US20050171574A1

US20050171574A1 - Electroporation to interrupt blood flow

Info

Publication number: US20050171574A1
Application number: US11/022,310
Authority: US
Inventors: Boris Rubinsky; Jon Edd; Liana Horowitz
Original assignee: University of California
Current assignee: University of California
Priority date: 2003-12-24
Filing date: 2004-12-21
Publication date: 2005-08-04
Also published as: JP5138229B2; US10117701B2; US20120071874A1; US8282631B2; EP1696812A2; ES2543832T3; JP2007516792A; AU2004311842A1; US9005189B2; AU2004311842C1; EP1696812B1; US20190046255A1; AU2010214761A1; WO2005065284A2; US20050171523A1; AU2010214761B2; PL1696812T3; DK1696812T3; EP2474281B1; US11033321B2

Abstract

A method for disrupting blood flow to undesirable tissue such as cells of a cancerous or non-cancerous tumor is disclosed. It involves the placement of electrodes into or near the vicinity of vessels supplying blood to the undesirable tissue and through the application of electrical pulses causing blood flow disruption. The electric pulses irreversibly permeate the cell membranes, thereby invoking cell death. The irreversibly permeabilized cells are left in situ and are removed by the body immune system. The process may further comprise monitoring blood flow and/or infusion of a material such as a chemotherapeutic agent or marker into the blood.

Description

CROSS-REFERENCE

This application claims the benefit of U.S. Provisional Application No. 60/532,588, filed Dec. 24, 2003, which application is incorporated herein by reference.

FIELD OF THE INVENTION

This invention relates to the field of electrode devices useful to disrupt blood flow in order to carry out treatments.

BACKGROUND OF THE INVENTION

In many medical procedures, such as the treatment of benign or malignant tumors, it is important to be able to ablate the undesirable tissue in a controlled and focused way without affecting the surrounding desirable tissue. Over the years, a large number of minimally invasive methods have been developed to selectively destroy specific areas of undesirable tissues as an alternative to resection surgery. There are a variety of techniques with specific advantages and disadvantages, which are indicated and contraindicated for various applications. For example, cryosurgery is a low temperature minimally invasive technique in which tissue is frozen on contact with a cryogen cooled probe inserted in the undesirable tissue (Rubinsky, B., ed. Cryosurgery. Annu. Rev. Biomed. Eng. Vol. 2. 2000. 157-187.). The area affected by low temperature therapies, such as cryosurgery, can be easily controlled through imaging. However, the probes are large and difficult to use. Non-selective chemical ablation is a technique in which chemical agents such as ethanol are injected in the undesirable tissue to cause ablation (Shiina, S., et al., Percutaneous ethanol injection therapy for hepatocellular carcinoma: results in 146 patients. AJR, 1993. 160: p. 1023-8). Non-selective chemical therapy is easy to apply. However, the affected area cannot be controlled because of the local blood flow and transport of the chemical species. Elevated temperatures are also used to ablate tissue. Focused ultrasound is a high temperature non-invasive technique in which the tissue is heated to coagulation using high-intensity ultrasound beams focused on the undesirable tissue (Lynn, J. G., et al., A new method for the generation of use of focused ultrasound in experimental biology. J. Gen Physiol., 1942. 26: p. 179-93; Foster, R. S., et al., High-intensity focused ultrasound in the treatment of prostatic disease. Eur. Urol., 1993. 23: p. 44-7). Electrical currents are also commonly used to heat tissue. Radiofrequency ablation (RF) is a high temperature minimally invasive technique in which an active electrode is introduced in the undesirable tissue and a high frequency alternating current of up to 500 kHz is used to heat the tissue to coagulation (Organ, L. W., Electrophysiological principles of radiofrequency lesion making. Appl. Neurophysiol., 1976. 39: p. 69-76). In addition to RF heating traditional Joule heating methods with electrodes inserted in tissue and dc or ac currents are also common, (Erez, A., Shitzer, A. (Controlled destruction and temperature distribution in biological tissue subjected to monoactive electrocoagulation) J. Biomech. Eng. 1980: 102(1): 42-9). Interstitial laser coagulation is a high temperature thermal technique in which tumors are slowly heated to temperatures exceeding the threshold of protein denaturation using low power lasers delivered to the tumors by optical fibers (Bown, S. G., Phototherapy of tumors. World. J. Surgery, 1983. 7: p. 700-9). High temperature thermal therapies have the advantage of ease of application. The disadvantage is the extent of the treated area is difficult to control because blood circulation has a strong local effect on the temperature field that develops in the tissue. The armamentarium of surgery is enhanced by the availability of the large number of minimally invasive surgical techniques in existence, each with their own advantages and disadvantages and particular applications. This document discloses another minimally invasive surgical technique for tissue ablation, irreversible electroporation. We will describe the technique, evaluate its feasibility through mathematical modeling and demonstrate the feasibility with in vivo experimental studies.
Electroporation is defined as the phenomenon that makes cell membranes permeable by exposing them to certain electric pulses (Weaver, J. C. and Y. A. Chizmadzhev, Theory of electroporation: a review. Bioelectrochem. Bioenerg., 1996. 41: p. 135-60). Electroporation pulses are defined as those electrical pulses that through a specific combination of amplitude, shape, time length and number of repeats produce no other substantial effect on biological cells than the permeabilization of the cell membrane. The range of electrical parameters that produce electroporation is bounded by: a) parameters that have no substantial effect on the cell and the cell membrane, b) parameters that cause substantial thermal effects (Joule heating) and c) parameters that affect the interior of the cell, e.g. the nucleus, without affecting the cell membrane. Joule heating, the thermal effect that electrical currents produce when applied to biological materials is known for centuries. It was noted in the previous paragraph that electrical thermal effects which elevate temperatures to values that damage cells are commonly used to ablate undesirable tissues. The pulse parameters that produce thermal effects are longer and/or have higher amplitudes than the electroporation pulses whose only substantial effect is to permeabilize the cell membrane.
There are a variety of methods to electrically produce thermal effects that ablate tissue. These include RF, electrode heating, and induction heating. Electrical pulses that produce thermal effects are distinctly different from the pulses which produce electroporation. The distinction can be recognizing through their effect on cells and their utility. The effect of the thermal electrical pulses is primarily on the temperature of the biological material and their utility is in raising the temperature to induce tissue ablation through thermal effects.
The effect of the electroporation parameters is primarily on the cell membrane and their utility is in permeabilizing the cell membrane for various applications. Electrical parameters that only affect the interior of the cell, without affecting the cell membrane were also identified recently. They are normally referred to as “nanosecond pulses”. It has been shown that high amplitude, and short (substantially shorter than electroporation pulses—nanoseconds versus millisecond) length pulses can affect the interior of the cell and in particular the nucleus without affecting the membrane. Studies on nanosecond pulses show that they are “distinctly different than electroporation pulses” (Beebe S J. Fox P M. Rec L J. Somers K. Stark R H. Schoenbach K H. Nanosecond pulsed electric field (nsPEF) effects on cells and tissues: apoptosis induction and tumor growth inhibition. PPPS-2001 Pulsed Power Plasma Science 2001. 28th IEEE International Conference on Plasma Science and 13th IEEE International Pulsed Power Conference. Digest of Technical Papers (Cat. No. 01 CH37251). IEEE. Part vol. 1, 2001, pp. 211-15 vol. 1. Piscataway, N.J., USA. Several applications have been identified for nano-second pulses. One of them is for tissue ablation through an effect on the nucleus (Schoenbach, K. H., Beebe, S. J., Buescher, K. S. Method and apparatus for intracellular electro-manipulation U.S. Patent Application Pub No. US 2002/0010491 A1, Jan. 24, 2002). Another is to regulate genes in the cell interior, (Gunderson, M. A. et al. Method for intracellular modification within living cells using pulsed electrical fields—regulate gene transcription and entering intracellular U.S. Patent application 2003/0170898 A1, Sep. 11, 2003). Electrical pulses that produce intracellular effects are distinctly different from the pulses which produce electroporation. The distinction can be recognizing through their effect on cells and their utility. The effect of the intracellular electrical pulses is primarily on the intracellular contents of the cell and their utility is in manipulating the intracellular contents for various uses—including ablation. The effect of the electroporation parameters is primarily on the cell membrane and their utility is in permeabilizing the cell membrane for various applications, which will be discussed in greater detail later.
Electroporation is known for over half a century. It was found that as a function of the electrical parameters, electroporation pulses can have two different effects on the permeability of the cell membrane. The permeabilization of the membrane can be reversible or irreversible as a function of the electrical parameters used. In reversible electroporation the cell membrane reseals a certain time after the pulses cease and the cell survives. In irreversible electroporation the cell membrane does not reseal and the cell lyses. A schematic diagram showing the effect of electrical parameters on the cell membrane permeabilization (electroporation) and the separation between: no effect, reversible electroporation and irreversible electroporation is shown in FIG. 1 (Dev, S. B., Rabussay, D. P., Widera, G., Hofmann, G. A., Medical applications of electroporation, IEEE Transactions of Plasma Science, Vol 28 No 1, February 2000, pp 206-223) Dielectric breakdown of the cell membrane due to an induced electric field, irreversible electroporation, was first observed in the early 1970s (Neumann, E. and K. Rosenheck, Permeability changes induced by electric impulses in vesicular membranes. J. Membrane Biol., 1972. 10: p. 279-290; Crowley, J. M., Electrical breakdown of biomolecular lipid membranes as an electromechanical instability. Biophysical Journal, 1973. 13: p. 711-724; Zimmermann, U., J. Vienken, and G. Pilwat, Dielectric breakdown of cell membranes. Biophysical Journal, 1974. 14(11): p. 881-899). The ability of the membrane to reseal, reversible electroporation, was discovered separately during the late 1970s (Kinosita Jr, K. and T. Y. Tsong, Hemolysis of human erythrocytes by a transient electric field. Proc. Natl. Acad. Sci. USA, 1977. 74(5): p. 1923-1927; Baker, P. F. and D. E. Knight, Calcium-dependent exocytosis in bovine adrenal medullary cells with leaky plasma membranes. Nature, 1978. 276: p. 620-622; Gauger, B. and F. W. Bentrup, A Study of Dielectric Membrane Breakdown in the Fucus Egg, J. Membrane Biol., 1979. 48(3): p. 249-264).
The mechanism of electroporation is not yet fully understood. It is thought that the electrical field changes the electrochemical potential around a cell membrane and induces instabilities in the polarized cell membrane lipid bilayer. The unstable membrane then alters its shape forming aqueous pathways that possibly are nano-scale pores through the membrane, hence the term “electroporation” (Chang, D. C., et al., Guide to Electroporation and Electrofusion. 1992, San Diego, Calif.: Academic Press, Inc.). Mass transfer can now occur through these channels under electrochemical control. Whatever the mechanism through which the cell membrane becomes permeabilized, electroporation has become an important method for enhanced mass transfer across the cell membrane.
The first important application of the cell membrane permeabilizing properties of electroporation is due to Neumann (Neumann, E., et al., Gene transfer into mouse lyoma cells by electroporation in high electric fields. J. EMBO, 1982. 1: p. 841-5). He has shown that by applying reversible electroporation to cells it is possible to sufficiently permeabilize the cell membrane so that genes, which are macromolecules that normally are too large to enter cells, can after electroporation enter the cell. Using reversible electroporation electrical parameters is crucial to the success of the procedure, since the goal of the procedure is to have a viable cell that incorporates the gene.
Following this discovery electroporation became commonly used to reversible permeabilize the cell membrane for various applications in medicine and biotechnology to introduce into cells or to extract from cells chemical species that normally do not pass, or have difficulty passing across the cell membrane, from small molecules such as fluorescent dyes, drugs and radioactive tracers to high molecular weight molecules such as antibodies, enzymes, nucleic acids, HMW dextrans and DNA. It is important to emphasize that in all these applications electroporation needs to be reversible since the outcome of the mass transport requires for the cells to be alive after the electroporation.
Following work on cells outside the body, reversible electroporation began to be used for permeabilization of cells in tissue. Heller, R., R. Gilbert, and M. J. Jaroszeski, Clinical applications of electrochemotherapy. Advanced drug delivery reviews, 1999. 35: p. 119-129. Tissue electroporation is now becoming an increasingly popular minimally invasive surgical technique for introducing small drugs and macromolecules into cells in specific areas of the body. This technique is accomplished by injecting drugs or macromolecules into the affected area and placing electrodes into or around the targeted tissue to generate reversible permeabilizing electric field in the tissue, thereby introducing the drugs or macromolecules into the cells of the affected area (Mir, L. M., Therapeutic perspectives of in vivo cell electropermeabilization. Bioelectrochemistry, 2001. 53: p. 1-10).
The use of electroporation to ablate undesirable tissue was introduced by Okino and Mohri in 1987 and Mir et al. in 1991. They have recognized that there are drugs for treatment of cancer, such as bleomycin and cys-platinum, which are very effective in ablation of cancer cells but have difficulties penetrating the cell membrane. Furthermore, some of these drugs, such as bleomycin, have the ability to selectively affect cancerous cells which reproduce without affecting normal cells that do not reproduce. Okino and Mori and Mir et al. separately discovered that combining the electric pulses with an impermeant anticancer drug greatly enhanced the effectiveness of the treatment with that drug (Okino, M. and H. Mohri, Effects of a high-voltage electrical impulse and an anticancer drug on in vivo growing tumors. Japanese Journal of Cancer Research, 1987. 78(12): p. 1319-21; Mir, L. M., et al., Electrochemotherapy potentiation of antitumour effect of bleomycin by local electric pulses. European Journal of Cancer, 1991. 27: p. 68-72). Mir et al. soon followed with clinical trials that have shown promising results and coined the treatment electrochemotherapy (Mir, L. M., et al., Electrochemotherapy, a novel antitumor treatment: first clinical trial. C. R. Acad. Sci., 1991. Ser. III 313(613-8)).
Currently, the primary therapeutic in vivo applications of electroporation are antitumor electrochemotherapy (ECT), which combines a cytotoxic nonpermeant drug with permeabilizing electric pulses and electrogenetherapy (EGT) as a form of non-viral gene therapy, and transdermal drug delivery (Mir, L. M., Therapeutic perspectives of in vivo cell electropermeabilization. Bioelectrochemistry, 2001. 53: p. 1-10). The studies on electrochemotherapy and electrogenetherapy have been recently summarized in several publications (Jaroszeski, M. J., et al., In vivo gene delivery by electroporation. Advanced applications of electrochemistry, 1999. 35: p. 131-137; Heller, R., R. Gilbert, and M. J. Jaroszeski, Clinical applications of electrochemotherapy. Advanced drug delivery reviews, 1999. 35: p. 119-129; Mir, L. M., Therapeutic perspectives of in vivo cell electropermeabilization. Bioelectrochemistry, 2001. 53: p. 1-10; Davalos, R. V., Real Time Imaging for Molecular Medicine through electrical Impedance Tomography of Electroporation, in Mechanical Engineering. 2002, University of California at Berkeley: Berkeley. p. 237). A recent article summarized the results from clinical trials performed in five cancer research centers. Basal cell carcinoma (32), malignant melanoma (142), adenocarcinoma (30) and head and neck squamous cell carcinoma (87) were treated for a total of 291 tumors (Mir, L. M., et al., Effective treatment of cutaneous and subcutaneous malignant tumours by electrochemotherapy. British Journal of Cancer, 1998. 77(12): p. 2336-2342).
Electrochemotherapy is a promising minimally invasive surgical technique to locally ablate tissue and treat tumors regardless of their histological type with minimal adverse side effects and a high response rate (Dev, S. B., et al., Medical Applications of Electroporation. IEEE Transactions on Plasma Science, 2000. 28(1): p. 206-223; Heller, R., R. Gilbert, and M. J. Jaroszeski, Clinical applications of electrochemotherapy. Advanced drug delivery reviews, 1999. 35: p. 119-129). Electrochemotherapy, which is performed through the insertion of electrodes into the undesirable tissue, the injection of cytotoxic dugs in the tissue and the application of reversible electroporation parameters, benefits from the ease of application of both high temperature treatment therapies and non-selective chemical therapies and results in outcomes comparable of both high temperature therapies and non-selective chemical therapies.
In addition, because the cell membrane permeabilization electrical field is not affected by the local blood flow, the control over the extent of the affected tissue by this mode of ablation does not depend on the blood flow as in thermal and non-selective chemical therapies. In designing electroporation protocols for ablation of tissue with drugs that are incorporated in the cell and function in the living cells it was important to employ reversible electroporation; because the drugs can only function in a living cell. Therefore, in designing protocols for electrochemotherapy the emphasize was on avoiding irreversible electroporation. The focus of the entire field of electroporation for ablation of tissue was on using reversible pulses, while avoiding irreversible electroporation pulses, that can cause the incorporation of selective drugs in undesirable tissue to selectively destroy malignant cells. Electrochemotherapy which employs reversible electroporation in combination with drugs, is beneficial due to its selectivity however, a disadvantage is that by its nature, it requires the combination of chemical agents with an electrical field and it depends on the successful incorporation of the chemical agent inside the cell.
An important concern in the studies of electrochemotherapy and electrogenetherapy in living tissue is the effect of electroporation on blood flow. Martin et al., have found that when reversible electroporation is used for introducing genes into cells on the blood vessel wall the blood vessels remain intact and their response to stimuli where indistinguishable from those of control vessels (Martin, J. B., Young, J. L., Benoit, J. N., Dean, D. A., Gene transfer to intact Mesenteric arteries by electroporation, Journal of vascular research, 2000, Vol 37: 372-380). Ivanusa et al have found using MRI that with certain electroporation pulses, which appear to be in the irreversible electroporation range, that the electroporation transiently but significantly reduced tumor blood flow (Ivanusa, T., Beravs, K., Cemazar, M, Jevtic, V., Demsar, F., Sersa, G. MRI macromolecular contrast agents as indicators of changed tumor blood flow, Radiol. Oncol. 2001; 35(2): 139-47). These findings are very different from those described here.
Sersa et al performed studies whose goal was to determine the effect of electrochemotherapy, reversible elctroporation with bleomycin or cisplatin, on tumor blood flow (Sersa, G., Sentjurc, M., Ivanusa, T., Beravs, K, Kotnik, V., Coer, A., Swartz, H. M., Cemazar, M Reduced blood flow and axygenation in SA-1 tumours after electrochemotherapy with cisplatin, Br. J. Cancer, 2002: 87(9): 1047-54) (Sersa, G., Cemazar, M, Miklavcic, D. Tumor blood flow modifying effects of electrochemotherapy: a potential targeted mechanism radiol. Oncol 2003: 37(1): 43-8). In the first of the papers they report reduced blood flow that persisted for several days when using reversible electroporation with cisplatin. In the second paper they report complete shut down of blood flow after 24 hours when using reversible electroporation with bleomycin and 50% reduction in blood flow when using reversible electroporation with cisplatin.
The present inventors have found through histological analysis of electroporated tissue that in regions of tissue which are irreversible electroporated the local blood flow completely ceases, whereas outside that area the blood flow is not affected. This has the effect of local blood flow cessation and the appearance of global blood flow reduction. The applications of local blood flow cessation with irreversible electroporation are disclosed and described here.
Irreversible electroporation has been considered detrimental to conventional electrochemotherapy. However, the present invention shows that it can be used to disrupt blood flow. Once blood flow to an area is stopped the cells in that area die. Thus, the method can be used in various treatments as described here.

SUMMARY OF THE INVENTION

The present invention comprises a method for disrupting blood flow, involving the placement of electrodes into or near the vicinity where the undesirable flow of blood is occurring and using the electrodes to provide electrical pulses. The length of time of the electrical pulses, the voltage applied and the resulting membrane permeability are all controlled within defined ranges. The invention may further comprise monitoring blood flow in a specific area and determining desired results have been achieved once the flow being monitored has been determined to have stopped flowing. Cells which have been deprived of blood flow die and may be left in situ and may be removed by natural processes such as the body's own immune system. The invention may further comprise infusing a material such as a chemotherapeutic agent and/or a marker in blood prior to interrupting blood flow. Such may be timed to trap the material in a targeted cite and may be used to ablate tumor cells.
This concept of disrupting blood flow via irreversible electroporation is different from other forms of electrical therapies and treatments. Irreversible electroporation is different from intracellular electro-manipulation which substantially only affects the interior of the cell and does not cause irreversible cell membrane damage. Irreversible electroporation is not electrically induced thermal coagulation—which induces cell damage through thermal effects but rather a more benign method to destroy only the cell membrane of cells in the targeted tissue. Irreversible electroporation which irreversible destroys the cell membrane is also different from electrochemotherapy in which reversible electroporation pulses are used to introduce drugs into the living cells and in which the drugs subsequently affect the living cell.
An electrical pulse can either have no effect on the cell membrane, effect internal cell components, reversibly open the cell membrane after which cells can survive, or irreversibly open the cell membrane. When the membrane of a cell is irreversibly opened the cell dies. When a sufficient number of cells in an area are killed (e.g. blood vessel cells) blood flow to that area is disrupted. When blood flow to other cells is disrupted those cells die. Others have generally considered irreversible electroporation of tissue to be undesirable due to the possibility of instantaneous necrosis of the entire tissue affected by the electrical field, regardless of its diseased or healthy state. Irreversible electroporation is detrimental in certain applications, such as gene therapy or electrochemotherapy, where the sole purpose of the electric pulses is to facilitate the introduction of the drug or gene into the cells of a tissue without killing the cell (Mir, L. M. and S. Orlowski, The basis of electrochemotherapy, in Electrochemotherapy, electrogenetherapy, and transdermal drug delivery: Electrically mediated delivery of molecules to cells, M. J. Jaroszeski, R. Heller, R. Gilbert, Editors, 2000, Humana Press, p. 99-118).
In contrast, irreversible electroporation to disrupt blood flow can provide useful treatments. The method is carried out using electrical pulses to serve as the active means for tissue destruction by a specific means, i.e. by fatally disrupting the cell membrane. Electrochemotherapy may be selective, but it does require the combination of chemical agents with the electrical field. Irreversible electroporation to disrupt blood flow, although non-selective, may be used to stop bleeding or for the ablation of undesirable tissue (such as a tumor) as a minimally invasive surgical procedure with or without the use of adjuvant drugs. Its non-selective mode of tissue ablation is acceptable in the field of minimally invasive surgery and provides results which in some ways are comparable to cryosurgery, non-selective chemical ablation and high temperature thermal ablation.
An aspect of the invention is a method whereby blood flow is disrupted by applying pulses of very precisely determined length and voltage. This may be done while measuring and/or observing changes in electrical impedance in real time and noting decreases at the onset of electroporation and adjusting the current in real time to obtain irreversible cellular damage without thermal damage. In embodiments where voltage is applied, the monitoring of the impedance affords the user knowledge of the presence or absence of pores. This measurement can show the progress of the pore formation and indicate the occurrence of irreversible pore formation, leading to cell death and blood flow disruption.
An aspect of this invention is that the onset and extent of electroporation of cells in tissue can be correlated to changes in the electrical impedance (which term is used herein to mean the voltage over current) of the tissue. At a given point, the electroporation becomes irreversible. A decrease in the resistivity of a group of biological cells occurs when membranes of the cells become permeable due to pore formation. By monitoring the impedance of the biological cells in a tissue, one can detect the average point in time in which pore formation of the cells occurs, as well as the relative degree of cell membrane permeability due to the pore formation. By gradually increasing voltage and testing cells in a given tissue one can determine a point where irreversible electroporation occurs and at which blood flow is disrupted. This information can then be used to establish that, on average, the cells of the tissue have, in fact, undergone irreversible electroporation and blood flow has been disrupted. This information can also be used to control the electroporation process and thereby control blood flow by governing the selection of the voltage magnitude.
The invention provides the simultaneous irreversible electroporation of multitudes of cells providing a direct indication of the actual occurrence of electroporation and an indication of the degree of electroporation averaged over the multitude sufficient to disrupt blood flow. The discovery is likewise useful in the irreversible electroporation of cells which make-up vessels and of cells in blood. The benefits of this process include a high level of control over the beginning point of irreversible electroporation and the control of blood flow to and out of very specific areas.
A feature of the invention is that the magnitude of electrical current during electroporation of the tissue becomes dependent on the degree of electroporation so that current and pulse length are adjusted within a range predetermined to obtain irreversible electroporation of targeted cells of the blood and blood vessels while minimizing cellular damage to surrounding cells and tissue.
An aspect of the invention is that pulse length and current are precisely adjusted within ranges to provide more than mere intracellular electro-manipulation which results in cell death and less than that which would cause thermal damages to the surrounding tissues.
Another aspect of the invention is that the electroporation may be carried out with or without adding drugs or other materials of any sort to the blood.
Another aspect of the invention is monitoring blood flow into and/or out of an area and adjusting any or all of current, voltage, pulse length or number of pulses in real time to obtain a residual degree of blood flow restriction into or out of the area.
Another aspect of the invention comprises infusion of a drug and/or image marking agent into blood and then disrupting blood flow to a targeted area so that the drug and/or image marker are trapped in the targeted area.
Another aspect of the invention is measuring blood flow in real time provides an indirect indication of electroporation of a targeted area.
Another feature of the invention is that measuring current and/or blood flow (in real time) through a circuit gives a measurement of the average overall degree of electroporation obtained.
Another aspect of the invention is that the precise electrical resistance of the tissue is calculated from cross-time voltage measurement with probe electrodes and cross-current measurement with the circuit attached to electroporation electrodes.
Another aspect of the invention is that the precise electrical resistance of the tissue is calculated from cross-time voltage measurement with probe electrodes and cross-current measurement with the circuit attached to electroporation electrodes.
Another aspect of the invention is that electrical measurements of the tissue can be used to map the electroporation and blood flow distribution of the tissue.
Unlike electrical impedance tomography or detection of reversible electroporation which needs to be done during or close to the time the reversible electroporation pulses are applied—because of the transient nature of the reversible electroporation; in reversible electroporation it is possible and perhaps even preferential to perform the current or EIT measurements a substantial time (several minutes or more) after the electroporation to verify that it is indeed irreversible.
Another aspect of the invention is treating cancer by infusing a chemotherapeutic agent into blood, and applying current pulses as described here to disrupt blood flow and thereby trap the chemotherapeutic agent in a target area.
Yet another aspect of the invention is infusing a higher than normal concentration of a chemotherapeutic agent into a blood vessel immediately upstream of a targeted area and applying current when the agent reached the targeted area to disrupt blood flow and trap the agent in the tumor.
Still another aspect of the invention is to infuse a marker molecule with a chemotherapeutic agent into a blood vessel upstream of a targeted area followed by current application sufficient to disrupt flow when the marker is determined to be at the targeted area.
In another aspect of the invention an organ is flushed such as with normal saline solution, then fixed, and thereafter subjected to histology to examine the effects of prior irreversible electroporation on cells of that organ.
These and further features, advantages and objects of the invention will be better understood from the description that follows.

BRIEF DESCRIPTION OF THE DRAWINGS

The invention is best understood from the following detailed description when read in conjunction with the accompanying drawings. It is emphasized that, according to common practice, the various features of the drawings are not to scale. On the contrary, the dimensions of the various features are arbitrarily expanded or reduced for clarity. Included in the drawings are the following figures:
FIG. 1. is a graph showing a schematic relationship between field strength and pulselength applicable to the electroporation of cells.
FIGS. 2A, 2B and 2C are each images of irreversibly electroporated areas for two-electrode configurations using 10 mm center-to-center spacing as following for FIGS. 2A, B and C: (2A) 0.5 mm (857V); (2B) 1.0 mm (1295V); (2C) 1.5 mm (1575V) diameter electrodes with a 680V/cm threshold for irreversible electroporation.
FIGS. 3A, 3B, and 3C are images showing irreversibly electroporated regions using a 680 V/cm threshold for a two-electrode confirmation with 1 mm diameter and 876V and 5 mm spacing for FIGS. 3A; 1116V and 7.5 mm for FIG. 3B; and 1295V and 10 mm spacing for FIG. 3C.
FIGS. 4A, 4B and 4C are images showing the effect of electrode diameter for a 4-electrode configuration with 10 mm spacing wherein FIG. 4A is for 0.5 mm diameter and 940V; FIG. 4B is for 1.0 mm diameter and 1404V and FIG. 4C is for 1.5 mm and 1685V.
FIGS. 5A, 5B and 5C are images showing the effect of electrode spacing for a 4-electrode configuration wherein the electrode is 1 mm in diameter and FIG. 5A shows results with a 5 mm and 910V; FIG. 5B 7.5 mm and 1175V and FIG. 5C 10 mm and 1404V.
FIG. 6 is an image showing the irreversible (1295V, 680V/cm threshold) as compared to the reversible region (1300V, 360V/cm threshold) using virtually the same electrical parameters. 1300V is the most common voltage applied across two electrodes for ECT. The most common voltage parameters are eight 100 μs pulses at a frequency of 1 Hz. Applying a single 800 μs pulse provides a conservative estimate of the heating associated with a procedure. The one second space normally between pulses will enlarge an area amount of heat to be dissipated through the tissue.
FIG. 7 is an image showing reversible electroporation with 1 mm electrodes, 10 mm spacing. A voltage of 189V applied between the electrodes induces reversible electroporation without any irreversible electroporation by not surpassing the 680V/cm irreversible electroporation threshold anyone in the domain. The shaded area is greater than 360 V/cm.
FIGS. 8A and 8B show a comparison of the effect of blood flow and metabolism on the amount of irreversible electroporation. FIG. 8A no blood flow or metabolism. FIG. 8B w_b=1 kg/m³, c_b=3640 J/(kg K), T_b=37° C., and q′″=33.8 kW/m³.
FIG. 9 is a schematic view of a liver between two cylindrical Ag/AgCl electrodes. The distance between the electrodes was 4 mm and the radius of the electrodes is 10 mm. The electrodes were clamped with special rig parallel and concentric to each other. The liver lobe was compressed between the electrodes to achieve good contact.
FIG. 10 is a photo of a view of a liver which was electroporated by irreversible electroporation with two cylindrical surface electrodes of 10 mm in diameter. Histology shows that the dark area is necrotic.
FIG. 11 is a photo of a cross section through an electroporated liver. Histology shows that the dark area is necrotic. The distance between the two A1 plates that hold the liver is exactly 4 mm. The electroporation electrodes were 10 mm in diameter and centered in the middle of the lesion.
FIG. 12 shows the liver of calculated temperature distribution (C), upper panel, and electrical potential gradient (electroporation gradient) (V/cm), lower panel, for the in vivo experiment. The FIG. 12 also shows conditions through a cross section of a liver slab through the center of the electroporated area. Height of the slab is 4 mm.
FIG. 13 combines FIGS. 11 and 12 to show a comparison between the extent of tissue necrosis (dark area) and the temperature and voltage gradient distribution in the electroporated tissue. It is evident that most of the dark area was at a temperature of about 42 C following the 40 milliseconds electroporation pulse. The edge of the dark area seems to correspond to the 300 V/cm electroporation gradient line.
FIG. 14 is a photo of a micrograph of the interface between irreversible electroporated liver and normal liver. The left hand side shows normal hepatocytes with clear nucleus and nuclei, well defined cell membrane and clean (flushed) sinusoids. The right hand side shows condensed nuclei, no evidence of cell membrane, expanded cell border with no evidence of sinusoids. Disintegrated red blood cells are in what could have been the spaces of the sinusoids. No effect of flushing.

DETAILED DESCRIPTION OF THE INVENTION

Before the present methods, treatments and devices are described, it is to be understood that this invention is not limited to particular embodiments described, as such may, of course, vary. It is also to be understood that the terminology used herein is for the purpose of describing particular embodiments only, and is not intended to be limiting, since the scope of the present invention will be limited only by the appended claims.
Where a range of values is provided, it is understood that each intervening value, to the tenth of the unit of the lower limit, unless the context clearly dictates otherwise, between the upper and lower limits of that range is also specifically disclosed. Each smaller range between any stated value or intervening value in a stated range and any other stated or intervening value in that stated range is encompassed within the invention. The upper and lower limits of these smaller ranges may independently be included or excluded in the range, and each range where either, neither or both limits are included in the smaller ranges is also encompassed within the invention, subject to any specifically excluded limit in the stated range. Where the stated range includes one or both of the limits, ranges excluding either or both of those included limits are also included in the invention.
Unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs. Although any methods and materials similar or equivalent to those described herein can be used in the practice or testing of the present invention, the preferred methods and materials are now described. All publications mentioned herein are incorporated herein by reference to disclose and describe the methods and/or materials in connection with which the publications are cited. The present disclosure is controlling to the extent it conflicts with any incorporated publication.
It must be noted that as used herein and in the appended claims, the singular forms “a”, “an”, and “the” include plural referents unless the context clearly dictates otherwise. Thus, for example, reference to “a pulse” includes a plurality of such pulses and reference to “the sample” includes reference to one or more samples and equivalents thereof known to those skilled in the art, and so forth.
The publications discussed herein are provided solely for their disclosure prior to the filing date of the present application. Nothing herein is to be construed as an admission that the present invention is not entitled to antedate such publication by virtue of prior invention. Further, the dates of publication provided may be different from the actual publication dates which may need to be independently confirmed.

Definitions

The term “reversible electroporation” encompasses permeabilization of the cell membrane through the application of electrical pulses across the cell. In “reversible electroporation” the permeabilization of the cell membrane ceases after the application of the pulse and the cell membrane permeability reverts to normal. The cell survives “reversible electroporation.” It is used as a means for introducing chemicals, DNA, or other materials into cells.
The term “irreversible electroporation” also encompasses the permeabilization of the cell membrane through the application of electrical pulses across the cell. However, in “irreversible electroporation” the permeabilization of the cell membrane does not cease after the application of the pulse and the cell membrane permeability does not revert to normal. The cell does not survive “irreversible electroporation” and the cell death is caused by the disruption of the cell membrane and not merely by internal perturbation of cellular components. Openings in the cell membrane are created and/or expanded in size resulting in a fatal disruption in the normal controlled flow of material across the cell membrane. The cell membrane is highly specialized in its ability to regulate what leaves and enters the cell. Irreversible electroporation destroys that ability to regulate in a manner such that the cell can not compensate and as such the cell dies.

Invention in General

The present invention is a result of the new finding that: a) irreversible electroporation can cause permanent occlusion of certain blood vessels, b) it can cause disintegration and trapping of cells in the area that was irreversible electroporated and c) it can also cause trapping of any kind of compound present at that location at the instant of irreversible electroporation in the region that was electroporated.
The discovery that with irreversible electroporation the occlusion of blood flow in the irreversible electroporated area is permanent has important applications as described below.
Irreversible electroporation may be used to occlude blood flow and blood supply in an undesirable region of tissue so as to induce cell death by ischemia in the region that was irreversible electroporated. This is substantially different from other uses of electrical pulses for tissue ablation which are for the destruction of individual cells and which do not address blood vessels. The advantage of using irreversible electroporation to occlude blood flow is that cell death by ischemia is absolute over the entire region in which blood ceases to flow—while cell destruction by electroporation needs to address each cell individually and may suffer from a statistical probability that some cells may survive. Occlusion of blood flow and induction of ischemia by chemical methods has been considered as a method for the treatment of cancer. Irreversible electroporation provides a very efficient method for occluding blood flow without the need for chemicals.
FIG. 14 shows that red blood cells have become trapped and disintegrated in the irreversible electroporation area. This shows that drugs may be loaded in vesicles or liposomes (a standard method for drug delivery) and the irreversible electroporation can cause the vesicles to disintegrate in the electroporated region. This provides for the delivery of a drug directly to that region.
The results provided here also show that there is no blood flow in the irreversible electroporated region which shows that drugs which are injected systemically in the body blood flow circulation would be entrapped in the irreversible electroporation. These drugs could be designed to produce long term effects. Further, the drugs could be in controlled release formulations and be slowly delivered to the tissue surrounding the electroporated area as well as to cells in the electroporated area. Drugs trapped in this manner would not be washed out of the body through the kidneys or metabolized by the liver and therefore would have a long term effect. The drugs could be for destruction of cancer and they could act on possible cancer cells that have survive in the electroporated zone or the area immediately surrounds this area. It should be emphasized that the drugs discussed here are substantially different from those used in rreversible electroporation. More specifically, drugs used in reversible electroporation are restricted to those that normally cannot easily penetrate the cell membrane and the reversible electroporation is used to introduce these drugs in the cells. The typical drugs are bleomycin an Cis-platinum. Using blood flow occlusion with irreversible electroporation allows any kind of drug to be employed because the mechanism for using the drugs is different. Here we do not promote the transport of the drug across the cell membrane but rather the retention of the drug in the irreversible electroporated area for long periods of time. This, for instance, would allow the injection in the local blood stream or the interstitial tissue in the area of the tissue to be ablated of extremely high concentrations of a drug. Such high concentrations would be very detrimental to the body if injected systemically. The irreversible electroporation traps the drugs and allows them to be released slowly through the diffusion process, in the area in which they are most needed. The process of diffusion is substantially slower than the convection by blood.
Another method to utilize the blood occlusion for delivery of drugs is to inject after the irreversible electroporation in the electroporated region the drug. The blood occlusion will ensure that the drug is trapped in this area.
In addition to drugs other types of chemicals or additives can be trapped inside the irreversible electroporated region. An important application compresses the use of imaging markers—such as gadolinium for MRI or markers for ultrasound or CT. These markers are injected and used to image the area that was irreversible electroporated using any imaging technique relevant to the markers and/or area.
The invention provides a method and a system for blood flow disruption to a targeted area resulting in destruction (ablation) of undesirable tissue in the targeted area. One embodiment of the invention involves the insertion (bringing) electroporation electrodes to the vicinity of the undesirable tissue and in good electrical contact with the tissue and the application of electrical pulses that cause irreversible electroporation of the cells throughout the entire area of the undesirable tissue. In another embodiment a blood vessel or group of blood vessels are targeted at a point or points immediately upstream of a flow of blood to an area of undesired tissue. By disrupting blood flow through the vessel or vessels the cells of the tissue of the targeted area are killed even without directly subjecting cells of the undesired tissue to irreversible electroporation. The cells whose membrane was irreversible permeabilized as well as those whose blood supply has been disrupted may be left in situ (not removed) and as such may be gradually removed by the body's immune system. Cell death is produced by inducing the electrical parameters of irreversible electroporation in the undesirable area.
Electroporation protocols involve the generation of electrical fields in tissue and are affected by the Joule heating of the electrical pulses. When designing tissue electroporation protocols it is important to determine the appropriate electrical parameters that will maximize tissue permeabilization without inducing deleterious thermal effects. It has been shown that substantial volumes of tissue can be electroporated with reversible electroporation without inducing damaging thermal effects to cells and has quantified these volumes (Davalos, R. V., B. Rubinsky, and L. M. Mir, Theoretical analysis of the thermal effects during in vivo tissue electroporation. Bioelectrochemistry, 2003. Vol 61(1-2): p. 99-107). In accordance with the present invention unwanted thermal damage can be further reduced. This can be accomplished by applying current to a smaller area and disrupting blood flow to a larger area and thereby ablating tissue in the larger area which is deprived of blood flow.
The electrical pulses required to induce irreversible electroporation in tissue are larger in magnitude and duration from the electrical pulses required for reversible electroporation. Further, the duration and strength of the pulses required for irreversible electroporation are different from other methodologies using electrical pulses such as for intracellular electro-manipulation or thermal ablation. The methods are very different even when the intracellular (nano-seconds) electro-manipulation is used to cause cell death, e.g. ablate the tissue of a tumor or when the thermal effects produce damage to cells causing cell death.
Typical values for pulse length for irreversible electroporation are in a range of from about 5 microseconds to about 62,000 milliseconds or about 75 microseconds to about 20,000 milliseconds or about 100 microseconds±10 microseconds. This is significantly longer than the pulse length generally used in intracellular (nano-seconds) electro-manipulation which is 1 microsecond or less—see published U.S. application 2002/0010491 published Jan. 24, 2002.
The pulse is at voltage of about 100 V/cm to 7,000 V/cm or 200 V/cm to 2000 V/cn or 300V/cm to 1000 V/cm about 600 V/cm±10% for irreversible electroporation. This is substantially lower than that used for intracellular electro-manipulation which is about 10,000 V/cm, see U.S. application 2002/0010491 published Jan. 24, 2002.
The voltage expressed above is the voltage gradient (voltage per centimeter). The electrodes may be different shapes and sizes and be positioned at different distances from each other. The shape may be circular, oval, square, rectangular or irregular etc. The distance of one electrode to another may be 0.5 to 10 cm., 1 to 5 cm., or 2-3 cm. The electrode may have a surface area of 0.1-5 sq. cm. or 1-2 sq. cm.
The size, shape and distances of the electrodes can vary and such can change the voltage and pulse duration used. Those skilled in the art will adjust the parameters in accordance with this disclosure to obtain the desired degree of electroporation and avoid thermal damage to surrounding cells.
Thermal effects require electrical pulses that are substantially longer from those used in irreversible electroporation (Davalos, R. V., B. Rubinsky, and L. M. Mir, Theoretical analysis of the thermal effects during in vivo tissue electroporation. Bioelectrochemistry, 2003. Vol 61(1-2): p. 99-107). FIG. 1 is showing that irreversible electroporation pulses are longer and have higher amplitude than the reversible electroporation pulses. When using irreversible electroporation for tissue ablation, there may be concern that the irreversible electroporation pulses will be as large as to cause thermal damaging effects to the surrounding tissue and the extent of the tissue ablated by irreversible electroporation will not be significant relative to that ablated by thermal effects. Under such circumstances irreversible electroporation could not be considered as an effective tissue ablation modality as it will act in superposition with thermal ablation. To a degree, this problem is addressed via the present invention. Specifically, blood vessels supplying blood to a tumor can be targeted. When the flow is disrupted the tumor cells die even when the tumor cells themselves may not have been subjected to irreversible electroporation.
The present invention evaluates, through mathematical models and experiment, the maximal extent of tissue ablation that could be accomplished by irreversible electroporation prior to the onset of thermal effects. The models focused on electroporation of liver tissue with two and four needle electrodes and on electroporation of liver tissue with two infinite parallel plates using available experimental data. The experiment (EXAMPLE 3) evaluates irreversible electroporation between two cylindrical electrodes, also in the liver. The liver was chosen because it is considered a potential candidate for irreversible electroporation ablation. The results show that the area that can be ablated by irreversible electroporation prior to the onset of thermal effects is comparable to that which can be ablated by electrochemotherapy, validating the use of irreversible electroporation as a potential minimally invasive surgical modality.
The results obtained by disrupting blood flow to a given area are dramatically shown in FIG. 14 which is a photo of a micrograph. This micrograph is from the interface between irreversible electroporated liver and normal liver. The left hand side shows normal hepatocytes with clear nucleus and nuclei. The photo shows well defined cell membranes and clean (flushed) sinusoids. The right hand side of FIG. 14 shows condensed nuclei, no evidence of cell membrane, expanded cell border with no evidence of sinusoids. The disintegrated red blood cells shown in FIG. 14 are in what could have been the spaces of the sinusoids. Flushing is not believed to have had an effect on the results obtained on the right hand side of FIG. 14.
Earlier studies have shown that the extent of electroporation can be imaged in real time with electrical impedance tomography (EIT) (Davalos, R. V., B. Rubinsky, and D. M. Otten, A feasibility study for electrical impedance tomography as a means to monitor tissue electroporation for molecular medicine. IEEE Transactions on Biomedical Engineering, 2002. 49(4): p. 400-403). In irreversible electroporation the electroporated area persists indefinitely after the electroporation pulse, showing that irreversible electroporation may be imaged leisurely with EIT. Irreversible electroporation, therefore, has the advantage of a tissue ablation technique that is as easy to apply as high temperature ablation, without the need for adjuvant chemicals as electrochemotherapy and with real-time control of the affected area with electrical impedance tomography. Further, in accordance with the invention various types of imaging and monitoring technologies can be used to determine blood flow into and out of a specific area of targeted tissues. These monitoring technologies can be used with the present invention with or without the use of imaging agents which may be added to the blood.
Embolotherapy
The invention can be used with high volume procedures including uterine fibroid embolization (UFE) and targeted liver embolization (TLE).
Uterine fibroids are benign tumors which can cause symptoms such as excessive bleeding, pain and disfigurement. If left untreated, the symptoms can persist until menopause, which severely impacts the patient's quality of life. They afflict approximately 25 million women in the U.S. Industry sources indicate that 200,000-300,000 of the 600,000 hysterectomies performed in the U.S. each year are due to fibroids. Further, there is a large pool of approximately six million women in the U.S. who are symptomatic enough to see their doctor. Today, many of these women take drugs that are not curative and often have severe side effects such as osteoporosis, or they go untreated.
UFE is the occlusion of the blood supply to uterine fibroids to reduce their size and alleviate associated symptoms. Uterine fibroids afflict approximately 25 million women in the U.S., cause mild to moderate symptoms in approximately 6 million, and over 200,000 to undergo surgical procedures.

Uterine Fibroid Embolization

The primary surgical procedures for uterine fibroids are hysterectomy and myomectomy, both of which often are accompanied by complications and long recovery periods. Driven by demand from women for minimally invasive procedures, the UFE market is projected to grow from 5,000 procedures and under $10 million in 1998 to more than 300,000 procedures and over $500 million by 2004.
TLE is the occlusion of the blood supply to liver tumors to deprive them of the nutrients they require to survive. Over four million people in the U.S. are positive for Hepatitis C which is thought to be a precursor to liver cancer in 10 to 20 percent of these individuals. Thus, the need for the present invention will increase as there is likely to be a significant increase in the incidence of liver cancer in the U.S. in the coming years. The present invention can be used with imaging materials and material such as such as embosphere micro spheres can be used to block the flow of blood to liver tumors.
Embolization is also used in neurointerventions (in the brain and spinal cord) and other parts of the body to occlude the blood flow to hyper vascularized tumors. While not high volume, these are often intricate procedures, especially in the brain, that require an embolic material that can pass through a micro catheter easily and be targeted precisely as can be carried out with the present invention. The methods of the present invention may be aided by the use of commercially available materials such as EmboGold® Micro spheres which bring visibility to the procedure. EmboGold Micro spheres were first marketed in the U.S. in September, 2001 and are precisely calibrated, spherical, hydrophilic, micro-porous beads made of an acrylic co-polymer, which is then cross-linked with gelatin. They are colored to facilitate handling and procedural efficiency. They eliminate aggregation in the catheter, unwanted proximal embolization and unpredictable distal embolization due to particle fragmentation.

EXAMPLES

The following examples are put forth so as to provide those of ordinary skill in the art with a complete disclosure and description of how to make and use the present invention, and are not intended to limit the scope of what the inventors regard as their invention nor are they intended to represent that the experiments below are all or the only experiments performed. Efforts have been made to ensure accuracy with respect to numbers used (e.g. amounts, temperature, etc.) but some experimental errors and deviations should be accounted for. Unless indicated otherwise, parts are parts by weight, molecular weight is weight average molecular weight, temperature is in degrees Centigrade, and pressure is at or near atmospheric.

Example 1

The mathematical model provided here shows that irreversible tissue ablation can affect substantial volumes of tissue, without inducing damaging thermal effects. To this end, the present invention uses the Laplace equation to calculate the electrical potential distribution in tissue during typical electroporation pulses and a modified Pennes (bioheat), (Pennes, H. H., Analysis of tissue and arterial blood flow temperatures in the resting forearm. J of Appl. Physiology., 1948. 1: p. 93-122), equation to calculate the resulting temperature distribution. It is important to note that there are several forms of the bioheat equation which have been reviewed (Carney, C. K., Mathematical models of bioheat transfer, in Bioengineering heat transfer, Y. I. Choi, Editor. 1992, Academic Press, Inc: Boston. p. 19-152; Eto, T. K. and B. Rubinsky, Bioheat transfer, in Introduction to bioengineering, S. A. Berger, W. Goldsmith, and E. R. Lewis, Editors. 1996, Oxford press). While the Pennes equation is controversial, it is nevertheless commonly used because it can provide an estimate of the various biological heat transfer parameters, such as blood flow and metabolism. The modified Pennes equation in this study contains the Joule heating term in tissue as an additional heat source.
The electrical potential associated with an electroporation pulse is determined by solving the Laplace equation for the potential distribution:
∇·(σ∇φ)=0 (1)

- where φ is the electrical potential and σ is the electrical conductivity. The electrical boundary condition of the tissue that is in contact with the leftmost electrode(s) on which the electroporation pulse is applied is:
  φ=V₀ (2)

The electrical boundary condition at the interface of the rightmost electrode(s) is:
φ=0 (3)
The boundaries where the analyzed domain is not in contact with an electrode are treated as electrically insulative to provide an upper limit to the electrical field near the electroporation electrodes and an upper limit to the temperature distribution that results from electroporation: $\begin{matrix} \frac{\partial ϕ}{\partial n} = 0 & (4) \end{matrix}$
Solving the Laplace equation enables one to calculate the associated Joule heating, the heat generation rate per unit volume from an electrical field (p):
p=σ|∇φ| ² (5)
This term is added to the original Pennes equation, (Pennes, H. H., Analysis of tissue and arterial blood flow temperatures in the resting forearm. J of Appl. Physiology., 1948. 1: p. 93-122) to represent the heat generated from the electroporation procedure: $\begin{matrix} \nabla \cdot (k \nabla T) + w_{b} c_{b} (T_{a} - T) + q^{′′′} + p = ρ c_{p} \frac{\partial T}{\partial t} & (6) \end{matrix}$
To solve equation (4) it is assumed that the entire tissue is initially at the physiological temperature of 37° C.:
T(x,y,z,0)=37 (7)
The outer surface of the analyzed domain and the surfaces of the electrodes are taken to be adiabatic, which should produce an upper limit to the calculated temperature distribution in the tissue: $\begin{matrix} \frac{\partial T}{\partial n} = 0 on the electrodes boundary and the outer surface domain & (8) \end{matrix}$
The analysis modeled conditions typical to tissue electroporation in the liver. The liver was chosen because it is the organ that most minimally invasive ablation techniques treat since cancer in the liver can be resolved by extirpation of the diseased area while surgical resection is not possible in many cases for this organ (Onik, G., B. Rubinsky, and et al., Ultrasound-Guided Hepatic Cryosurgery in the Treatment of Metastatic Colon Carcinoma. Cancer, 1991. 67(4): p. 901-907). The electroporation parameters, i.e. pulse parameters for reversible and irreversible electroporation where obtained from rat liver data (Miklavcic, D., et al., A validated model of in vivo electric field distribution in tissues for electrochemotherapy and for DNA electrotransfer for gene therapy. Biochimica et Biophysica Acta, 2000. 1523(1): p. 73-83; Suzuki, T., et al., Direct gene transfer into rat liver cells by in vivo electroporation. FEBS Letters, 1998. 425(3): p. 436-440), but biological parameters corresponding to the human liver were used in the analysis. Tissue thermal properties are taken from reference (Duck, F. A., Physical Properties of Tissues: A Comprehensive Reference Book. 1990, San Diego: Academic Press) and the electrical properties from reference (Boone, K., D. Barber, and B. Brown, Review—Imaging with electricity: report of the European Concerted Action on Impedance Tomography. J. Med. Eng. Technol., 1997. 21: p. 201-232) and are listed in table 1. The tissue is assumed isotropic and macroscopically homogeneous. The intent of the analysis was to determine the extent of the region in which reversible or irreversible electroporation is induced in the liver for various electroporation voltages and durations while the maximal temperature in the tissue is below 50° C. Thermal damage is a time-dependent process described by an Arhenius type equation (Henriques, F. C. and A. R. Moritz, Studies in thermal injuries: the predictability and the significance of thermally induced rate processes leading to irreversible epidermal damage. Arch Pathol., 1947.43: p. 489-502; Diller, K. R., Modeling of bioheat transfer processes at high and low temperatures, in Bioengineering heat transfer, Y. I. Choi, Editor. 1992, Academic Press, Inc: Boston. p. 157-357),
Ω=∫ξe ^−E ^a ^/RT dt (9)
Where Ω is a measure of thermal damage, ξ is the frequency factor, E_ais the activation energy and R is the universal gas constant. A detailed description on the various degrees of thermal damage as described in Equation (9) above can be found in (Diller, K. R., Modeling of bioheat transfer processes at high and low temperatures, in Bioengineering heat transfer, Y. I. Choi, Editor. 1992, Academic Press, Inc: Boston. p. 157-357).
A careful examination shows that the thermal damage is a complex function of time, temperature and all the parameters in Equation (9) above and that there are various degrees of thermal damage. In various applications or for various considerations it is possible to design irreversible electroporation protocols that induce some degree of thermal damage, either in part of the electroporated region or at a reduced level throughout the electroporated region. However, in this example we have chosen 50° C. as the target temperature for several reasons. Thermal damage begins at temperatures higher than 42° C., but only for prolonged exposures. Damage is relatively low until 50° C. to 60° C. at which the rate of damage dramatically increases (Diller, K. R., Modeling of bioheat transfer processes at high and low temperatures, in Bioengineering heat transfer, Y. I. Choi, Editor. 1992, Academic Press, Inc: Boston. p. 157-357). Therefore 50 C will be a relatively low bound on the possible thermal effects during irreversible electroporation. It is anticipated that the electrical parameters chosen for irreversible electroporation without a thermal effect could be substantially longer and higher than those obtained from an evaluation for 50 C in this example. Furthermore, since the Laplace and bioheat equations are linear, the results provided here can be extrapolated and considered indicative of the overall thermal behavior.
The analyzed configurations have two needles or four needle electrodes embedded in a square model of the liver. Needle electrodes are commonly used in tissue electroporation and will be most likely also used in the liver (Somiari, S., et al., Theory and in vivo application of electroporative gene delivery. Molecular Therapy, 2000. 2(3): p. 178-187). The square model of the liver was chosen large enough to avoid outer surface boundary effects and to produce an upper limit for the temperature, which develops during electroporation in the liver. For each configuration the surface of one electrode is assumed to have a prescribed voltage with the other electrode set to ground. The effect of the spacing between the electrodes was investigated by comparing distances of 5, 7.5 and 10 mm, which are typical. The electrodes were also modeled with typical dimensions of 0.5, 1 and 1.5 mm in diameter. The blood flow perfusion rate was taken to zero or 1.0 kg/m³s (Deng, Z. S. and J. Liu, Blood perfusion-based model for characterizing the temperature fluctuations in living tissue. Phys A STAT Mech Appl, 2001. 300: p. 521-530). The metabolic heat was taken to be either zero or 33.8 kW/m³(Deng, Z. S. and J. Liu, Blood perfusion-based model for characterizing the temperature fluctuations in living tissue. Phys A STAT Mech Appl, 2001. 300: p. 521-530).
The calculations were made for an electroporation pulse of 800 μs. This pulse duration was chosen because typically, reversible electroporation is done with eight separate 100 μs pulses, (Miklavcic, D., et al., A validated model of in vivo electric field distribution in tissues for electrochemotherapy and for DNA electro transfer for gene therapy. Biochimica et Biophysica Acta, 2000. 1523(1): p. 73-83) and therefore the value we chose is an upper limit of the thermal effect in a pulse time frame comparable to that of reversible electroporation. Consequently, the results obtained here are the lower limit in possible lesion size during irreversible electroporation. It should be emphasized that we believe irreversible electroporation tissue ablation can be done with shorter pulses than 800 μs. To evaluate the thermal effect, we gradually increased in our mathematical model the applied pulse amplitude for the 800 μs pulse length until our calculations indicated that the electroporation probe temperature reached 50° C., which we considered to be the thermal damage limit. Then, we evaluated the electric field distribution throughout the liver.
A transmembrane potential on the order of 1V is required to induce irreversible electroporation. This value is dependent on a variety of conditions such as tissue type, cell size and other external conditions and pulse parameters. The primary electrical parameter affecting the transmembrane potential for a specific tissue type is the amplitude of the electric field to which the tissue is exposed. The electric field thresholds used in estimating the extent of the region that was irreversibly electroporated were taken from the fundamental studies of Miklavcic, Mir and their colleagues performed with rabbit liver tissue (Miklavcic, D., et al., A validated model of in vivo electric field distribution in tissues for electrochemotherapy and for DNA electro transfer for gene therapy. Biochimica et Biophysica Acta, 2000. 1523(1): p. 73-83). In this study, that correlated electroporation experiments with mathematical modeling, they have found that the electric field for reversible electroporation is 362+/−21 V/cm and is 637+/−43 V/cm for irreversible electroporation for rat liver tissue. Therefore, in the analysis an electric field of 360 V/cm is taken to represent the delineation between no electroporation and reversible electroporation and 680 V/cm to represent the delineation between reversible and irreversible electroporation.
All calculations were performed using MATLAB's finite element solver, Femlab v2.2 (The MathWorks, Inc. Natick, Mass.). To ensure mesh quality and validity of solution, the mesh was refined until there was less than a 0.5% difference in solution between refinements. The baseline mesh with two 1 mm electrodes, 10 mm spacing had 4035 nodes and 7856 triangles. The simulations were conducted on a Dell Optiplex GX240 with 512 MB of RAM operating on Microsoft Windows 2000.

Results and Discussion

FIGS. 2 and 3 examine the effect of the electrode size and spacing on the ablated area in a two-needle electroporation configuration. In obtaining these figures, we ignored the effect of the blood flow and metabolism in the heat transfer equation, which should give an upper limit for the estimated ablation area. FIG. 2 compares the extent of the irreversible electroporated area for electroporation electrode sizes of 0.5, 1 and 1.5 mm in diameter and a distance between electrodes of 10 mm. The strong effect of the electrode size is evident. It is seen that for the smaller electrodes, the irreversibly electroporated area is not contiguous, while for a 1.5 mm electrode the area of potential tissue, ablation has an elliptical shape with dimensions of about 15 mm by 10 mm. In the brackets, we give the electroporation voltage for which the probe temperature reaches 50° C. in these three configurations. It is seen that the range is from 857V for the 0.5 mm probe to 1575V for the 1.5 mm probe. This is within the typical range of tissue electroporation pulses. FIG. 3 evaluates the effect of the spacing between the electrodes. It is observed that in the tested range, the small dimension of the contiguous elliptical shape of the ablated lesion remains the same, while the larger dimension seems to scale with the distance between the electrodes.
FIGS. 2 and 3 demonstrate that the extent of tissue ablation with irreversible electroporation is comparable to that of other typical minimally invasive methods for tissue ablation, such as cryosurgery (Onik, G. M., B. Rubinsky, and et. al., Ultrasound-guided hepatic cryosurgery in the treatment of metastatic colon carcinoma. Cancer, 1991. 67(4): p. 901-907; Onik, G. M., et al., Transrectal ultrasound-guided percutaneous radical cryosurgical ablation of the prostate. Cancer, 1993. 72(4): p. 1291-99). It also shows that varying electrode size and spacing can control lesion size and shape. The shape and size of the ablated lesion can be also controlled by varying the number of electrodes used. This is shown in FIGS. 4 and 5, for a four-electrode configuration. These figures also compare the effect of probe size and spacing and the results were also obtained by ignoring the effect of blood flow and metabolism in the energy equation. Again, it is seen that larger electrodes have a substantial effect on the extent of the ablated region and that the extent of ablation scales with the spacing between the electrodes.
A comparison between reversible and irreversible electroporation protocols can be achieved from FIGS. 6 and 7. In FIG. 6, an 800 μs, 1295 V pulse was applied between two 1.5 mm diameter electrodes placed 10 mm apart. This produces a tissue temperature lower than 50° C. The figure plots the margin of the irreversibly electroporated region, i.e. the 680 V/cm voltage-to-distance gradients and that of the reversible electroporated region, the 360 V/cm gradients. FIG. 7 was obtained for two 1 mm electrodes placed 10 mm apart. In this figure, we produced an electroporated region that was only reversibly electroporated, i.e. with electric fields lower than 360 V/cm. In comparing FIGS. 6 and 7, it is obvious that the extent of the ablated area possible through electrochemotherapy alone is substantially smaller than that through irreversible electroporation alone.
The effect of blood flow and metabolism on the extent of irreversible electroporation is illustrated in FIG. 8. The figures compare a situation with metabolism and a relatively high blood flow rate to a situation without blood flow or metabolism. It is obvious that metabolism and blood perfusion have a negligible effect on the possible extent of irreversible tissue electroporation. This is because the effect of the Joule heating produced by the electroporation current is substantially larger than the effects of blood flow or metabolism.
An even more conservative estimate for the thermal damage can be obtained by assuming that the tissue reaches 50° C. instantaneously, during the electroporation pulses such that the damage is defined as
Ω=t _p ξe ^−ΔE/RT (10)
Several values taken from the literature for activation energy and frequency factor were applied to equation (10) with the pulse lengths calculated in the examples above. Because the application of the pulse is so short, the damage would be near zero, many times less than the value (Ω=0.53) to induce a first degree burn (Diller, K. R., Modeling of bioheat transfer processes at high and low temperatures, in Bioengineering heat transfer, Y. I. Choi, Editor. 1992, Academic Press, Inc: Boston. p. 157-357). regardless of the values used for activation energy and frequency factor.
Currently, tissue ablation by electroporation is produced through the use of cytotoxic drugs injected in tissue combined with reversible electroporation, a procedure known as electrochemotherapy. The present invention shows that irreversible electroporation by itself produces substantial tissue ablation for the destruction of undesirable tissues in the body. The concern was that higher voltages required for irreversible electroporation would cause Joule heating and would induce thermal tissue damage to a degree that would make irreversible electroporation a marginal effect in tissue ablation. Using a mathematical model for calculating the electrical potential and temperature field in tissue during electroporation, the present invention shows that the area ablated by irreversible tissue electroporation prior to the onset of thermal effects is substantial and comparable to that of other tissue ablation techniques such as cryosurgery. Our earlier studies have shown that the extent of electroporation can be imaged in real time with electrical impedance tomography (Davalos, R. V., B. Rubinsky, and D. M. Otten, A feasibility study for electrical impedance tomography as a means to monitor tissue electroporation for molecular medicine. IEEE Transactions on Biomedical Engineering, 2002. 49(4): p. 400-403; Davalos, R. V., et al., Electrical impedance tomography for imaging tissue electroporation. IEEE Transactions on Biomedical Engineering, 2004). Irreversible electroporation, therefore, has the advantage of being a tissue ablation technique, which is as easy to apply as high temperature ablation, without the need for adjuvant chemicals as required in electrochemical ablation and electrochemotherapy. In addition, a unique aspect of irreversible electroporation is that the affected area can be controlled in real time with electrical impedance tomography.

Example 2

This example was developed to produce a correlation between electroporation pulses and thermal effects. The system analyzed is an infinitesimally small control volume of tissue exposed to an electroporation voltage gradient of V (Volts/cm). The entire electrical energy is dissipated as heat and there is no conduction of heat from the system. The calculations produce the increase in temperature with time during the application of the pulse and the results are a safe lower limit for how long a certain electroporation pulse can be administered until a certain temperature is reached. To generate the correlation an energy balance is made on a control volume between the Joule heating produced from the dissipation of heat of the V (volt/cm) electrical potential dissipating through tissue with an electrical conductivity of σ (ohm-cm) and the raise in temperature of the control volume made of tissue with a density ρ (g/cc) and specific heat, c, (J/g K). the calculation produces the following equation for the raise in temperature (T) per unit time (t) as a function of the voltage gradients and the thermal and electrical properties of the liver. $\begin{matrix} \frac{ⅆ T}{ⅆ t} = \frac{V^{2} σ}{ρ c} & (2 - 1) \end{matrix}$
The table below was obtained for the liver with the following properties:

- Electrical resistivity of liver—8.33 Ohm-meter
- Specific heat of liver—J/g K
- Density of liver—1 g/cc

We obtain the following table:

TABLE 1


Voltage	Time per degree	time from 37 C. to
Gradient - V (V/cm)	C. rise (ms)	65 C. (ms)

50	1199.52	33586.56
100	299.88	8396.64
150	133.28	3731.84
200	74.97	2099.16
250	47.98	1343.46
300	33.32	932.96
350	24.48	685.44
400	18.74	524.79
450	14.81	414.65
500	12.00	335.87
550	9.91	277.57
600	8.33	233.24
650	7.10	198.74
700	6.12	171.36
750	5.33	149.27
800	4.69	131.20
850	4.15	116.22
900	3.70	103.66
950	3.32	93.04
1000	3.00	83.97
1050	2.72	76.16
1100	2.48	69.39
1150	2.27	63.49
1200	2.08	58.31
1250	1.92	53.74
1300	1.77	49.68
1350	1.65	46.07
1400	1.53	42.84
1450	1.43	39.94
1500	1.33	37.32

The second column of Table 1 gives the amount of time it takes for the temperature of the liver to raise 1 C, when the tissue experiences the electroporation pulse in column 1. The time for even a relatively high electroporation voltage of 1500V/cm is of the order of 1.33 millisecond for 1 C rise and 37.32 millisecond until a temperature of 65 C is reached. Using the equation (2-1) or Table 1 it is possible to evaluate the amount of time a certain pulse can be applied without inducing thermal effects. Considering the typical electroporation parameters reported so far there is no limitation in the electroporation length from thermal considerations. Column 3 of Table 1 shows the time required to reach 65 C, which is where thermal damage may begin. The calculations in this example give a lower limit for the extent of time in which a certain thermal effects will be induced by electroporation pulses. For more precise calculations it is possible to use the equation developed in this example with equation (9) or (10) from Example 1.

Example 3

The goal of this experiment was to verify the ability of irreversible electroporation pulses to produce substantial tissue ablation in the non-thermal regime. To this end we have performed experiments on the liver of Spraque-Dawley male rats (250 g to 350 g) under an approved animal use and care protocol. After the animals were anesthetized by injection of Nembutal Sodium Solution (50 mg/ml Pentobarbital) the liver was exposed via a midline incisions and one lobed clamped between two cylindrical electrodes of Ag/AgCl, with a diameter of 10 mm (In Vivo Metric, Healdsburg, Calif.). The electrodes had their flat surface parallel; they were concentric and the liver between the electrodes was compressed so that the lobes were separated by 4 mm. A schematic of the electrodes and the liver is shown in FIG. 9. The liver was exposed to a single electroporation pulse of 40 milliseconds. One electrode was set to 400 V and the other grounded. The rest of the liver was not in contact with any media and therefore is considered electrically insulated. After electroporation the rat was maintained under controlled anesthesia for three hours. Following exsanguination the liver was flushed with physiological saline under pressure and fixed by perfusion with formaldehyde. The liver was resected through the center of the electroporated region and analyzed by histology. FIGS. 10 and 11 show the appearance of the liver. Histology has determined that the dark area corresponds to the region of tissue necrosis. The electrical field in the electroporated liver and the temperature distribution were calculated using the equations in Example 1, subject to one electrode at a voltage of 400V and the other grounded, for 40 milliseconds. The liver was modeled as an infinite slab of 4 mm thickness, with concentric cylindrical electrodes (see FIG. 9). The results are shown in FIG. 12. FIG. 12 shows lines of constant voltage gradients (V/cm) and lines of constant temperature. It is evident that in the majority of the electroporated tissue the temperature is about 42 C immediately after the pulse. The highest temperature occurs near the edge of the cylindrical electrodes, where it is about 50 C. FIG. 13 was obtained by bringing together FIGS. 11 and 12. Superimposing the calculated results on the histological measurements reveals that the dark (necrotic) area margin corresponds to electroporation parameters of about 300 V/cm. The results demonstrate that irreversible electroporation can induce substantial tissue necrosis without the need for chemical additives as in electrochemotherapy and without a thermal effect.
The results obtained by disrupting blood flow to a given area are dramatically shown in FIG. 14 which is a photo of a micrograph. This micrograph is from the interface between irreversible electroporated liver and normal liver. The left hand side shows normal hepatocytes with clear nucleus and nuclei. The photo shows well defined cell membranes and clean (flushed) sinusoids. The right hand side of FIG. 14 shows condensed nuclei, no evidence of cell membrane, expanded cell border with no evidence of sinusoids. The disintegrated red blood cells shown in FIG. 14 are in what could have been the spaces of the sinusoids. Flushing is not believed to have had an effect on the results obtained on the right hand side of FIG. 14.
The preceding merely illustrates the principles of the invention. It will be appreciated that those skilled in the art will be able to devise various arrangements which, although not explicitly described or shown herein, embody the principles of the invention and are included within its spirit and scope. Furthermore, all examples and conditional language recited herein are principally intended to aid the reader in understanding the principles of the invention and the concepts contributed by the inventors to furthering the art, and are to be construed as being without limitation to such specifically recited examples and conditions. Moreover, all statements herein reciting principles, aspects, and embodiments of the invention as well as specific examples thereof, are intended to encompass both structural and functional equivalents thereof. Additionally, it is intended that such equivalents include both currently known equivalents and equivalents developed in the future, i.e., any elements developed that perform the same function, regardless of structure. The scope of the present invention, therefore, is not intended to be limited to the exemplary embodiments shown and described herein. Rather, the scope and spirit of present invention is embodied by the appended claims.

Claims

1. A method of disrupting blood flow, comprising the steps of:

(a) identifying blood vessels providing blood to a targeted area of tissue to be ablated;

(b) placing a first electrode and a second electrode such that the identified blood vessels are positioned between the first and second electrodes;

(c) applying electrical pulses between the first and second electrodes in an amount sufficient to disrupt blood flow through the vessels thereby disrupting blood flow to cells of the targeted area.

2. The method of claim 1, further comprising:

(d) allowing the cells of the target area deprived of blood flow to be removed by internal systems of an organism comprised of the tissue.

3. The method of claim 1, wherein the electrical pulses are applied for a duration in a range of from about 5 microseconds to about 62 seconds.

4. The method of claim 1, wherein the electrical pulses are applied for a period of about 100 microseconds,± about 10 microseconds.

5. The method of claim 1, wherein from about 1 to about 15 pulses are applied.

6. The method of claim 1, wherein about eight pulses of about 100 microseconds each in duration are applied.

7. The method of claim 1, wherein the pulses produce a voltage gradient in a range of from about 50 volt/cm to about 8000 volt/cm.

8. The method of claim 1, wherein the first electrode is placed at about 5 mm to 10 cm from the second electrode.

9. The method of claim 1, wherein the first and second electrodes are positioned in an area of blood vessels upstream of the targeted area, in a direct of blood flow toward the targeted area of tissue.

10. The method of claim 1, further comprising:

infusing a material into the blood prior to applying the electrical pulses.

11. The method of claim 10, wherein the material is a chemotherapeutic agent.

12. The method of claim 10, wherein the material is an imaging agent.

13. The method of claim 1, wherein the first electrode and second electrode are circular in shape.

14. The method of claim 1, wherein the first electrode and the second electrode each have a surface area of about 1 square centimeter.

15. The method of claim 1, further comprising:

monitoring blood flow in the blood vessels.

16. The method of claim 15, further comprising:

adjusting the electrical pulses based on real time information of the monitored blood flow.

17. The method of claim 1, further comprising:

monitoring temperature of the identified tissue and adjusting the electrical pulses to maintain the temperature at 100° C. or less.

18. The method of claim 17, wherein the temperature is maintained at 50° C. or less.

19. A method of claim 1, further comprising:

adjusting applied voltage, length of pulses, and number of pulses to obtain blood flow disruption to the target area thereby minimizes damage to non-target tissue.

20. The method of claim 1, wherein:

adjusting duration of the applied voltage is in accordance with the current-to-voltage ratio to achieve blood flow disruption to the targeted area.

21. The method of claim 20, wherein the current-to-voltage ratio is adjusted based on temperature to maintained target tissue temperature at 100° C. or less.

22. The method of claim 20, wherein the current-to-voltage ratio is adjusted based on temperature to maintained target tissue temperature at 50° C. or less.

23. The method of claim 15, further comprising:

adjusting current-to-voltage ratio based on monitored blood flow.

24. A method of treating cancer, comprising:

(a) identifying a grouping of biological cells in a tissue of a living mammal as being cancer cells and applying a voltage across the cells;

(b) continuously detecting a ratio of electric current through the cells to voltage across the cells as an indication of degree of electroporation of the biological cells; and

(c) adjusting a determined magnitude of the applied voltage in accordance with changes in detected magnitude of the current-to-voltage ratio to achieve a disruption of blood flow to the grouping of cells identified as being cancer cells.

25. The method of claim 24, wherein step (b) comprises continuously detecting the current-to-voltage ratio in an indication of onset of electroporation of biological cells, and step (c) comprises adjusting the duration of the applied voltage in accordance with continuously detected current-to-voltage ratio to achieve disruption of blood flow to the grouping of cells identified as being cancer cells.

26. The method of claim 24, wherein the current-to-voltage ratio is an indication of degree of electroporation averaged over the cells identified as cancer cells, achieving disruption of blood flow to the cancer cells.

27. The method of claim 24, wherein the voltage is applied between two microelectrodes positioned with the grouping of biological cells in between.

28. The method of claim 24, wherein the voltage is applied between two microelectrodes positioned with a vessel providing blood to the cancer cells in between the microelectrodes.

29. The method of claim 28, wherein the vessel is in a mammal.

30. The method of claim 29, wherein the mammal is a human.

31. A method for disrupting blood flow, comprising:

(a) applying a voltage across a target blood vessel;

(b) continuously detecting the ratio of electric current through the target vessel to voltage across the vessel as an indication of degree of blood flow through the vessel; and

(c) adjusting the applied voltage in accordance with changes in current-to-voltage ratio to achieve disruption of blood flow through the vessel, thereby achieving disruption of flow through the vessel at a level which minimizes damage to non-target tissue.

32. The method of claim 31, wherein:

step (b) comprises continuously detecting the current-to-voltage ratio as an indication of an onset of blood flow disruption, and

step (c) comprises adjusting duration of the applied voltage in accordance with the current-to-voltage ratio to achieve blood flow disruption through the vessel.

33. The method of claim 31, wherein:

voltage is applied between two electrodes inserted in a mammal, and the electrodes are positioned to apply voltage across a targeted vessel;

step (b) comprises further correlating the current-to-voltage ratio with the temperature of the targeted vessel; and

step (c) comprises adjusting the magnitude of the voltage while the targeted vessel is between the electrodes based on an averaged degree of blood flow disruption in the targeted vessel.

34. The method of claim 33, wherein the current-to-voltage ratio is adjusted based on temperature to maintain targeted vessel temperature at 60° C. or less.

35. The method of claim 34, wherein the current-to-voltage ratio is adjusted based on temperature to maintain targeted vessel temperature at 50° C. or less.

36. A method of ablating a portion of a blood vessel, comprising the steps of:

identifying a portion of a blood vessel to be ablated;

placing first and second electrodes such that an identified position of the vessel is positioned between the first and second electrodes;

applying a predetermined electric field to the identified position of the vessel for a time sufficient to disrupt blood flow through the identified portion of the vessel.

37. A device for disrupting blood flow, comprising:

first and second electrodes that position a blood vessel to be disrupted therebetween;

a voltage generator means that applies a voltage between the first and second electrodes in a manner which provides a predetermined electric field around the blood vessel for a time sufficient to disrupt blood flow through the vessel.

38. The device of claim 37, wherein the generator means generates pulses of 100 microseconds±about 10 microseconds at a voltage gradient in a range of from about 50 volt/cm to about 8000 volt/cm.

39. The device of claim 37, further comprising:

a means for adjusting the voltage and pulse duration of the generator means to obtain blood flow disruption.

40. The device of claim 37, further comprising:

a means for monitoring blood flow.

41. A method of carrying our uterine fibroid embolization, comprising the steps of:

(a) identifying blood vessels providing blood to a targeted area of uterine fibroid tissue to be ablated;

(c) applying electrical pulses between the first and second electrodes in an amount sufficient to disrupt blood flow through the vessels thereby disrupting blood flow to cells of the targeted uterine fibroid tissue.

42. The method of claim 41, wherein the electrical pulses are applied for a duration in a range of from about 5 microseconds to about 62 seconds.

43. The method of claim 41, wherein the electrical pulses are applied for a period of about 100 microseconds,±about 10 microseconds and wherein from about 1 to about 15 pulses are applied.

44. The method of claim 41, wherein about eight pulses of about 100 microseconds each in duration are applied, wherein the pulses produce a voltage gradient in a range of from about 50 volt/cm to about 8000 volt/cm.

45. The method of claim 41, wherein the first electrode is placed at about 5 mm to 10 cm from the second electrode.

46. The method of claim 41, wherein the first and second electrodes are positioned in an area of blood vessels upstream of the targeted uterine fibroid tissue, in a direction of blood flow toward the targeted area of uterine fibroid tissue.

47. The method of claim 41, further comprising:

monitoring blood flow in the blood vessels; and

48. The method of claim 41, further comprising:

49. The method of claim 48, wherein the temperature is maintained at 50° C. or less.

50. A method of treating a uterine fibroid, comprising:

(a) identifying a uterine fibroid and applying a voltage across the uterine fibroid;

(b) continuously detecting a ratio of electric current through the uterine fibroid to voltage across at least a portion of the uterine fibroid as an indication of degree of electroporation of cells of the uterine fibroid; and

(c) adjusting a determined magnitude of the applied voltage in accordance with changes in detected magnitude of the current-to-voltage ratio to achieve a disruption of blood flow to cells of the uterine fibroid.

51. The method of claim 50, wherein step (b) comprises continuously detecting the current-to-voltage ratio in an indication of onset of electroporation of the uterine fibroid cells, and step (c) comprises adjusting the duration of the applied voltage in accordance with continuously detected current-to-voltage ratio to achieve disruption of blood flow to the uterine fibroid.

52. A method of carrying our targeted embolotherapy, comprising the steps of:

53. The method of claim 1, wherein the electrical pulses are applied for a duration in a range of from about 5 microseconds to about 62 second and wherein the area of tissue to be ablated is chosen from a cancerous tumor, a benign tumor, a uterine fibroid and a portion of a liver.