the medica~ent will be deposited slowly over a long period of time. Current flow of down as low as 0.0001 ampere-hour per square centimeter of s~in surface below membrane 22 is a typical current which may be selected for the application of a particular drug. Electrical resistance of the skin to current flow is of the order of 6-~ X ohms and is roughly independent of the dis-tance be~ween the points on the skin where electrical contact is made. This is because skin electrical resistance is largely ~hat of resistance to penetra-tion, the cutrent flowing through the fluids of the body in which electrical resistance being very low.
Thus, in order to establish current flow at the rate indicated, by ohm's law, it is seen that total resistance of the circui~ using a 1.5 volt battery should be about 360 K ohms for each square centimeter of application. This resistance, the effective resistance, Ref, of the circuit, can be built into any one component or combination of components of the circuit shown in Fig~ 3, including tl)e battery resistance, electrodes, cover material, etc~ In addition, if desired, in order to maintain current flow constant over the full period of operation a constant current limiting device can be made integral with and a part of conductor 26, or any other part of the circuit where it is found convenient to do so.
Furthermore, as indicated schematically in Fig. 4, a~plicator 10 may be designed to incorporate provision to insure that the deposit of medicament will cease after a given period of time or after a certain ~2~9~3 quantity of drug is administered. This can be a- in-plished by inserting in the circuit an integrating device such as a reverse plating cell 38. Cell 38, as is known in the art, comprises a pair of electrodes on which one is a coating o~ material to be trans~ferred to the other electrode. When all of the plating material is de~osited, after a predetermined period o~ ~ime based upon the thickness of the original coating has lapsed, or integrated current flow representing the desired ~uantity of drug to be delivered, there is a large increase in internal resistance resulting in a substantial drop of current flow and an effective halt to drug ~igration. Such a device can be employed to establish in advance the period of time over which the medicament is to be applied or, as noted above, the quantity of the drug to ~e delivered. Cell 38 is a relatively high resistance device and could provide for much of the high resistance required for the o~era~ion of ap~licator 10.
Cell 38 may be made a part of contact 32 or be inserted betheen contact 32 and cover material 14. In addition, provision may be made for curren~ flow to be built up gradually to avoid any shock to the reci~ient of the drug.
Applica~or 10 may be prepared in advance, in different sizes and shapes, sealed within a plastic pouch, with a ?rotective s~rip over its exposed side.
Different drugs can be incorporated for particular applications, batteries may be varied to meet specific current flow requirements, and of course the electrical orientation of each battery would depend on the particular medicament. In the use of the device, the ~ro~ective stri~ is relnoved and the applicator placed on the skin where desired such as behind the ear.
2~ 3 Current flow starts immecliately along with migration ~f the drug.
The use of the invention as herein described makes it possible for the first time to provide for drug therapy over an extended period of time with a degree ~f control and accuracy which here~ofore h~ not boen possible or practical. The cost of such therapy using this invention is reduced significantly wlth the result that extensive use of the invention will have a favorable economic impact on medical care.
While only certain preferred embodiments of this invent;on have been described, it is understood that many embodiments thereof are pcssible without departing from the principles of this invention as defined in the claims which ~ollow.
,. --10--
Inasmuch as it is seen that the use of this elec~rotherapy is limited to medical facilities, the costs involved in this mode of trea~ment are a direct function of the time spent using the equipment~ i.e., the time it takes to administer the medicament. Conse-quently there is great emphasis on delivering the drug as quickly as possible, resorting to the highest permissible rate of curren~ flow~ The-most effective application of syste~ic drugs is where it is delivered into the blood stream at a very constant and low rate over a long period of time, iOe., perhaps from one or more hours up to days. In such a situation it is seen that present apparatus and methods for using electro-phoresis ~or the application of medicaments are just not feasible~
There have been attempts to provide apparatus for such electrotherapy which is self-contained, so that the patient can wear the device carrying on normal activities while the drug is being administered.
Devices of this type are disclosed in U. S. Patent Nos.
385,556t 486,902, and 2,784,715. These devices are bulky, expensive, and do not provide for adequate control over the rate of~delivery nor time over which the drug is delivered.
SU1~ RY OF THE PRESENT II`~VENTION
The present invention overcomes or reduces many of the drawbacks of previous devices and methods for utilizing electrophoresis for the non-invasive ~rans-cutaneous delivery of a medicament.
9;~
This is accomplished in accordance with the principles of this inven~ion by enclosin~ a complete electrophoretic drug administration system within an applicator virtually indistinguishable when in place from an adhesive bandage. The applicator is extremely shallow, ca?able of being made with a thickness of only about a tenth of an inch, and its length and width would be determined by the desired rate of drug deliveryO
One preferred embodiment of this invention con-sists of a compact, multilayered appliçator having a first active layer containing medicament in contact with the skin, a second active layer superimposed on the first layer comprising a member to r~ake electrical contact with the skin through the first layer, and a third active layer superimposed on the second layer comprîsing the electrical battery for the applicator in electrical contact with the second layer. Other laye~s may be included to provide other functions to be described. The assembly just described is enclosed within a cover of electrically conductive material having a lip extending outwardly from the first layer and leaving the la~ter exposed and in contact with the skin. ~he underside of the lip is coated with ân electrically conductive adhesive material so that when the a?plicator is mounted on the skin the cover material surrounded ~y ~he lip is in contact with the skin. The lip acts as a return electrode so ~hat the skin completes the elec~rical circuit when the ap~licator is applied causing current to flow and ~,edicament to be moved through the skin into the blood stream.
All of the layers of the applicator may be made from conformable ma~erial so that the applicator is ~224~3 capable of being made large enough to be moun~ed over wide areas regardless of the contour involved.
Features which may be included in the applicator as described above include provision to insure a constant current flow and a device to terminate drug delivery after a predetermined period of time or quantity of drug.
It is thus a principal object of this invention to provide self-contained apparatus and a method for the electrophoretic deposition of a medicament at a con~
trolled rate.
Other objects and advantages of this invention will hereinafter become obvious from ~he following description of preferred embodiments of this invention~
BRIEF DESCRIPTION OF THE FIGURES
Fig~ 1 is an isometric view of an applicator embodyin~ the principles of this invention.
~ ig. 2 is a section view along 2-2 of Fig. 1 showing the applicator mounted on skin.
Fi~. ~ is a schematic of electrical circuitry incorporated in the embodiment shown in ~ig. 1 and 2.
Fig. 4 is an alternative arrangement for the circuit shown in Fig. 3.
DESCRIPTI~ OF T~E PREFERRE~ E~;BODIMEI~TS
~ eferring to Figs. 1 and 2, applicator 10 consists of an outer cover 12 having a raised portion 14 and a lip 16 alon~ the outer periphery. It is understood that applicator 10 can have any convenient shape or size, for example, ~uare~ rectangular, oval, circular, or tailored ~or a specific location on the skin, as 9~3 long as this is a raised central portion to accommodate the rest of the elec~rophoresis unit to be described and the lip along its periphery.
As seen in Fiq. 2, where applicator 10 is mounted on the surface of skin 18 of a patient, enclosed within the raised portion 14 of cover 12 are several layers to be described. The first layer is a microporous or semi-permeable membrane 22 through which the medicament migrates to be deposited on skin 18. As will be noted from the fo~lowing discussion, membrane 22 may not be needed depending on the nature of the reservoir for the medicament.
The second layer consists of a flexible pouch or reservoir 24 containing the drug to be administered.
As is un~erstood in the art, and shown i~ one or more of the Ua 5~ patents identified above, reservoir 24 can be a pouch containing the drug of choice in solution or suspension, the walls of which are sufficiently dense to prevent leakage of the drug under ambient condi-tions, but sufficiently porous to permi~ migration of the charged particles or ions under the influence of the electric field i~posed. It should be noted ~hat i~
would be appropriate to employ the microporous melnbrane 22 when leakage under ambient conditions could occur, for example, as a result of packing of the applicators for shipment or stnrage, fluctuating temperatures, and possibly puncture of the reservoir~ Also, the use of the membrane 22 could deyend in large meas~re on the nat~re of the medicament involved. In the alternative, reservoir 24 can consist of porous material in which the drug ls impregnated rather than a you~h containing the liquid medicament.
The third or next layer above reservoir 24 is an extended contact 26 which could be incorporated as one 9~3 face of battery ~8 which is the next layer~ Contact 26 could be any suitable conductive material, preferably conformable to permit applicator 10 to be curved or bent to conform to the shaped surfaoe of the skin.
Suitable materials of this type are well known in the art and include electrically conductive polymers, preferable non-ionic. Carbon loaded or surface metalized plastics are also available for such use.
Battery 28 comprising the next layer can be made up of a group of cells internally connected in series to obtain the desired voltage necessary ~o obtain the electrophoretic action with the par~icular medicament.
Orientation of battery 28 would depend on whether the charged (ionic) particles of the drug of choice are positive or negative. If the particles are negatively charged in solution or suspension then contact 26 would be connected to the negative side of battery 28 as the skin will then be positive with respect to that contact and will attract the ions. With regard to battery 28, it sh~uld be noted that any conventisnal miniaturized battery cells now generally available can be employed, arranged and connected in series to obtain the desired operating voltage~ In addition, the technology now exists for batteries which are made up ov very thin, flexible sheets of a conductive polymer with high surface areas relative to thickness to provide adequate current densities. One such so-called plastic battery is described in "Batteries Todayn, Autumn 1981, pages 10, 11~ and 24. t~hen such a battery is emyloyed, sheets may be layered to place the cells in series, and an effective compron~ise between number of sheets and surface areas cf sheets is to layer them in a dia~onal as shown somewhat schema~ically in Fig, 2. Of course, battery selection would ultimately depend on such ~ 2 ~ ~ ~ 3 factors as the degree of conformability desired, voltage and current densities required for a specific application~ and time of discharge.
Layered abDve battery 28 would be another contact 32 which could be similar in construction ~o that of contact 26 and connected electrically to the opposite side of battery 28~
Cover 12 which encloses all of the layers of applicator 10 is made from a flexible conductive plastic material such as a polymer impregnated with carbon or surface metalized plastic. .Insulating material 34 fills the space between the side wall of raised portion 14 and the various layers contained therein.
An electrically conductive adhesive material 36 coats the underside of lip 16 so that applicator 10 may be placed on and adhere to skin lB and make good electrical contact.
It will be seen that the above described arrange-ment forms a co~plete electric circuit from one side of battery 28, cover 12, adhesive material 36, skin 18, microporous membrane 22~ liquid reservoir 24, and back to battery 28.
For a more particular description of the elec-trical circuit formed by the arrangement just described, reference is made to Fig. 3 wherein the circuit is shown schematicaly with numerals corre-sponding t~ the structure shown in Figs~ 1 and 2~
~ attery 28 is connected through contact 32, cover 12, and adhesive layer 36 to s~in 180 The other side of bat~ery 28 is connected electrically through contact 26, liquid reservoir 24 and membrane 22 to skin 18 to complete the ci rcuit. Resistor Reff re~resents the effective re~istance of the complete circuit, including ~2~9~9~3 skin 18, the adhesive layer 36, cover 12, battery 28 and its contacts 26 and 32, as well as reservoir 24 and membrane 22, In a system of this type, one of the aimC
is to establish a very low rate of current flow so that the medica~ent will be deposited slowly over a long period of time. Current flow of down as low as 0.0001 ampere-hour per square centimeter of s~in surface below membrane 22 is a typical current which may be selected for the application of a particular drug. Electrical resistance of the skin to current flow is of the order of 6-~ X ohms and is roughly independent of the dis-tance be~ween the points on the skin where electrical contact is made. This is because skin electrical resistance is largely ~hat of resistance to penetra-tion, the cutrent flowing through the fluids of the body in which electrical resistance being very low.
Thus, in order to establish current flow at the rate indicated, by ohm's law, it is seen that total resistance of the circui~ using a 1.5 volt battery should be about 360 K ohms for each square centimeter of application. This resistance, the effective resistance, Ref, of the circuit, can be built into any one component or combination of components of the circuit shown in Fig~ 3, including tl)e battery resistance, electrodes, cover material, etc~ In addition, if desired, in order to maintain current flow constant over the full period of operation a constant current limiting device can be made integral with and a part of conductor 26, or any other part of the circuit where it is found convenient to do so.
Furthermore, as indicated schematically in Fig. 4, a~plicator 10 may be designed to incorporate provision to insure that the deposit of medicament will cease after a given period of time or after a certain ~2~9~3 quantity of drug is administered. This can be a- in-plished by inserting in the circuit an integrating device such as a reverse plating cell 38. Cell 38, as is known in the art, comprises a pair of electrodes on which one is a coating o~ material to be trans~ferred to the other electrode. When all of the plating material is de~osited, after a predetermined period o~ ~ime based upon the thickness of the original coating has lapsed, or integrated current flow representing the desired ~uantity of drug to be delivered, there is a large increase in internal resistance resulting in a substantial drop of current flow and an effective halt to drug ~igration. Such a device can be employed to establish in advance the period of time over which the medicament is to be applied or, as noted above, the quantity of the drug to ~e delivered. Cell 38 is a relatively high resistance device and could provide for much of the high resistance required for the o~era~ion of ap~licator 10.
Cell 38 may be made a part of contact 32 or be inserted betheen contact 32 and cover material 14. In addition, provision may be made for curren~ flow to be built up gradually to avoid any shock to the reci~ient of the drug.
Applica~or 10 may be prepared in advance, in different sizes and shapes, sealed within a plastic pouch, with a ?rotective s~rip over its exposed side.
Different drugs can be incorporated for particular applications, batteries may be varied to meet specific current flow requirements, and of course the electrical orientation of each battery would depend on the particular medicament. In the use of the device, the ~ro~ective stri~ is relnoved and the applicator placed on the skin where desired such as behind the ear.
2~ 3 Current flow starts immecliately along with migration ~f the drug.
The use of the invention as herein described makes it possible for the first time to provide for drug therapy over an extended period of time with a degree ~f control and accuracy which here~ofore h~ not boen possible or practical. The cost of such therapy using this invention is reduced significantly wlth the result that extensive use of the invention will have a favorable economic impact on medical care.
While only certain preferred embodiments of this invent;on have been described, it is understood that many embodiments thereof are pcssible without departing from the principles of this invention as defined in the claims which ~ollow.
,. --10--
Claims (8)
1. An applicator for the electrophoretic migra-tion of a medicament in ionic solution or suspension through the skin into the blood stream of a patient comprising reservoir means containing said medicament, battery means adjacent one side of said reservoir means with the side of said battery means facing said reservoir means having the same charge as the charge of the medicament ions in said solution or suspension, cover means of electrically conductive material partially enclosing said battery means and said reservoir means leaving the side of said reservoir means opposite that of said battery means exposed for contacting said skin, said cover means having a lip along the periphery of said applicator for making contact with said skin when mounted on said skin leaving said battery means and reservoir means fully enclosed, and electrically conductive adhesive material coating the underside of said lip whereby when said applicator is mounted on said skin a complete electrical circuit through said skin is formed and the ions of said medicament in said reservoir means migrate out of said reservoir means and through said skin into the blood stream of said patient.
2. The applicator of claim 1 in which said reservoir means is made from a microporous material whereby said solution or suspension provides an electrical path therethrough.
3. The applicator of claim 2 in which all com-ponents are conformable to the shape of said skin.
4. The applicator of claim 2 having means to maintain constant current flow during the period said medicament is being delivered.
5. The applicator of claim 4 having means to terminate deposition of said medicament after a pre-determined quantity of medicament is delivered.
6. The applicator of claim 5 in which the last named means is a reverse plating cell.
7. The applicator of claim 3 having a semi-permeable membrane within said cover means on the side of said reservoir means facing said skin.
8. The applicator of claim 7 having means within said cover means for electrically insulating the latter from said reservoir means.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US524,252 | 1983-08-18 | ||
| US06/524,252 US4557723A (en) | 1983-08-18 | 1983-08-18 | Applicator for the non-invasive transcutaneous delivery of medicament |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1224993A true CA1224993A (en) | 1987-08-04 |
Family
ID=24088425
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000461304A Expired CA1224993A (en) | 1983-08-18 | 1984-08-17 | Applicator for the non-invasive transcutaneous delivery of medicament |
Country Status (10)
| Country | Link |
|---|---|
| US (1) | US4557723A (en) |
| EP (1) | EP0147524B1 (en) |
| JP (1) | JPS6060860A (en) |
| KR (1) | KR930005050B1 (en) |
| AT (1) | ATE45290T1 (en) |
| AU (1) | AU563137B2 (en) |
| BR (1) | BR8404119A (en) |
| CA (1) | CA1224993A (en) |
| DE (1) | DE3479294D1 (en) |
| MX (1) | MX158181A (en) |
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-
1983
- 1983-08-18 US US06/524,252 patent/US4557723A/en not_active Expired - Lifetime
-
1984
- 1984-08-13 AU AU31850/84A patent/AU563137B2/en not_active Ceased
- 1984-08-17 MX MX202435A patent/MX158181A/en unknown
- 1984-08-17 EP EP84109840A patent/EP0147524B1/en not_active Expired
- 1984-08-17 CA CA000461304A patent/CA1224993A/en not_active Expired
- 1984-08-17 DE DE8484109840T patent/DE3479294D1/en not_active Expired
- 1984-08-17 JP JP59171396A patent/JPS6060860A/en active Granted
- 1984-08-17 BR BR8404119A patent/BR8404119A/en not_active IP Right Cessation
- 1984-08-17 AT AT84109840T patent/ATE45290T1/en not_active IP Right Cessation
- 1984-08-17 KR KR1019840004970A patent/KR930005050B1/en not_active IP Right Cessation
Also Published As
| Publication number | Publication date |
|---|---|
| ATE45290T1 (en) | 1989-08-15 |
| KR930005050B1 (en) | 1993-06-15 |
| DE3479294D1 (en) | 1989-09-14 |
| EP0147524A1 (en) | 1985-07-10 |
| KR850001702A (en) | 1985-04-01 |
| BR8404119A (en) | 1985-07-16 |
| MX158181A (en) | 1989-01-13 |
| JPH0456627B2 (en) | 1992-09-09 |
| AU3185084A (en) | 1985-02-21 |
| AU563137B2 (en) | 1987-06-25 |
| EP0147524B1 (en) | 1989-08-09 |
| JPS6060860A (en) | 1985-04-08 |
| US4557723A (en) | 1985-12-10 |
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| Date | Code | Title | Description |
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| MKEX | Expiry |