WO2002068044A2 - Tissue electroperforation for enhanced drug delivery and sampling - Google Patents
Tissue electroperforation for enhanced drug delivery and sampling Download PDFInfo
- Publication number
- WO2002068044A2 WO2002068044A2 PCT/US2002/006101 US0206101W WO02068044A2 WO 2002068044 A2 WO2002068044 A2 WO 2002068044A2 US 0206101 W US0206101 W US 0206101W WO 02068044 A2 WO02068044 A2 WO 02068044A2
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- membrane
- electrode
- electroperforation
- electric current
- electrodes
- Prior art date
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14507—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue specially adapted for measuring characteristics of body fluids other than blood
- A61B5/1451—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue specially adapted for measuring characteristics of body fluids other than blood for interstitial fluid
- A61B5/14514—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue specially adapted for measuring characteristics of body fluids other than blood for interstitial fluid using means for aiding extraction of interstitial fluid, e.g. microneedles or suction
-
- 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
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/325—Applying electric currents by contact electrodes alternating or intermittent currents for iontophoresis, i.e. transfer of media in ionic state by an electromotoric force into the body
-
- 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
- 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
- A61N1/303—Constructional details
- A61N1/306—Arrangements where at least part of the apparatus is introduced into the body
Definitions
- Electroporation is a process of creating transient microscopic pores on a barrier membrane, by extremely short pulses of high electric voltage and low current.
- U.S. Patent Nos . 5,019,034, 5,547,467, 5,667,491, and 5,749,847 describe an "electroporation" method of treating a tissue in order to transiently increase the tissue's permeability to enhance molecular transport either for drug delivery or for sampling of interstitial fluids. All three of these transport methods are described by Sun in “Skin Absorption Enhancement by Physical Means: Heat, Ultrasound, and Electricity,” Transdermal and Topical Drug Delivery Systems, Interpharm Press, Inc., 1997, pages 327-355.
- US patent No. 5,993,434 discloses an apparatus that provides an effective and convenient means for positioning electrodes into tissue for the injection of therapeutic compounds into the tissue and application of electric fields to the tissue.
- the present invention features a method for transporting a molecule through a barrier membrane of at least one layer of cells (e.g., the skin of a mammal such as a human) comprising the steps of: ablating the membrane (e.g., destroying the cells of the membrane) with an electric current from a treatment electrode; and utilizing a driving force to move the molecule through the perforated membrane (e.g., either moved into or out of the mammal through the membrane) .
- membranes include, but are not limited to, skin, buccal, vaginal, and rectal membranes (e.g., of a human) .
- Molecules e.g., compounds such as active agents
- Molecules which may be delivered by the method and/or device of the present invention include, but are not limited to, any material capable of exerting a biological effect on a human body, such as therapeutic drugs, including, but not limited to, organic and macromolecular compounds such as polypeptides, proteins, saccharides, polysaccharides, polynucleotides, and nutrients .
- the treatment electrode does not contact the membrane and an electric current forms an electric arc between the treatment electrode and the membrane.
- the method further comprises the use of an indifferent electrode, where the electric current passes from the treatment electrode, through the membrane, and to the indifferent electrode.
- the two electrodes may or may not have direct contact with the skin.
- the electric current may be a direct current, an alternating current, or a mixture thereof.
- the frequency of the alternating current may be between about 30 Hz to about 10,000kHz (e.g., between about 60 kHz to about 5 MHz such as between about 100 kHz to about 4 MHz) .
- the voltage of the current, the energy output, the duration of the process, as well as the size, shape and number of the electroperforation electrodes may vary depending on the size and depth of the ablation required.
- the voltage may range from about 1 to about 2000 volts (e.g., 5 to 700 volts) .
- the waveform of the electric current may be a damped sine wave, modulated sine wave, pure sine wave, damped square wave, modulated square wave, pure square wave, direct current, or a blend wave thereof.
- driving forces include, but are not limited to: iontophoresis, electro-osmosis, reverse iontophoresis, and electroporation where a delivery electrode and a return electrode are used to transport the molecule through the membrane; phonophoresis where an ultrasonic transducer that converts electric energy into acoustic energy to transport the molecule; pressure gradients where a mechanic apparatus that is capable generating either a positive or negative pressure gradient across the barrier membrane is used, respectively to move molecules into or out of the mammal; heat where the increase in temperature enhances transport of the molecule; and concentration gradients where the higher concentration of the molecule one side of the membrane causes its transport across the membrane .
- the method further comprises the step of piercing the membrane with a member selected from the group consisting of needles or blades. In one embodiment, the method further comprises the step of applying a conductive material to the membrane prior the ablation. Examples of a conductive materials include, but are not limited to, electrolytes, metal particles, or carbon particles. In one embodiment, the method further comprises the step of cooling and/or applying an analgesic to the membrane prior to or during the ablation. In one embodiment, the method further comprises the step of monitoring the electrical resistance (e.g., impedance) of the membrane in order to determine the presence of ablation in the membrane.
- the electrical resistance e.g., impedance
- the present invention features a device for transporting a molecule through a barrier membrane of a mammal comprising: a housing having a skin contacting surface; a reservoir having an orifice in communication with the skin contacting surface; a current controller for making an electric current capable of ablating the membrane; and a treatment electrode proximate to the skin contacting surface for delivering the current to the membrane where the treatment electrode is in electronic communication with the current controller; wherein upon contacting the skin contacting surface with the membrane, the device is capable of both ablating the membrane with the electric current and transporting the molecule either from the reservoir, through the membrane, and into the mammal or from the mammal, through the membrane, and into the reservoir.
- the treatment electrode may or may not come into contact with the membrane .
- the device comprises a plurality of treatment electrodes (e.g., between 2 and 200 treatment electrodes, such as between 2 and 50 treatment electrodes, per square centimeter of the electrode surface) .
- the device comprises an indifferent electrode which is used either as an return electrode when in contact with the membrane to complete the electric circuit in bi-terminal electroperforation, or, when not in contact with the membrane, to help directing the electric energy to the barrier membrane in the mono-terminal mode of electroperforation. See S.V. Pollack, S.V.: “Electrosurgery", in Dermatology, Ed. S.L. Moschella and H.J. Hurley, (W.B. Saunders Company, 1992), pages 2419-2431.
- the device comprises a sensor for measuring the electrical resistance (e.g., impedance) of the membrane.
- the reservoir comprises an iontophoretic electrode for drug delivery by iontophoresis and/or electro-osmosis, or for interstitial fluid sampling by reverse iontophoresis.
- the reservoir comprises a delivery electrode and a semipermeable membrane (e.g., permeable to the fluid within the reservoir, but not permeable to the molecule being transported through the membrane) , wherein the semipermeable membrane separates the delivery electrode and the orifice.
- the reservoir further comprises a sensor selected from the group consisting of sensors for measuring the pH, molecule or ion concentration, electric conductivity, amperage, and potential, pressure, color and temperature of the fluid in the reservoir.
- the device further comprises a power supply (e.g., a battery) for providing a source of electric current to the current controller from which the current controller modifies (e.g., via a circuit) the electric parameters of the current (e.g., the voltage, waveform, frequency, and duration) for use in ablating the membrane.
- a power supply e.g., a battery
- the current controller modifies (e.g., via a circuit) the electric parameters of the current (e.g., the voltage, waveform, frequency, and duration) for use in ablating the membrane.
- the current controller is capable of being attached to an external power supply.
- FIG. 1 is a schematic representation of an example of an apparatus of the present invention that can be used for the electroperforation process under a "mono- terminal" condition.
- FIG. 2a is a schematic representation of an example of an apparatus of the present invention that can be used for the electroperforation process under a "bi-terminal" condition, using one small treatment electrode and one large indifferent electrode .
- FIG. 2b is a schematic representation of an example of an apparatus of the present invention that can be used for the electroperforation process under a "bi-terminal" condition, using two small, closely positioned electrodes parallel to the barrier membrane.
- FIG. 2c is a schematic representation of an example of an apparatus of the present invention that can be used for the electroperforation process under a "bi-terminal" condition, using two closely positioned electrodes. The small treatment electrode is located closer to the membrane .
- FIG. 3 is a schematic representation of an example of an apparatus of the present invention that can be used both for the electroperforation process and for the transportation of a molecule through the perforated barrier.
- FIG. 5 is a schematic representation of an example of an apparatus that combines an electroperforation unit with an iontophoresis unit.
- the electroperforation unit has four electroperforation electrodes that can be used for the electroperforation process under a "mono- terminal" condition.
- the iontophoresis unit is used for the transportation of a molecule through the perforated barrier.
- FIG. 7b is a cross-section view of a schematic representation of an example of an apparatus of the present invention having spacers .
- FIG. 8 is a cross-section view of a schematic representation of some examples of electroperforation electrode tips that can be used in the apparatus of the present invention.
- FIG. 10 shows the blood glucose reduction in two pigs as a result from transdermal insulin delivery by iontophoresis through the skin treated with electroperforation.
- FIG. 12 shows an electrical schematic of one embodiment of the electroperforation mechanism.
- stratum cornea with different lipid contents respond differently toward the use of chemical penetration enhancers that primarily affect lipid domain and pathways.
- Stratum cornea thickness affects most transdermal delivery relying on passive diffusion of drugs.
- Mechanical properties such as skin elasticity and toughness dictate the outcome of mechanical ablation of stratum corneum utilizing methods described in PCT Patent Applications WO 98/11937 and WO 97/48440, U.S. Patent Nos. 5,250,023 and 5,843,114, and Henry et al . , "Micro fabricated Microneedles : A Novel Approach to Transdermal Drug Delivery” , S. Henry, D.V. McAllister, M.G. Allen and M.R. Prausnitz, Journal of Pharmaceutical Sciences, Vol.
- the electroperforation process of the present invention may be conducted in a liquid such as drug solution. It, therefore, is possible to repeat electric current treatment to the skin during a drug delivery process if the pores created previously have closed due to eventual tissue growth or other reasons.
- a drug solution may be present or absent during the electroperforation process.
- the drug solution may be subsequently placed into the chamber 34 (e.g., either through a septum with a syringe or through a port on the wall of the chamber 34 from a breakable capsule (neither shown) ) after the electroperforation process is completed.
- the electroperforation mechanism 111 comprises an oscillator 110, which produces a clock signal, which provides the timing pulse to the counter 112.
- the counter 112 increases to the next state on each successive rising edge of the oscillator 110 pulse.
- various outputs of the multiplexor 116 are selected according to the state of the counter 110.
- the outputs of the multiplexor 116 activate the appropriate high voltage relay within the relay bank 122 thus allowing the RF signal from the RF power source 120 to reach a particular electrode on the electrode array 124.
- the high state threshold 170 depends on the IC Logic family and supply voltage.
- Initial activation of the foot switch 130 sends the input of inverter 118B high causing a low signal 160 at the input of 118A.
- Propagation of the signal through 118A causes a high signal at the input of AND-gate 118E. Since the RC charging circuit 118H, 1181 has not reached the high signal threshold potential 170 a low value 160 is propagated through inverter 118C thus causing a high voltage 170 on the second input to the AND-gate 118E.
- the inverter 118D converts the signal to a low voltage which activates the one-shot timing circuit 114C.
- the one-shot or monostable multivibrator and the astable multivibrator are well known circuit configurations using the 555/556 family of IC timers (ST Microelectronics NE556N) .
- ST Microelectronics NE556N IC timers
- This monostable circuit 114C is inverted by inverter 114F and presented as an input to the OR-gate 114G for logical control of the enable line of the counter 112A.
- a special feature of the RF control circuitry is that the foot switch 130 must be reset before another cycle can be completed. This combination of circuitry prevents any foot switch 130 oscillations or multiple circuit activations before a single cycle completes.
- Additional control circuitry utilizes OR-gate 114L and OR-gate 114N to select between the two multiplexors 116A, 116B based on the level of the MSB (pin 2) of the counter 112A output. A high voltage on the MSB results in multiplexor 116B while a low signal on this same line selects multiplexor 116A.
- OR-gate 114G The combined outputs of the two monostable pulses function as inputs to OR-gate 114G.
- the output of this component serves as an input to the OR-gates 114L, 114N which select the appropriate multiplexors 116A, 116B.
- the RF ground relay 144 is also closed while the analog ground relay 146 is deactivated (opened) .
- the impedance feedback means functions to insure that the proper depth of penetration has been reached within the tissue from each activation of the electrode array 124.
- the microprocessor's 140 algorithm compares the initial and current impedance values under each electrode fired and determines if an additional electroperforation pulse is required based on predefined thresholds .
- the tissue locations under various electrodes which have not reached a certain impedance threshold shall be automatically selected by the microprocessor's 140 algorithm and an additional electroperforation cycle for those particular electrodes will occur.
- the microprocessor 140 will have an algorithm which automatically increases or decreases the RF power and pulse duration applied to the electrode array 124 to obtain the necessary impedance change at the skin surface .
- the impedance values can be measured between any two electrodes of the electrode array 124 or between any electrode and the grounding pad 126.
- the impedance change measured resulted in about a 60%- 75% reduction in impedance when compared to the pre- treatment case.
- the above mentioned embodiment utilized a 1000Hz sinusoidal signal for impedance testing.
- the aforementioned circuit could contain a microprocessor control for additional flexibility and improved feedback control .
- the microprocessor based device could communicate information about the device settings, procedure duration, and effectiveness through serial, optical, or telemetry based methods.
- the impedance/conductance based electrode could serve a dual purpose and function as a delivery electrode utilizing delivery means such as iontophoresis to enhance drug delivery.
- This entire circuit whether analog or microprocessor based could be contained in a drug delivery patch which monitors the skin during the electroperforation process to insure breakdown of the stratum corneum and then provides a driving force using iontophoresis, electroperforation, or concentration gradients to facilitate drug delivery.
- Additional embodiments of these device could function as a skin preparatory treatment for enhancing drug delivery or enabling drug delivery of large or difficult-to-deliver molecules including; insulin, erythropoetin, proteins, peptides, and hormones.
- Another embodiment of this device could contain vacuum, suction, reverse iontophoresis, or other extraction capabilities to elicit substances from interstitial fluid once the stratum corneum has been perforated.
- An additional embodiment may contain infrared sensors to monitor tissue effects at the surface of the skin such as erythema as well as conduct spectroscopy of specific analytes at the skin service such as glucose.
Abstract
Description
Claims
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
AU2002252152A AU2002252152A1 (en) | 2001-02-28 | 2002-02-28 | Tissue electroperforation for enhanced drug delivery and sampling |
EP02721210A EP1365834A2 (en) | 2001-02-28 | 2002-02-28 | Tissue electroperforation for enhanced drug delivery and sampling |
JP2002567405A JP4216073B2 (en) | 2001-02-28 | 2002-02-28 | Tissue electroporation for improved drug delivery and diagnostic sampling |
CA002442567A CA2442567A1 (en) | 2001-02-28 | 2002-02-28 | Tissue electroperforation for enhanced drug delivery and sampling |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/795,908 | 2001-02-28 | ||
US09/795,908 US7133717B2 (en) | 1999-08-25 | 2001-02-28 | Tissue electroperforation for enhanced drug delivery and diagnostic sampling |
Publications (2)
Publication Number | Publication Date |
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WO2002068044A2 true WO2002068044A2 (en) | 2002-09-06 |
WO2002068044A3 WO2002068044A3 (en) | 2002-11-28 |
Family
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Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
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PCT/US2002/006101 WO2002068044A2 (en) | 2001-02-28 | 2002-02-28 | Tissue electroperforation for enhanced drug delivery and sampling |
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US (1) | US7133717B2 (en) |
EP (1) | EP1365834A2 (en) |
JP (1) | JP4216073B2 (en) |
AU (1) | AU2002252152A1 (en) |
CA (1) | CA2442567A1 (en) |
WO (1) | WO2002068044A2 (en) |
Cited By (1)
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EP2613725A1 (en) * | 2010-09-09 | 2013-07-17 | Old Dominion Univesity Research Foundation | Multi-electrode electrical pulse delivery system for treatment of biological tissues |
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EP2613725A1 (en) * | 2010-09-09 | 2013-07-17 | Old Dominion Univesity Research Foundation | Multi-electrode electrical pulse delivery system for treatment of biological tissues |
EP2613725A4 (en) * | 2010-09-09 | 2014-02-26 | Old Dominion Univesity Res Foundation | Multi-electrode electrical pulse delivery system for treatment of biological tissues |
US9872721B2 (en) | 2010-09-09 | 2018-01-23 | Old Dominion University Research Foundation | Multi-electrode electrical pulse delivery system for treatment of biological tissues |
US10881447B2 (en) | 2010-09-09 | 2021-01-05 | Old Dominion University Research Foundation | Multi-electrode electrical pulse delivery system for treatment of biological tissues |
Also Published As
Publication number | Publication date |
---|---|
WO2002068044A3 (en) | 2002-11-28 |
JP2004523308A (en) | 2004-08-05 |
JP4216073B2 (en) | 2009-01-28 |
CA2442567A1 (en) | 2002-09-06 |
EP1365834A2 (en) | 2003-12-03 |
US7133717B2 (en) | 2006-11-07 |
AU2002252152A1 (en) | 2002-09-12 |
US20020010414A1 (en) | 2002-01-24 |
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