U.S. patent application number 12/163727 was filed with the patent office on 2008-10-30 for electroporation to interrupt blood flow.
This patent application is currently assigned to THE REGENTS OF THE UNIVERSITY OF CALIFORNIA. Invention is credited to JON FRANCIS EDD, LIANA HOROWITZ, BORIS RUBINSKY.
Application Number | 20080269586 12/163727 |
Document ID | / |
Family ID | 34748811 |
Filed Date | 2008-10-30 |
United States Patent
Application |
20080269586 |
Kind Code |
A1 |
RUBINSKY; BORIS ; et
al. |
October 30, 2008 |
ELECTROPORATION TO INTERRUPT BLOOD FLOW
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.
Inventors: |
RUBINSKY; BORIS; (GIVATAAIM,
IL) ; EDD; JON FRANCIS; (BERKELEY, CA) ;
HOROWITZ; LIANA; (GIVATAAIM, IL) |
Correspondence
Address: |
BOZICEVIC, FIELD & FRANCIS LLP
1900 UNIVERSITY AVENUE, SUITE 200
EAST PALO ALTO
CA
94303
US
|
Assignee: |
THE REGENTS OF THE UNIVERSITY OF
CALIFORNIA
|
Family ID: |
34748811 |
Appl. No.: |
12/163727 |
Filed: |
June 27, 2008 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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11022310 |
Dec 21, 2004 |
|
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12163727 |
|
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60532588 |
Dec 24, 2003 |
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Current U.S.
Class: |
600/371 ;
600/549; 606/50 |
Current CPC
Class: |
A61N 1/0412 20130101;
A61B 2018/00827 20130101; A61N 1/05 20130101; A61N 1/327 20130101;
A61B 18/1233 20130101; A61B 2018/00714 20130101; A61B 18/1477
20130101; A61B 2018/1425 20130101; A61B 18/12 20130101; A61B
2018/00761 20130101; A61B 2018/00577 20130101; A61N 1/0472
20130101; A61B 2018/00613 20130101 |
Class at
Publication: |
600/371 ; 606/50;
600/549 |
International
Class: |
A61B 18/18 20060101
A61B018/18; A61B 5/026 20060101 A61B005/026; A61B 5/01 20060101
A61B005/01 |
Claims
1.-36. (canceled)
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.-53. (canceled)
54. The device of claim 37, wherein the generator is designed to
apply electrical pulses for a duration in a range of from about 5
microseconds to about 62 seconds.
55. The device of claim 37, wherein the generator is designed to
apply electrical pulses for a period of about 100 microseconds,
.+-.about 10 microseconds.
56. The device of claim 37, wherein the generator is designed so
that on activation it applies from about 1 to about 15 pulses.
57. The device of claim 37, wherein the generator is designed so
that on activation it applies about eight pulses of about 100
microseconds each in duration.
58. The device of claim 37, wherein the generator is designed so
that on activation it applies pulses that produce a voltage
gradient in a range of from about 50 volt/cm to about 8000
volt/cm.
59. The device of claim 37, wherein the first electrode is
positioned at about 5 mm to 10 cm from the second electrode.
60. The device of claim 37, further comprising: a monitor for
monitoring blood flow in blood vessels.
61. The device of claim 60, further comprising: a means for
adjusting the electrical pulses based on real time information of
the monitored blood flow.
62. The device of claim 37, further comprising: a monitor for
monitoring temperature of the identified tissue; and a means for
adjusting the electrical pulses to maintain the temperature at
100.degree. C. or less.
63. The device of claim 62, wherein the monitor maintains the
temperature at 50.degree. C. or less.
64. A device of claim 37, further comprising: a means for 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.
65. The device of claim 37, further comprising: a means for
adjusting duration of applied voltage is in accordance with
current-to-voltage ratio to achieve blood flow disruption to a
targeted area.
66. The device of claim 65, wherein the means for adjusting,
adjusts the current-to-voltage ratio based on temperature to
maintain target tissue temperature at 100.degree. C. or less.
67. The device of claim 65, wherein the means for adjusting,
adjusts the current-to-voltage ratio based on temperature to
maintain target tissue temperature at 50.degree. C. or less.
68. The device of claim 37, further comprising: a means for
adjusting current-to-voltage ratio connected to and interactive
with a means for monitoring blood flow.
69. The device of claim 37, a means for determining an indication
of degree of electroporation averaged over cells identified as
cancer cells.
70. The device of claim 37, wherein the electrodes are
microelectrodes.
Description
CROSS-REFERENCE
[0001] 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
[0002] This invention relates to the field of electrode devices
useful to disrupt blood flow in order to carry out treatments.
BACKGROUND OF THE INVENTION
[0003] 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. Radio frequency 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., Shizer, 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.
[0004] 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.
[0005] 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 U. 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. 01CH37251). 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 US 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.
[0006] 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, Vol28 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).
[0007] 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.
[0008] 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.
[0009] 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.
[0010] 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).
[0011] 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)).
[0012] 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).
[0013] 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 drugs 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.
[0014] 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.
[0015] 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.
[0016] 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.
[0017] 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.
[0018] 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
[0019] 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.
[0020] 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.
[0021] 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).
[0022] 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.
[0023] 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.
[0024] 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.
[0025] 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.
[0026] 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.
[0027] 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.
[0028] 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.
[0029] 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.
[0030] 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.
[0031] 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.
[0032] 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.
[0033] 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.
[0034] 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.
[0035] 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.
[0036] 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.
[0037] 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.
[0038] 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.
[0039] These and further features, advantages and objects of the
invention will be better understood from the description that
follows.
BRIEF DESCRIPTION OF THE DRAWINGS
[0040] 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:
[0041] FIG. 1. is a graph showing a schematic relationship between
field strength and pulselength applicable to the electroporation of
cells.
[0042] FIGS. 2 A, 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.
[0043] 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 FIG. 3A; 1116V and 7.5 mm for FIG. 3B; and 1295V and 10
mm spacing for FIG. 3C.
[0044] 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.
[0045] 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.
[0046] 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 .mu.s pulses at a
frequency of 1 Hz. Applying a single 800 .mu.s 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.
[0047] 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.
[0048] 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.sub.b=1 kg/m.sup.3,
c.sub.b=3640 J/(kg K), T.sub.b=37.degree. C., and q'''-33.8
kW/m.sup.3.
[0049] 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.
[0050] 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.
[0051] 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.
[0052] 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.
[0053] 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.
[0054] 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
[0055] 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.
[0056] 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.
[0057] 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.
[0058] 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.
[0059] 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
[0060] 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.
[0061] 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
[0062] 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.
[0063] The discovery that with irreversible electroporation the
occlusion of blood flow in the irreversible electroporated area is
permanent has important applications as described below.
[0064] 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.
[0065] 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.
[0066] 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 reversible
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.
[0067] 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.
[0068] 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.
[0069] 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.
[0070] 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.
[0071] 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.
[0072] 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.
[0073] 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.
[0074] 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.
[0075] 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.
[0076] 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.
[0077] 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.
[0078] 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.
[0079] 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
[0080] The invention can be used with high volume procedures
including uterine fibroid embolization (UFE) and targeted liver
embolization (TLE).
[0081] 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.
[0082] 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
[0083] 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.
[0084] 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.
[0085] 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.RTM. 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
[0086] 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
[0087] 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:
.gradient.(.pi..gradient..phi.)=0 (1)
[0088] where .phi. is the electrical potential and .sigma. 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:
.phi.=V.sub.0 (2)
[0089] The electrical boundary condition at the interface of the
rightmost electrode(s) is:
.phi.=0 (3)
[0090] 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:
.differential. .phi. .differential. n = 0 ( 4 ) ##EQU00001##
[0091] 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=.sigma.|.gradient..phi.|.sup.2 (5)
[0092] 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:
.gradient. ( k .gradient. T ) + w b c b ( T a - T ) + q '' ' + p =
.rho. c p .differential. T .differential. t ( 6 ) ##EQU00002##
[0093] To solve equation (4) it is assumed that the entire tissue
is initially at the physiological temperature of 37.degree. C.:
T(x,y,z,0)=37 (7)
[0094] 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:
.differential. T .differential. n = 0 ##EQU00003##
on the electrodes boundary and the outer surface domain (8)
[0095] 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.degree. 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),
.OMEGA.=.intg..xi.e.sup.-.sup.a.sup./RTdt (9)
[0096] Where .OMEGA. is a measure of thermal damage, is the
frequency factor, E.sub.a is 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).
[0097] 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.degree. C. as the target temperature for several reasons.
Thermal damage begins at temperatures higher than 42.degree. C.,
but only for prolonged exposures. Damage is relatively low until
50.degree. C. to 60.degree. 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.
[0098] 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/m.sup.3 s (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/m.sup.3 (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).
[0099] The calculations were made for an electroporation pulse of
800 .mu.s. This pulse duration was chosen because typically,
reversible electroporation is done with eight separate 100 .mu.s
pulses, (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) 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 vs. To evaluate the thermal effect, we
gradually increased in our mathematical model the applied pulse
amplitude for the 800 .mu.s pulse length until our calculations
indicated that the electroporation probe temperature reached
50.degree. C., which we considered to be the thermal damage limit.
Then, we evaluated the electric field distribution throughout the
liver.
[0100] 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 electrotransfer 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.
[0101] 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
[0102] 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.degree. 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.
[0103] 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.
[0104] A comparison between reversible and irreversible
electroporation protocols can be achieved from FIGS. 6 and 7. In
FIG. 6, an 800 .mu.s, 1295 V pulse was applied between two 1.5 mm
diameter electrodes placed 10 mm apart. This produces a tissue
temperature lower than 50.degree. 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.
[0105] 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.
[0106] An even more conservative estimate for the thermal damage
can be obtained by assuming that the tissue reaches 50.degree. C.
instantaneously, during the electroporation pulses such that the
damage is defined as
.OMEGA.=t.sub.p.xi.e.sup.-.DELTA.E/RT (10)
[0107] 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 (Q=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.
[0108] 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
[0109] 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 .sigma. (ohm-cm) and the raise in temperature of
the control volume made of tissue with a density .rho. (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.
T t = V 2 .sigma. .rho. c ( 2 - 1 ) ##EQU00004##
[0110] The table below was obtained for the liver with the
following properties:
[0111] Electrical resistivity of liver--8.33 Ohm-meter
[0112] Specific heat of liver--J/g K
[0113] Density of liver--1 g/cc
[0114] We obtain the following table:
TABLE-US-00001 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
[0115] 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
[0116] 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 5.degree. 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.
[0117] 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.
[0118] 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.
* * * * *