U.S. patent application number 16/021479 was filed with the patent office on 2018-10-25 for surgical instrument comprising an electrode.
The applicant listed for this patent is Ethicon LLC. Invention is credited to Gary L. Long, David N. Plescia.
Application Number | 20180303541 16/021479 |
Document ID | / |
Family ID | 43838129 |
Filed Date | 2018-10-25 |
United States Patent
Application |
20180303541 |
Kind Code |
A1 |
Long; Gary L. ; et
al. |
October 25, 2018 |
SURGICAL INSTRUMENT COMPRISING AN ELECTRODE
Abstract
A surgical instrument can comprise a first electrode, a second
electrode, and a retractable sheath. At least one of the electrodes
can comprise an insulative jacket extending along the length
thereof which can comprise a tissue stop for limiting the
progression of the electrode into tissue. In various embodiments, a
surgical instrument can comprise a first electrode, a second
electrode, and a displaceable arc guard positioned between the
electrodes. In certain embodiments, a surgical instrument can
comprise an electrode including a flexible mesh configured to
conform to the tissue against which it is positioned.
Inventors: |
Long; Gary L.; (Cincinnati,
OH) ; Plescia; David N.; (Mentor, OH) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
Ethicon LLC |
Guaynabo |
PR |
US |
|
|
Family ID: |
43838129 |
Appl. No.: |
16/021479 |
Filed: |
June 28, 2018 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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14695824 |
Apr 24, 2015 |
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16021479 |
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12641837 |
Dec 18, 2009 |
9028483 |
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14695824 |
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Current U.S.
Class: |
1/1 |
Current CPC
Class: |
A61B 2090/065 20160201;
A61B 2018/00083 20130101; A61B 18/1402 20130101; A61B 2017/00221
20130101; A61B 2018/00107 20130101; A61B 2018/0022 20130101; A61B
2018/00547 20130101; A61B 2018/1465 20130101; A61N 1/327 20130101;
A61B 2018/00077 20130101; A61B 2018/00577 20130101; A61B 18/1477
20130101 |
International
Class: |
A61B 18/14 20060101
A61B018/14 |
Claims
1. A surgical instrument, comprising: a shaft comprising a
conductor; and an electrode, comprising: a support member mounted
to said shaft; and a flexible mesh comprising an electrically
conductive material, wherein said support member is configured to
support at least a portion of said flexible mesh, and wherein said
flexible mesh is in electrical communication with said
conductor.
2. The surgical instrument of claim 1, wherein said flexible mesh
comprises a substrate, and wherein said electrically conductive
material is coated on said substrate.
3. The surgical instrument of claim 1, wherein said flexible mesh
comprises a substrate, and wherein said electrically conductive
material is perfused within said substrate.
4. The surgical instrument of claim 1, wherein said support member
comprises a first portion and a second portion, and wherein said
flexible mesh extends between said first portion and said second
portion.
5. The surgical instrument of claim 1, wherein said support member
comprises a perimeter, and wherein said flexible mesh is attached
to said support member along said perimeter.
6. A surgical instrument kit, comprising: a first instrument
comprising a first electrode; and a second instrument, comprising:
a shaft comprising a conductor; and a second electrode, comprising:
a support member mounted to said shaft; and a flexible mesh
comprising an electrically conductive material, wherein said
support member is configured to support at least a portion of said
flexible mesh, and wherein said flexible mesh is in electrical
communication with said conductor.
7. The surgical instrument kit of claim 6, wherein said flexible
mesh comprises a substrate, and wherein said electrically
conductive material is coated on said substrate.
8. The surgical instrument kit of claim 6, wherein said flexible
mesh comprises a substrate, and wherein said electrically
conductive material is perfused within said substrate.
9. The surgical instrument kit of claim 6, wherein said support
member comprises a first portion and a second portion, and wherein
said flexible mesh extends between said first portion and said
second portion.
10. The surgical instrument kit of claim 6, wherein said support
member comprises a perimeter, and wherein said flexible mesh is
attached to said support member along said perimeter.
Description
CROSS REFERENCE TO RELATED APPLICATIONS
[0001] This application is a divisional application claiming
priority under 35 U.S.C. .sctn. 121 to U.S. patent application Ser.
No. 14/695,824, entitled SURGICAL INSTRUMENT COMPRISING AN
ELECTRODE, filed Apr. 24, 2015, now U.S. Patent Application
Publication No. 2015/0230858, which is a divisional application
claiming priority under 35 U.S.C. .sctn. 121 to U.S. patent
application Ser. No. 12/641,837, entitled SURGICAL INSTRUMENT
COMPRISING AN ELECTRODE, filed Dec. 18, 2009, now U.S. Pat. No.
9,028,483, the entire disclosures of which are hereby incorporated
by reference herein.
BACKGROUND
i. Field of the Invention
[0002] The present invention generally relates to surgical devices
and methods.
ii. Description of the Related Art
[0003] Traditional, or open, surgical techniques may require a
surgeon to make large incisions in a patient's body in order to
access a tissue treatment region, or surgical site. In some
instances, these large incisions may prolong the recovery time of
and/or increase the scarring to the patient. As a result, minimally
invasive surgical techniques are becoming more preferred among
surgeons and patients owing to the reduced size of the incisions
required for various procedures. In some circumstances, minimally
invasive surgical techniques may reduce the possibility that the
patient will suffer undesirable post-surgical conditions, such as
scarring and/or infections, for example. Further, such minimally
invasive techniques can allow the patient to recover more rapidly
as compared to traditional surgical procedures.
[0004] Endoscopy is one minimally invasive surgical technique which
allows a surgeon to view and evaluate a surgical site by inserting
at least one cannula, or trocar, into the patient's body through a
natural opening in the body and/or through a relatively small
incision. In use, an endoscope can be inserted into, or through,
the trocar so that the surgeon can observe the surgical site. In
various embodiments, the endoscope may include a flexible or rigid
shaft, a camera and/or other suitable optical device, and a handle
portion. In at least one embodiment, the optical device can be
located on a first, or distal, end of the shaft and the handle
portion can be located on a second, or proximal, end of the shaft.
In various embodiments, the endoscope may also be configured to
assist a surgeon in taking biopsies, retrieving foreign objects,
and introducing surgical instruments into the surgical site.
[0005] Laparoscopic surgery is another minimally invasive surgical
technique where procedures in the abdominal or pelvic cavities can
be performed through small incisions in the patient's body. A key
element of laparoscopic surgery is the use of a laparoscope which
typically includes a telescopic lens system that can be connected
to a video camera. In various embodiments, a laparoscope can
further include a fiber optic system connected to a halogen or
xenon light source, for example, in order to illuminate the
surgical site. In various laparoscopic, and/or endoscopic, surgical
procedures, a body cavity of a patient, such as the abdominal
cavity, for example, can be insufflated with carbon dioxide gas,
for example, in order to create a temporary working space for the
surgeon. In such procedures, a cavity wall can be elevated above
the organs within the cavity by the carbon dioxide gas. Carbon
dioxide gas is usually used for insufflation because it can be
easily absorbed and removed by the body.
[0006] In at least one minimally invasive surgical procedure, an
endoscope and/or laparoscope can be inserted through a natural
opening of a patient to allow a surgeon to access a surgical site.
Such procedures are generally referred to as Nature Orifice
Transluminal Endoscopic Surgery or (NOTES).TM. and can be utilized
to treat tissue while reducing the number of incisions, and
external scars, to a patient's body. In various NOTES procedures,
for example, an endoscope can include at least one working channel
defined therein which can be used to allow the surgeon to insert a
surgical instrument therethrough in order to access the surgical
site.
[0007] The foregoing discussion is intended only to illustrate
various aspects of the related art in the field of the invention at
the time, and should not be taken as a disavowal of claim
scope.
FIGURES
[0008] Various features of the embodiments described herein are set
forth with particularity in the appended claims. The various
embodiments, however, both as to organization and methods of
operation, together with advantages thereof, may be understood in
accordance with the following description taken in conjunction with
the accompanying drawings as follows.
[0009] FIG. 1 illustrates one embodiment of an electrical ablation
system.
[0010] FIGS. 2A-D illustrate one embodiment of the electrical
ablation system in various phases of deployment.
[0011] FIG. 2E illustrates one embodiment of the electrical
ablation device comprising multiple needle electrodes.
[0012] FIG. 3 illustrates one embodiment of the electrical ablation
system shown in FIGS. 1 and 2A-D in use to treat undesirable tissue
located on the surface of the liver.
[0013] FIG. 4 is a cross-sectional view of a surgical instrument
comprising a first electrode, a second electrode, and a retractable
sheath movable relative to the first electrode and the second
electrode.
[0014] FIG. 5 is a perspective view of a distal end of the surgical
instrument of FIG. 4 illustrating the sheath in an extended
position.
[0015] FIG. 6 is a perspective view of a distal end of the surgical
instrument of FIG. 4 illustrating the sheath in a retracted
position.
[0016] FIG. 7 is a perspective view of a distal end of an
alternative embodiment of a surgical instrument illustrating a
first electrode, a second electrode, and insulative jackets
positioned around the first electrode and the second electrode.
[0017] FIG. 8 is a cross-sectional view of the surgical instrument
of FIG. 7 illustrating the first and second electrodes positioned
within tissue and the insulative jackets positioned against the
tissue.
[0018] FIG. 9 is a perspective view of a distal end of an
alternative embodiment of a surgical instrument illustrating a
first electrode, a second electrode, and an insulative guard,
wherein the insulative guard is movable between an extended
positioned in which it is positioned intermediate the distal ends
of the first electrode and the second electrode and a retracted
position in which it is displaced proximally relative to the distal
ends of the first and second electrodes.
[0019] FIG. 10 is a cross-sectional view of the surgical instrument
of FIG. 9 illustrating the distal ends of the first and second
electrodes positioned against tissue and the insulative guard in
its extended position.
[0020] FIG. 11 is a cross-sectional view of the surgical instrument
of FIG. 9 illustrating the distal ends of the first and second
electrodes inserted into the tissue and the insulative guard in a
retracted position.
[0021] FIG. 12 is a perspective view of a distal end of an
alternative embodiment of a surgical instrument comprising a
flexible electrode.
[0022] FIG. 13 illustrates the surgical instrument of FIG. 12
positioned against the liver of a patient at one location and an
additional surgical instrument comprising an electrode positioned
against the liver at another location.
[0023] FIG. 14 illustrates the necrotic regions of liver tissue
which can be created by the surgical instrument of FIG. 12 and the
additional surgical instrument of FIG. 13.
[0024] FIG. 15 is another illustration of the necrotic regions of
liver tissue which can be created by the surgical instrument of
FIG. 12 and the additional surgical instrument of FIG. 13.
[0025] FIG. 16 illustrates an alternative embodiment of a surgical
instrument comprising a flexible balloon positioned against the
liver of a patient.
[0026] FIG. 17 is a perspective view of a distal end of a surgical
instrument.
[0027] FIG. 18 is an end view of the surgical instrument of FIG.
17.
[0028] FIG. 19 is a graph of the voltage field that can be
generated by the surgical instrument of FIG. 17.
[0029] FIG. 20 is an elevational view of a distal end of a surgical
instrument.
[0030] FIG. 21 is an end view of the surgical instrument of FIG.
20.
[0031] Corresponding reference characters indicate corresponding
parts throughout the several views. The exemplifications set out
herein illustrate various embodiments of the invention, in one
form, and such exemplifications are not to be construed as limiting
the scope of the invention in any manner.
DESCRIPTION
[0032] Various embodiments are directed to apparatuses, systems,
and methods for the electrical ablation treatment of undesirable
tissue such as diseased tissue, cancer, malignant and benign
tumors, masses, lesions, and other abnormal tissue growths.
Numerous specific details are set forth to provide a thorough
understanding of the overall structure, function, manufacture, and
use of the embodiments as described in the specification and
illustrated in the accompanying drawings. It will be understood by
those skilled in the art, however, that the embodiments may be
practiced without such specific details. In other instances,
well-known operations, components, and elements have not been
described in detail so as not to obscure the embodiments described
in the specification. Those of ordinary skill in the art will
understand that the embodiments described and illustrated herein
are non-limiting examples, and thus it can be appreciated that the
specific structural and functional details disclosed herein may be
representative and do not necessarily limit the scope of the
embodiments, the scope of which is defined solely by the appended
claims.
[0033] Reference throughout the specification to "various
embodiments," "some embodiments," "one embodiment," or "an
embodiment", or the like, means that a particular feature,
structure, or characteristic described in connection with the
embodiment is included in at least one embodiment. Thus,
appearances of the phrases "in various embodiments," "in some
embodiments," "in one embodiment," or "in an embodiment", or the
like, in places throughout the specification are not necessarily
all referring to the same embodiment. Furthermore, the particular
features, structures, or characteristics may be combined in any
suitable manner in one or more embodiments. Thus, the particular
features, structures, or characteristics illustrated or described
in connection with one embodiment may be combined, in whole or in
part, with the features structures, or characteristics of one or
more other embodiments without limitation.
[0034] It will be appreciated that the terms "proximal" and
"distal" may be used throughout the specification with reference to
a clinician manipulating one end of an instrument used to treat a
patient. The term "proximal" refers to the portion of the
instrument closest to the clinician and the term "distal" refers to
the portion located furthest from the clinician. It will be further
appreciated that for conciseness and clarity, spatial terms such as
"vertical," "horizontal," "up," and "down" may be used herein with
respect to the illustrated embodiments. However, surgical
instruments may be used in many orientations and positions, and
these terms are not intended to be limiting and absolute.
[0035] Electrical ablation devices in accordance with the described
embodiments may comprise one or more electrodes configured to be
positioned into or proximal to undesirable tissue in a tissue
treatment region (e.g., target site, worksite) where there is
evidence of abnormal tissue growth, for example. In general, the
electrodes comprise an electrically conductive portion (e.g.,
medical grade stainless steel) and are configured to electrically
couple to an energy source. Once the electrodes are positioned into
or proximal to the undesirable tissue, an energizing potential is
applied to the electrodes to create an electric field to which the
undesirable tissue is exposed. The energizing potential (and the
resulting electric field) may be characterized by multiple
parameters such as frequency, amplitude, pulse width (duration of a
pulse or pulse length), and/or polarity. Depending on the
diagnostic or therapeutic treatment to be rendered, a particular
electrode may be configured either as an anode (+) or a cathode (-)
or may comprise a plurality of electrodes with at least one
configured as an anode and at least one other configured as a
cathode. Regardless of the initial polar configuration, the
polarity of the electrodes may be reversed by reversing the
polarity of the output of the energy source.
[0036] In various embodiments, a suitable energy source may
comprise an electrical waveform generator, which may be configured
to create an electric field that is suitable to create irreversible
electroporation in undesirable tissue at various electric filed
amplitudes and durations. The energy source may be configured to
deliver irreversible electroporation pulses in the form of
direct-current (DC) and/or alternating-current (AC) voltage
potentials (e.g., time-varying voltage potentials) to the
electrodes. The irreversible electroporation pulses may be
characterized by various parameters such as frequency, amplitude,
pulse length, and/or polarity. The undesirable tissue may be
ablated by exposure to the electric potential difference across the
electrodes.
[0037] In one embodiment, the energy source may comprise a wireless
transmitter to deliver energy to the electrodes using wireless
energy transfer techniques via one or more remotely positioned
antennas. Those skilled in the art will appreciate that wireless
energy transfer or wireless power transmission is the process of
transmitting electrical energy from an energy source to an
electrical load without interconnecting wires. An electrical
transformer is the simplest instance of wireless energy transfer.
The primary and secondary circuits of a transformer are not
directly connected and the transfer of energy takes place by
electromagnetic coupling through a process known as mutual
induction. Power also may be transferred wirelessly using RF
energy. Wireless power transfer technology using RF energy is
produced by Powercast, Inc. and can achieve an output of 6 volts
for a little over one meter. Other low-power wireless power
technology has been proposed such as described in U.S. Pat. No.
6,967,462, the entire disclosure of which is incorporated by
reference herein.
[0038] The apparatuses, systems, and methods in accordance with
certain described embodiments may be configured for minimally
invasive ablation treatment of undesirable tissue through the use
of irreversible electroporation to be able to ablate undesirable
tissue in a controlled and focused manner without inducing
thermally damaging effects to the surrounding healthy tissue. The
apparatuses, systems, and methods in accordance with the described
embodiments may be configured to ablate undesirable tissue through
the use of electroporation or electropermeabilization. More
specifically, in various embodiments, the apparatuses, systems, and
methods in accordance with the described embodiments may be
configured to ablate undesirable tissue through the use of
irreversible electroporation. Electroporation increases the
permeabilization of a cell membrane by exposing the cell to
electric pulses. The external electric field (electric
potential/per unit length) to which the cell membrane is exposed to
significantly increases the electrical conductivity and
permeability of the plasma in the cell membrane. The primary
parameter affecting the transmembrane potential is the potential
difference across the cell membrane. Irreversible electroporation
is the application of an electric field of a specific magnitude and
duration to a cell membrane such that the permeabilization of the
cell membrane cannot be reversed, leading to cell death without
inducing a significant amount of heat in the surrounding tissue.
The destabilizing potential forms pores in the cell membrane when
the potential across the cell membrane exceeds its critical
membrane voltage causing the cell to die under a process known as
apoptosis and/or necrosis. The application of irreversible
electroporation pulses to cells is an effective way for ablating
large volumes of undesirable tissue without deleterious thermal
effects to the surrounding healthy tissue associated with
thermal-inducing ablation treatments. This is because irreversible
electroporation destroys cells without heat and thus does not
destroy the cellular support structure or regional vasculature. A
destabilizing irreversible electroporation pulse, suitable to cause
cell death without inducing a significant amount of thermal damage
to the surrounding healthy tissue, may have amplitude in the range
of about several hundred to about several thousand volts and is
generally applied across biological membranes over a distance of
about several millimeters, for example, for a relatively long
duration. Thus, the undesirable tissue may be ablated in-vivo
through the delivery of destabilizing electric fields by quickly
creating cell necrosis.
[0039] The apparatuses, systems, and methods for electrical
ablation therapy in accordance with the described embodiments may
be adapted for use in minimally invasive surgical procedures to
access the tissue treatment region in various anatomic locations
such as the brain, lungs, breast, liver, gall bladder, pancreas,
prostate gland, and various internal body lumen defined by the
esophagus, stomach, intestine, colon, arteries, veins, anus,
vagina, cervix, fallopian tubes, and the peritoneal cavity, for
example, without limitation. Minimally invasive electrical ablation
devices may be introduced to the tissue treatment region using a
trocar inserted though a small opening formed in the patient's body
or through a natural body orifice such as the mouth, anus, or
vagina using translumenal access techniques known as Natural
Orifice Translumenal Endoscopic Surgery (NOTES).TM.. Once the
electrical ablation devices (e.g., electrodes) are located into or
proximal to the undesirable tissue in the treatment region,
electric field potentials can be applied to the undesirable tissue
by the energy source. The electrical ablation devices can comprise
portions that may be inserted into the tissue treatment region
percutaneously (e.g., where access to inner organs or other tissue
is done via needle-puncture of the skin). Other portions of the
electrical ablation devices may be introduced into the tissue
treatment region endoscopically (e.g., laparoscopically and/or
thoracoscopically) through trocars or working channels of the
endoscope, through small incisions, or transcutaneously (e.g.,
where electric pulses are delivered to the tissue treatment region
through the skin).
[0040] FIG. 1 illustrates one embodiment of an electrical ablation
system 10. The electrical ablation system 10 may be employed to
ablate undesirable tissue such as diseased tissues, cancers,
tumors, masses, lesions, abnormal tissue growths inside a patient
using electrical energy. The electrical ablation system 10 may be
used in conjunction with endoscopic, laparoscopic, thoracoscopic,
open surgical procedures via small incisions or keyholes,
percutaneous techniques, transcutaneous techniques, and/or external
non-invasive techniques, or any combinations thereof without
limitation. The electrical ablation system 10 may be configured to
be positioned within a natural body orifice of the patient such as
the mouth, anus, or vagina and advanced through internal body lumen
or cavities such as the esophagus, colon, cervix, urethra, for
example, to reach the tissue treatment region. The electrical
ablation system 10 also may be configured to be positioned and
passed through a small incision or keyhole formed through the skin
or abdominal wall of the patient to reach the tissue treatment
region using a trocar. The tissue treatment region may be located
in the brain, lungs, breast, liver, gall bladder, pancreas,
prostate gland, various internal body lumen defined by the
esophagus, stomach, intestine, colon, arteries, veins, anus,
vagina, cervix, fallopian tubes, and the peritoneal cavity, for
example, without limitation. The electrical ablation system 10 can
be configured to treat a number of lesions and ostepathologies
comprising metastatic lesions, tumors, fractures, infected sites,
and/or inflamed sites. Once positioned into or proximate the tissue
treatment region, the electrical ablation system 10 can be actuated
(e.g., energized) to ablate the undesirable tissue. In one
embodiment, the electrical ablation system 10 may be configured to
treat diseased tissue in the gastrointestinal (GI) tract,
esophagus, lung, or stomach that may be accessed orally. In another
embodiment, the electrical ablation system 10 may be adapted to
treat undesirable tissue in the liver or other organs that may be
accessible using translumenal access techniques such as, without
limitation, NOTES.TM. techniques, where the electrical ablation
devices may be initially introduced through a natural orifice such
as the mouth, anus, or vagina and then advanced to the tissue
treatment site by puncturing the walls of internal body lumen such
as the stomach, intestines, colon, cervix. In various embodiments,
the electrical ablation system 10 may be adapted to treat
undesirable tissue in the brain, liver, breast, gall bladder,
pancreas, or prostate gland, using one or more electrodes
positioned percutaneously, transcutaneously, translumenally,
minimally invasively, and/or through open surgical techniques, or
any combination thereof.
[0041] In one embodiment, the electrical ablation system 10 may be
employed in conjunction with a flexible endoscope 12, as well as a
rigid endoscope, laparoscope, or thoracoscope, such as the GIF-100
model available from Olympus Corporation. In one embodiment, the
endoscope 12 may be introduced to the tissue treatment region
trans-anally through the colon, trans-orally through the esophagus
and stomach, trans-vaginally through the cervix, transcutaneously,
or via an external incision or keyhole formed in the abdomen in
conjunction with a trocar. The electrical ablation system 10 may be
inserted and guided into or proximate the tissue treatment region
using the endoscope 12.
[0042] In the embodiment illustrated in FIG. 1, the endoscope 12
comprises an endoscope handle 34 and an elongate relatively
flexible shaft 32. The distal end of the flexible shaft 32 may
comprise a light source and a viewing port. Optionally, the
flexible shaft 32 may define one or more working channels for
receiving various instruments, such as electrical ablation devices,
for example, therethrough. Images within the field of view of the
viewing port are received by an optical device, such as a camera
comprising a charge coupled device (CCD) usually located within the
endoscope 12, and are transmitted to a display monitor (not shown)
outside the patient.
[0043] In one embodiment, the electrical ablation system 10 may
comprise an electrical ablation device 20, a plurality of
electrical conductors 18, a handpiece 16 comprising an activation
switch 62, and an energy source 14, such as an electrical waveform
generator, electrically coupled to the activation switch 62 and the
electrical ablation device 20. The electrical ablation device 20
comprises a relatively flexible member or shaft 22 that may be
introduced to the tissue treatment region using a variety of known
techniques such as an open incision and a trocar, through one of
more of the working channels of the endoscope 12, percutaneously,
or transcutaneously, for example.
[0044] In one embodiment, one or more electrodes (e.g., needle
electrodes, balloon electrodes), such as first and second
electrodes 24a,b, extend out from the distal end of the electrical
ablation device 20. In one embodiment, the first electrode 24a may
be configured as the positive electrode and the second electrode
24b may be configured as the negative electrode. The first
electrode 24a is electrically connected to a first electrical
conductor 18a, or similar electrically conductive lead or wire,
which is coupled to the positive terminal of the energy source 14
through the activation switch 62. The second electrode 24b is
electrically connected to a second electrical conductor 18b, or
similar electrically conductive lead or wire, which is coupled to
the negative terminal of the energy source 14 through the
activation switch 62. The electrical conductors 18a,b are
electrically insulated from each other and surrounding structures,
except for the electrical connections to the respective electrodes
24a,b. In various embodiments, the electrical ablation device 20
may be configured to be introduced into or proximate the tissue
treatment region using the endoscope 12 (laparoscope or
thoracoscope), open surgical procedures, or external and
non-invasive medical procedures. The electrodes 24a,b may be
referred to herein as endoscopic or laparoscopic electrodes,
although variations thereof may be inserted transcutaneously or
percutaneously. As previously discussed, either one or both
electrodes 24a,b may be adapted and configured to slideably move in
and out of a cannula, lumen, or channel defined within the flexible
shaft 22.
[0045] Once the electrodes 24a,b are positioned at the desired
location into or proximate the tissue treatment region, the
electrodes 24a,b may be connected to or disconnected from the
energy source 14 by actuating or de-actuating the switch 62 on the
handpiece 16. The switch 62 may be operated manually or may be
mounted on a foot switch (not shown), for example. The electrodes
24a,b deliver electric field pulses to the undesirable tissue. The
electric field pulses may be characterized based on various
parameters such as pulse shape, amplitude, frequency, and duration.
The electric field pulses may be sufficient to induce irreversible
electroporation in the undesirable tissue. The induced potential
depends on a variety of conditions such as tissue type, cell size,
and electrical pulse parameters. The primary electrical pulse
parameter affecting the transmembrane potential for a specific
tissue type is the amplitude of the electric field and pulse length
that the tissue is exposed to.
[0046] In one embodiment, a protective sleeve or sheath 26 may be
slideably disposed over the flexible shaft 22 and within a handle
28. In another embodiment, the sheath 26 may be slideably disposed
within the flexible shaft 22 and the handle 28, without limitation.
The sheath 26 is slideable and may be located over the electrodes
24a,b to protect the trocar and prevent accidental piercing when
the electrical ablation device 20 is advanced therethrough. Either
one or both of the electrodes 24a,b of the electrical ablation
device 20 may be adapted and configured to slideably move in and
out of a cannula, lumen, or channel formed within the flexible
shaft 22. The second electrode 24b may be fixed in place. The
second electrode 24b may provide a pivot about which the first
electrode 24a can be moved in an arc to other points in the tissue
treatment region to treat larger portions of the diseased tissue
that cannot be treated by fixing the electrodes 24a,b in one
location. In one embodiment, either one or both of the electrodes
24a,b may be adapted and configured to slideably move in and out of
a working channel formed within a flexible shaft 32 of the flexible
endoscope 12 or may be located independently of the flexible
endoscope 12. Various features of the first and second electrodes
24a,b are described in more detail in FIGS. 2A-D.
[0047] In one embodiment, the first and second electrical
conductors 18a,b may be provided through the handle 28. In the
illustrated embodiment, the first electrode 24a can be slideably
moved in and out of the distal end of the flexible shaft 22 using a
slide member 30 to retract and/or advance the first electrode 24a.
In various embodiments either or both electrodes 24a,b may be
coupled to the slide member 30, or additional slide members, to
advance and retract the electrodes 24a,b, e.g., position the
electrodes 24a,b. In the illustrated embodiment, the first
electrical conductor 18a coupled to the first electrode 24a is
coupled to the slide member 30. In this manner, the first electrode
24a, which is slideably movable within the cannula, lumen, or
channel defined by the flexible shaft 22, can advanced and
retracted with the slide member 30.
[0048] In various other embodiments, transducers or sensors may be
located in the handle 28 of the electrical ablation device 20 to
sense the force with which the electrodes 24a,b penetrate the
tissue in the tissue treatment zone. This feedback information may
be useful to determine whether either one or both of the electrodes
24a,b have been properly inserted in the tissue treatment region.
As is particularly well known, cancerous tumor tissue tends to be
denser than healthy tissue and thus greater force is required to
insert the electrodes 24a,b therein. The transducers or sensors 29
can provide feedback to the operator, surgeon, or clinician to
physically sense when the electrodes 24a,b are placed within the
cancerous tumor. The feedback information provided by the
transducers or sensors 29 may be processed and displayed by
circuits located either internally or externally to the energy
source 14. The sensor 29 readings may be employed to determine
whether the electrodes 24a,b have been properly located within the
cancerous tumor thereby assuring that a suitable margin of error
has been achieved in locating the electrodes 24a,b.
[0049] In one embodiment, the input to the energy source 14 may be
connected to a commercial power supply by way of a plug (not
shown). The output of the energy source 14 is coupled to the
electrodes 24a,b, which may be energized using the activation
switch 62 on the handpiece 16, or in one embodiment, an activation
switch mounted on a foot activated pedal (not shown). The energy
source 14 may be configured to produce electrical energy suitable
for electrical ablation, as described in more detail below.
[0050] In one embodiment, the electrodes 24a,b are adapted and
configured to electrically couple to the energy source 14 (e.g.,
generator, waveform generator). Once electrical energy is coupled
to the electrodes 24a,b, an electric field is formed in the tissue
from the voltage applied at the electrodes 24a,b. The energy source
14 may be configured to generate electric pulses at a predetermined
frequency, amplitude, pulse length, and/or polarity that are
suitable to induce irreversible electroporation to ablate
substantial volumes of undesirable tissue in the treatment region.
For example, the energy source 14 may be configured to deliver DC
electric pulses having a predetermined frequency, amplitude, pulse
length, and/or polarity suitable to induce irreversible
electroporation to ablate substantial volumes of undesirable tissue
in the treatment region. The DC pulses may be positive or negative
relative to a particular reference polarity. The polarity of the DC
pulses may be reversed or inverted from positive-to-negative or
negative-to-positive a predetermined number of times to induce
irreversible electroporation to ablate substantial volumes of
undesirable tissue in the treatment region.
[0051] In one embodiment, a timing circuit may be coupled to the
output of the energy source 14 to generate electric pulses. The
timing circuit may comprise one or more suitable switching elements
to produce the electric pulses. For example, the energy source 14
may produce a series of n electric pulses (where n is any positive
integer) of sufficient amplitude and duration to induce
irreversible electroporation suitable for tissue ablation when the
n electric pulses are applied to the electrodes 24a,b. In one
embodiment, the electric pulses may have a fixed or variable pulse
length, amplitude, and/or frequency.
[0052] The electrical ablation device 20 may be operated either in
bipolar or monopolar mode. In bipolar mode, the first electrode 24a
is electrically connected to a first polarity and the second
electrode 24b is electrically connected to the opposite polarity.
For example, in monopolar mode, the first electrode 24a is coupled
to a prescribed voltage and the second electrode 24b is set to
ground. In the illustrated embodiment, the energy source 14 may be
configured to operate in either the bipolar or monopolar modes with
the electrical ablation system 10. In bipolar mode, the first
electrode 24a is electrically connected to a prescribed voltage of
one polarity and the second electrode 24b is electrically connected
to a prescribed voltage of the opposite polarity. When more than
two electrodes are used, the polarity of the electrodes may be
alternated so that any two adjacent electrodes may have either the
same or opposite polarities, for example.
[0053] In monopolar mode, it is not necessary that the patient be
grounded with a grounding pad. Since a monopolar energy source 14
is typically constructed to operate upon sensing a ground pad
connection to the patient, the negative electrode of the energy
source 14 may be coupled to an impedance simulation circuit. In
this manner, the impedance circuit simulates a connection to the
ground pad and thus is able to activate the energy source 14. It
will be appreciated that in monopolar mode, the impedance circuit
can be electrically connected in series with either one of the
electrodes 24a,b that would otherwise be attached to a grounding
pad.
[0054] In one embodiment, the energy source 14 may be configured to
produce RF waveforms at predetermined frequencies, amplitudes,
pulse widths or durations, and/or polarities suitable for
electrical ablation of cells in the tissue treatment region. One
example of a suitable RF energy source is a commercially available
conventional, bipolar/monopolar electrosurgical RF generator such
as Model Number ICC 350, available from Erbe, GmbH.
[0055] In one embodiment, the energy source 14 may be configured to
produce destabilizing electrical potentials (e.g., fields) suitable
to induce irreversible electroporation. The destabilizing
electrical potentials may be in the form of bipolar/monopolar DC
electric pulses suitable for inducing irreversible electroporation
to ablate tissue undesirable tissue with the electrical ablation
device 20. A commercially available energy source suitable for
generating irreversible electroporation electric field pulses in
bipolar or monopolar mode is a pulsed DC generator such as Model
Number ECM 830, available from BTX Molecular Delivery Systems
Boston, Mass. In bipolar mode, the first electrode 24a may be
electrically coupled to a first polarity and the second electrode
24b may be electrically coupled to a second (e.g., opposite)
polarity of the energy source 14. Bipolar/monopolar DC electric
pulses may be produced at a variety of frequencies, amplitudes,
pulse lengths, and/or polarities. Unlike RF ablation systems,
however, which require high power and energy levels delivered into
the tissue to heat and thermally destroy the tissue, irreversible
electroporation requires very little energy input into the tissue
to kill the undesirable tissue without the detrimental thermal
effects because with irreversible electroporation the cells are
destroyed by electric field potentials rather than heat.
[0056] In one embodiment, the energy source 14 may be coupled to
the first and second electrodes 24a,b by either a wired or a
wireless connection. In a wired connection, the energy source 14 is
coupled to the electrodes 24a,b by way of the electrical conductors
18a,b, as shown. In a wireless connection, the electrical
conductors 18a,b may be replaced with a first antenna (not shown)
coupled the energy source 14 and a second antenna (not shown)
coupled to the electrodes 24a,b, wherein the second antenna is
remotely located from the first antenna.
[0057] In one embodiment, the energy source may comprise a wireless
transmitter to deliver energy to the electrodes using wireless
energy transfer techniques via one or more remotely positioned
antennas. As previously discussed, wireless energy transfer or
wireless power transmission is the process of transmitting
electrical energy from the energy source 14 to an electrical load,
e.g., the abnormal cells in the tissue treatment region, without
using the interconnecting electrical conductors 18a,b. An
electrical transformer is the simplest instance of wireless energy
transfer. The primary and secondary circuits of a transformer are
not directly connected. The transfer of energy takes place by
electromagnetic coupling through a process known as mutual
induction. Wireless power transfer technology using RF energy is
produced by Powercast, Inc. The Powercast system can achieve a
maximum output of 6 volts for a little over one meter. Other
low-power wireless power technology has been proposed such as
described in U.S. Pat. No. 6,967,462.
[0058] In one embodiment, the energy source 14 may be configured to
produce DC electric pulses at frequencies in the range of about 1
Hz to about 10000 Hz, amplitudes in the range of about .+-.100 to
about .+-.3000 VDC, and pulse lengths (e.g., pulse width, pulse
duration) in the range of about 1 .mu.s to about 100 ms. The
polarity of the electric potentials coupled to the electrodes 24a,b
may be reversed during the electrical ablation therapy. For
example, initially, the DC electric pulses may have a positive
polarity and an amplitude in the range of about +100 to about +3000
VDC. Subsequently, the polarity of the DC electric pulses may be
reversed such that the amplitude is in the range of about -100 to
about -3000 VDC. In one embodiment, the undesirable cells in the
tissue treatment region may be electrically ablated with DC pulses
suitable to induce irreversible electroporation at frequencies of
about 10 Hz to about 100 Hz, amplitudes in the range of about +700
to about +1500 VDC, and pulse lengths of about 10 .mu.s to about 50
.mu.s. In another embodiment, the abnormal cells in the tissue
treatment region may be electrically ablated with an electrical
waveform having an amplitude of about +500 VDC and pulse duration
of about 20 ms delivered at a pulse period T or repetition rate,
frequency f=1/T, of about 10 Hz. It has been determined that an
electric field strength of 1,000V/cm is suitable for destroying
living tissue by inducing irreversible electroporation.
[0059] FIGS. 2A-D illustrate one embodiment of the electrical
ablation device 20 in various phases of deployment. In the
embodiment illustrated in FIGS. 2A-D, the sheath 26 is disposed
over the flexible shaft 22, however, those skilled in the art will
appreciate that the sheath 26 may be disposed within the flexible
shaft 22. The electrical ablation device 20 may be used in
conjunction with the electrical ablation system 10 shown in FIG. 1.
It will be appreciated that other devices and electrode
configurations may be employed without limitation. FIG. 2A
illustrates an initial phase of deployment wherein the sheath 26 is
extended in the direction indicated by arrow 40 to cover the
electrodes 24a,b. The electrodes 24a,b may have dimensions of about
0.5 mm, about 1 mm, or about 1.5 mm in diameter. It will be
appreciated that the dimensions of the electrodes 24a,b may be
anywhere from about 0.5 mm to about 1.5 mm in diameter. The
electrical ablation device 20 may be introduced into the tissue
treatment region through a trocar, as illustrated in FIG. 3, for
example. FIG. 2B illustrates another phase of deployment wherein
the sheath 26 is retracted within the handle 28 in the direction
indicated by arrow 42. In this phase of deployment, the first and
second electrodes 24a,b extend through the distal end of the
flexible shaft 22 and are ready to be inserted into or proximate
the tissue treatment region. The first electrode 24a may be
retracted in direction 42 through a lumen 44 formed in the flexible
shaft 22 by holding the handle 28 and pulling on the slide member
30. FIG. 2C illustrates a transition phase wherein the first
electrode 24a is the process of being retracted in direction 42 by
pulling on the slide member 30 handle, for example, in the same
direction. FIG. 2D illustrates another phase of deployment wherein
the first electrode 24a is in a fully retracted position. In this
phase of deployment the electrical ablation device 20 can be
pivotally rotated about an axis 46 defined by the second electrode
24b. The electrodes 24a,b are spaced apart by a distance "r." The
distance "r" between the electrodes 24a,b may be 5.0 mm, about 7.5
mm, or about 10 mm. It will be appreciated that the distance "r"
between the electrodes 24a,b may be anywhere from about 5.0 mm to
about 10.0 mm. Thus, the electrical ablation device 20 may be
rotated in an arc about the pivot formed by the second electrode
24b, the first electrode 24a may be placed in a new location in the
tissue treatment region within the radius "r." Retracting the first
electrode 24a and pivoting about the second electrode 24b enables
the surgeon or clinician to target and treat a larger tissue
treatment region essentially comprising a circular region having a
radius "r," which is the distance between the electrodes 24a,b.
Thus, the electrodes 24a,b may be located in a plurality of
positions in and around the tissue treatment region in order to
treat much larger regions of tissue. Increasing the electrode 24a,b
diameter and spacing the electrodes 24a,b further apart enables the
generation of an electric field over a much larger tissue regions
and thus the ablation of larger volumes of undesirable tissue. In
this manner, the operator can treat a larger tissue treatment
region comprising cancerous lesions, polyps, or tumors, for
example.
[0060] Although the electrical ablation electrodes according to the
described embodiments have been described in terms of the
particular needle type electrodes 24a,b as shown and described in
FIGS. 1 and 2A-D, those skilled in the art will appreciate that
other configurations of electrical ablation electrodes may be
employed for the ablation of undesirable tissue, without
limitation. In one embodiment, the electrical ablation device 20
may comprise two or more fixed electrodes that are non-retractable.
In another embodiment, the electrical ablation device 20 may
comprise two or more retractable electrodes, one embodiment of
which is described below with reference to FIG. 2E. In another
embodiment, the electrical ablation device 20 may comprise at least
one slideable electrode disposed within at least one working
channel of the flexible shaft 32 of the endoscope 12. In another
embodiment, the electrical ablation device 20 may comprise at least
one electrode may be configured to be inserted into the tissue
treatment region transcutaneously or percutaneously. Still in
various other embodiments, the electrical ablation device 20 may
comprise at least one electrode configured to be introduced to the
tissue treatment region transcutaneously or percutaneously and at
least one other electrode may be configured to be introduced to the
tissue treatment region through at least one working channel of the
flexible shaft 32 of the endoscope 12. The embodiments, however,
are not limited in this context.
[0061] FIG. 2E illustrates one embodiment of an electrical ablation
device 100 comprising multiple needle electrodes 124m, where m is
any positive integer. In the illustrated embodiment, the electrical
ablation device 100 comprises four electrodes 124a, 124b, 124c,
124d. It will be appreciated that in one embodiment, the electrical
ablation device 800 also may comprise three needle electrodes 124a,
124b, 124c, without limitation. The electrical ablation device 100
may be used in conjunction with the electrical ablation system 10
shown in FIG. 1. It will be appreciated that other devices and
electrode configurations may be employed without limitation. The
electrodes 124a-m each may have dimensions of about 0.5 mm, about 1
mm, or about 1.5 mm in diameter. It will be appreciated that the
dimensions of each of the electrodes 124a-m may be anywhere from
about 0.5 mm to about 1.5 mm in diameter. The electrical ablation
device 100 may be introduced into the tissue treatment region
through a trocar, as subsequently described and illustrated with
reference to FIG. 3, for example.
[0062] The electrical ablation device 100 comprises essentially the
same components as the electrical ablation device 20 described with
reference to FIGS. 2A-D. The electrical ablation device 100
comprises the relatively flexible member or shaft 22, the
protective sheath 26, and one or more handles 28 to operate either
the sheath 26, the electrodes 124a,b,c,d, or both. The electrodes
124a,b,c,d may be individually or simultaneously deployable and/or
retractable in the direction indicated by arrow 142. The electrodes
124a,b,c,d extend out from the distal end of the electrical
ablation device 100. In one embodiment, the first and second
electrodes 124a, 124b may be configured as the positive electrode
coupled to the anode of the energy source 14 via corresponding
first and second electrical conductors 118a, 118b, and the third
and fourth electrodes 124c, 124d may be configured as the negative
electrode coupled to the cathode of the energy source 14 via
corresponding third and fourth electrical conductors 118c, 118d, or
similar electrically conductive leads or wires, through the
activation switch 62. Once the electrodes 124a,b,c,d are positioned
at the desired location into or proximate the tissue treatment
region, the electrodes 124a,b,c,d may be connected/disconnected
from the energy source 14 by actuating/de-actuating the switch
62.
[0063] As previously discussed with reference to FIGS. 2A-D, as
shown in FIG. 2E in one embodiment, the protective sleeve or sheath
26 may be slideably disposed over the flexible shaft 22 and within
the handle 28. In an initial phase of deployment, the sheath 26 is
extended in direction 40 to cover the electrodes 124a,b,c,d to
protect the trocar and prevent accidental piercing when the
electrical ablation device 100 is advanced therethrough. Once the
electrodes 124a,b,c,d are located into or proximate the tissue
treatment region, the sheath 26 is retracted in direction 42 to
expose the electrodes 124a,b,c,d. One or more of the electrodes
124a,b,c,d of the electrical ablation device 100 may be adapted and
configured to slideably move in and out of a cannula, lumen, or
channel formed within the flexible shaft 22. In one embodiment all
of the electrodes 124a,b,c,d are configured to slideably move in
and out channels formed within lumens formed within the flexible
shaft 22, referred to for example as the lumen 44 in FIGS. 2A-D, to
advance and retract the electrodes 124a,b,c,d as may be desired by
the operator. Nevertheless, in other embodiments, it may be desired
to fix all or certain ones of the one or more electrodes 124a,b,c,d
in place.
[0064] The various embodiments of electrodes described in the
present specification, e.g., the electrodes 24a,b, or 124a-m, may
be configured for use with an electrical ablation device (not
shown) comprising an elongated flexible shaft to house the needle
electrodes 24a,b, or 124a-m, for example. The needle electrodes
24a,b, or 124a-m, are free to extend past a distal end of the
electrical ablation device. The flexible shaft comprises multiple
lumen formed therein to slideably receive the needle electrodes
24a,b, or 124a-m. A flexible sheath extends longitudinally from a
handle portion to the distal end. The handle portion comprises
multiple slide members received in respective slots defining
respective walls. The slide members are coupled to the respective
needle electrodes 24a,b, or 124a-m. The slide members are movable
to advance and retract the electrode 24a,b, or 124a-m. The needle
electrodes 24a,b, or 124a-m, may be independently movable by way of
the respective slide members. The needle electrodes 24a,b, or
124a-m, may be deployed independently or simultaneously. An
electrical ablation device (not shown) comprising an elongated
flexible shaft to house multiple needle electrodes and a suitable
handle is described with reference to FIGS. 4-10 in commonly owned
U.S. patent application Ser. No. 11/897,676 titled "ELECTRICAL
ABLATION SURGICAL INSTRUMENTS," filed Aug. 31, 2007, now U.S.
Patent Application Publication No. 2009/0062788, the entire
disclosure of which is incorporated herein by reference in its
entirety.
[0065] It will be appreciated that the electrical ablation devices
20, 100 described with referenced to FIGS. 2A-E, may be introduced
inside a patient endoscopically, transcutaneously, percutaneously,
through an open incision, through a trocar (as shown in FIG. 3),
through a natural orifice, or any combination thereof. In one
embodiment, the outside diameter of the electrical ablation devices
20, 100 may be sized to fit within a working channel of an
endoscope and in other embodiments the outside diameter of the
electrical ablation devices 20, 100 may be sized to fit within a
hollow outer sleeve, or trocar, for example.
[0066] FIG. 3 illustrates one embodiment of the electrical ablation
system 10 shown in FIGS. 1 and 2A-D in use to treat undesirable
tissue 48 located on the surface of the liver 50. The undesirable
tissue 48 may be representative of a variety of diseased tissues,
cancers, tumors, masses, lesions, abnormal tissue growths, for
example. In use, the electrical ablation device 20 may be
introduced into or proximate the tissue treatment region through a
port 52 of a trocar 54. The trocar 54 is introduced into the
patient via a small incision 59 formed in the skin 56. The
endoscope 12 may be introduced into the patient trans-anally
through the colon, trans-orally down the esophagus and through the
stomach using translumenal techniques, or through a small incision
or keyhole formed through the patient's abdominal wall (e.g., the
peritoneal wall). The endoscope 12 may be employed to guide and
locate the distal end of the electrical ablation device 20 into or
proximate the undesirable tissue 48. Prior to introducing the
flexible shaft 22 through the trocar 54, the sheath 26 is slid over
the flexible shaft 22 in a direction toward the distal end thereof
to cover the electrodes 24a,b (as shown in FIG. 2A) until the
distal end of the electrical ablation device 20 reaches the
undesirable tissue 48.
[0067] Once the electrical ablation device 20 has been suitably
introduced into or proximate the undesirable tissue 48, the sheath
26 is retracted to expose the electrodes 24a,b (as shown in FIG.
2B) to treat the undesirable tissue 48. To ablate the undesirable
tissue 48, the operator initially may locate the first electrode
24a at a first position 58a and the second electrode 24b at a
second position 60 using endoscopic visualization and maintaining
the undesirable tissue 48 within the field of view of the flexible
endoscope 12. The first position 58a may be near a perimeter edge
of the undesirable tissue 48. Once the electrodes 24a,b are located
into or proximate the undesirable tissue 48, the electrodes 24a,b
are energized with irreversible electroporation pulses to create a
first necrotic zone 65a. For example, once the first and second
electrodes 24a,b are located in the desired positions 60 and 58a,
the undesirable tissue 48 may be exposed to an electric field
generated by energizing the first and second electrodes 24a,b with
the energy source 14. The electric field may have a magnitude,
frequency, and pulse length suitable to induce irreversible
electroporation in the undesirable tissue 48 within the first
necrotic zone 65a. The size of the necrotic zone is substantially
dependent on the size and separation of the electrodes 24a,b, as
previously discussed. The treatment time is defined as the time
that the electrodes 24a,b are activated or energized to generate
the electric pulses suitable for inducing irreversible
electroporation in the undesirable tissue 48.
[0068] This procedure may be repeated to destroy relatively larger
portions of the undesirable tissue 48. The position 60 may be taken
as a pivot point about which the first electrode 24a may be rotated
in an arc of radius "r," the distance between the first and second
electrodes 24a,b. Prior to rotating about the second electrode 24b,
the first electrode 24a is retracted by pulling on the slide member
30 (FIGS. 1 and 2A-D) in a direction toward the proximal end and
rotating the electrical ablation device 20 about the pivot point
formed at position 60 by the second electrode 24b. Once the first
electrode 24a is rotated to a second position 58b, it is advanced
to engage the undesirable tissue 48 at point 58b by pushing on the
slide member 30 in a direction towards the distal end. A second
necrotic zone 65b is formed upon energizing the first and second
electrodes 24a,b. A third necrotic zone 65c is formed by retracting
the first electrode 24a, pivoting about pivot point 60 and rotating
the first electrode 24a to a new location, advancing the first
electrode 24a into the undesirable tissue 48 and energizing the
first and second electrodes 24a,b. This process may be repeated as
often as necessary to create any number of necrotic zones 65p,
where p is any positive integer, within multiple circular areas of
radius "r," for example, that is suitable to ablate the entire
undesirable tissue 48 region. At anytime, the surgeon or clinician
can reposition the first and second electrodes 24a,b and begin the
process anew. In other embodiments, the electrical ablation device
100 comprising multiple needle electrodes 124a-m described with
reference to FIG. 2E may be employed to treat the undesirable
tissue 48. Those skilled in the art will appreciate that similar
techniques may be employed to ablate any other undesirable tissues
that may be accessible trans-anally through the colon, and/or
orally through the esophagus and the stomach using translumenal
access techniques. Therefore, the embodiments are not limited in
this context.
[0069] In various embodiments, as outlined above, a surgical
instrument can comprise a first electrode and a second electrode,
wherein at least one the first and second electrodes can be
operably coupled to a power source. In certain embodiments, as also
outlined above, a first electrode can be operably coupled with a
positive terminal of a voltage source and the second electrode can
be operably coupled with a negative terminal of the voltage source,
for example. In at least one embodiment, the first and second
electrodes can comprise columnar, or point, electrodes which can be
inserted into the tissue of a patient. In various circumstances, a
voltage potential can be applied to the two electrodes such that a
magnetic field can be created therebetween in order to treat the
tissue positioned intermediate the electrodes. In some
circumstances, the voltage potential may be sufficient to permit
current to flow between the electrodes. Various devices are
disclosed in commonly-owned co-pending U.S. patent application Ser.
No. 12/352,375, entitled ELECTRICAL ABLATION DEVICES, which was
filed on Jan. 12, 2009, the entire disclosure of which is
incorporated by reference herein. While such devices may be
suitable for their intended purposes, other devices disclosed
herein can provide various advantages.
[0070] In various embodiments, referring now to FIGS. 4-6, a
surgical instrument, such as surgical instrument 200, for example,
can comprise a handle portion 228, a shaft portion 222, and one or
more electrodes, such as electrodes 224a and 224b, for example.
Referring to FIG. 4, handle portion 228 can comprise a first
portion 231 and a second portion 233, wherein the first portion 231
and the second portion 233 can be moved relative to one another.
Electrodes 224a and 224b can be mounted, or rigidly secured, to the
first portion 231 wherein, in at least one embodiment, proximal
ends of electrodes 224a and 224b can be mounted to first portion
231 such that the proximal ends of the electrodes do not move
relative to first portion 231. In at least one embodiment, a sheath
226 of shaft portion 222 can be mounted, or rigidly secured, to
second portion 233 such that, when second portion 233 is moved
relative to first portion 231, sheath 226 can be moved relative to
first electrode 224a and/or second electrode 224b. In various
embodiments, second portion 233 can be moved between a first, or
distal, position (FIG. 5) in which the distal end 223 of sheath 226
surrounds the distal ends 235a, 235b of electrodes 224a, 224b and a
second, or proximal, position (FIG. 6) in which the distal end 223
of sheath 226 is retracted relative to the distal ends 235a, 235b
of electrodes 224a, 224b.
[0071] In various embodiments, further to the above, sheath 226 can
be moved between a distal position in which the distal ends 235a,
235b of electrodes 224a, 224b are positioned within the sheath 226
and a proximal position in which the distal ends 235a, 235b can
extend distally from the distal end 223 of sheath 226. In at least
one embodiment, the distal ends 235a, 235b of electrodes 224a, 224b
can be recessed with respect to the distal end 223 of sheath 226
when sheath 226 is in its distal position. In use, the distal end
223 of sheath 226 can be positioned against tissue within a
surgical site, for example, such that the electrodes 224a, 224b do
not contact the tissue. Such embodiments may also allow the
surgical instrument 200, or at least the distal end thereof, to be
inserted through a trocar without the electrodes 224a, 224b coming
into contact with, snagging on, and/or becoming damaged by the
trocar. Once the distal end of the surgical instrument 200 has been
suitably positioned relative to the targeted tissue, the sheath 226
can be retracted in order to expose the distal ends 235a, 235b of
the electrodes 224a, 224b such that the electrodes can be inserted
into the tissue. In various alternative embodiments, the distal
ends 235a, 235b of electrodes 224a, 224b can be positioned in the
same plane as the distal end of sheath 226 when the sheath 226 is
in its distal-most position.
[0072] In various embodiments, as outlined above, the second
portion 233 of handle 228 can be moved relative to the first
portion 231 of handle 228 in order to move the sheath 226 relative
to the electrodes 224a, 224b. In various circumstances, referring
again to FIG. 4, the first portion 231 can be held in a stationary,
or at least substantially stationary, position while the second
portion 233 can be slid relative to first portion 231 by a surgeon,
or other clinician, for example. In at least one embodiment, the
first portion 231 can comprise a cylindrical, or at least
substantially cylindrical, portion 235 and the second portion 233
can comprise a cylindrical, or at least substantially cylindrical,
aperture 237 configured to receive the cylindrical portion 235 of
first portion 231. The aperture 237 can be configured to closely
receive cylindrical portion 235 such that relative movement
therebetween can be limited to relative movement along a
predetermined path, such as axis 239, for example. In certain
embodiments, first portion 231 and second portion 233 can comprise
one or more cooperating keys and/or grooves which can be configured
to permit relative sliding movement therebetween along axis 239
while preventing, or at least inhibiting, relative movement
therebetween which is transverse to axis 239.
[0073] In various embodiments, referring now to FIG. 7, a surgical
instrument, such as surgical instrument 300, for example, can
comprise a sheath 326 and one or more electrodes, such as
electrodes 324a and 324b, for example. In use, similar to the
above, the electrodes 324a and 324b can be inserted into tissue and
a voltage differential can be applied to the electrodes such that
current can flow from one electrode to the other and, in addition,
flow through the tissue positioned intermediate and/or surrounding
the electrodes 324a and 324b. In various embodiments, at least one
electrode can comprise an insulative jacket surrounding at least a
portion of the electrode such that current does not arc, or jump,
between the electrodes of the surgical instrument without flowing
through the tissue. In certain embodiments, such as those having
two electrodes, for example, an insulative jacket may surround only
one of the electrodes, wherein such an insulative jacket can be
sufficient to prevent current from arcing between the electrodes.
In at least one embodiment, an insulative jacket 341a can surround
at least a portion of electrode 324a and, similarly, an insulative
jacket 341b can surround at least a portion of electrode 324b. The
insulative jackets can be comprised of any suitable material which
can increase the dielectric resistance between the electrodes 324a
and 324b, such as ceramic, for example. In various embodiments, as
a result of the above, an insulative jacket at least partially
surrounding an electrode can interrupt the air gap between the
electrodes in order to reduce the possibility of current arcing
between the electrodes.
[0074] In various embodiments, further to the above, insulative
jacket 341a can comprise a tube having an aperture, wherein
electrode 324a can extend through the aperture. In at least one
embodiment, insulative jacket 341a can be mounted, or rigidly
secured, to a handle portion of surgical instrument 300 and can
extend along a substantial length of electrode 324a. The insulative
jacket 341a can be configured such that the distal end 335a of
electrode 324a is not surrounded by insulative jacket 341a and such
that the distal end 335a of electrode 324a extends distally from
the distal end 343a of insulative jacket 341a. Similar to the
above, insulative jacket 341b can comprise a tube having an
aperture, wherein electrode 324b can extend through the aperture.
In at least one embodiment, insulative jacket 341b can be mounted,
or rigidly secured, to a handle portion of surgical instrument 300
and can extend along the length of electrode 324b. The insulative
jacket 341b can be configured such that the distal end 335b of
electrode 324b is not surrounded by insulative jacket 341b and such
that the distal end 335b of electrode 324b extends distally from
the distal end 343b of insulative jacket 341b. In at least one such
embodiment, the air gap between the electrodes 324a and 324b can be
interrupted by the insulative jackets 341a, 341b except for the
distance extending between the distal ends of the electrodes 324a,
324b and the distal ends of insulative jackets 341a, 341b.
[0075] Referring to FIG. 8, the distal ends 343a, 343b of
electrodes 324a, 324b can be inserted into tissue such that, if the
electrodes 324a and 324b are inserted a certain depth, insulative
jacket 341a and/or insulative jacket 341b can contact the tissue.
Once the insulative jacket 341a and/or insulative jacket 341b
contacts the tissue, the insulative jackets can prevent, or at
least inhibit, electrode 324a and/or electrode 324b from being
further inserted into the tissue. In at least one embodiment, the
distal end 343a and/or distal end 343b can comprise a datum which
can define the maximum insertion depth of the electrode 324a and/or
electrode 324b into the tissue. When the insulative jackets 341a
and 341b are in contact with, or at least nearly in contact with,
the tissue, very little, if any, uninterrupted air gap may exist
between the electrodes 324a and 324b. In various circumstances, as
a result, the possibility of current acting between the electrodes
without passing through the tissue can be reduced. In various
embodiments, the distal end 343a of insulative jacket 341a and the
distal end 343b of insulative jacket 341b can lie along a common
plane, or datum. In various other embodiments, although not
illustrated, the distal ends 343a and 343b of insulative jackets
341a and 341b can define different datums and/or can provide for
different insertion depths into the tissue, for example.
[0076] In various embodiments, referring now to FIG. 9, a surgical
instrument, such as surgical instrument 400, for example, can
comprise a sheath 426 and one or more electrodes, such as
electrodes 424a and 424b, for example. In use, similar to the
above, the electrodes 424a and 424b can be inserted into tissue and
a voltage differential can be applied to the electrodes such that
current can flow from one electrode to the other and, in addition,
flow through the tissue positioned intermediate and/or surrounding
the electrodes. The surgical instrument 400 can further comprise an
insulative guard, such as guard 441, for example, which can be
movable between a distal, or extended, position in which it is
positioned intermediate the distal ends of the first electrode 424a
and the second electrode 424b and a proximal, or retracted,
position in which the guard 441 is displaced proximally relative to
the distal ends of the first and second electrodes 424a and 424b.
In various embodiments, the guard 441 can be biased into a distal
position (FIG. 9) in which guard 441 is positioned intermediate the
distal end 443a of first electrode 424a and the distal end 443b of
second electrode 424b. In certain embodiments, the guard 441 can be
biased into its distal position by a spring, such as compression
spring 445, for example. More particularly, in at least one
embodiment, spring 445 can be positioned intermediate a portion of
sheath 426, such as support surface 447, for example, and a portion
of insulative guard 441, such as surface 449 and/or projections
extending therefrom, such that the compression spring 445 can apply
a biasing force to guard 441 and hold guard 441 in its distal
position. In such a distal position, the guard 441 can prevent, or
at least reduce the possibility of, current from arcing between the
electrodes.
[0077] As outlined above, the insulative guard 441 of surgical
instrument 400 can be biased into its distal position by
compression spring 445. In at least one embodiment, referring to
FIG. 9, guard 441 can comprise a distal end 451 which can be
positioned flush with the distal ends 443a and 443b of electrodes
424a and 424b. In at least one embodiment, the distal end 451 can
be positioned along a datum defined by distal ends 443a and 443b.
In certain other embodiments, although not illustrated, the distal
end 451 of guard 441 can extend beyond the distal end 443a and/or
the distal end 443b of the electrodes. As also outlined above, the
guard 441 can be retracted proximally. In at least one embodiment,
referring now to FIG. 10, the insulative guard 441 can be slid
proximally within sheath 426 such that the insulative guard 441 is
no longer positioned intermediate the distal ends 443a and 443b of
the electrodes. In certain embodiments, referring now to FIG. 11,
the surgical instrument 400 can be configured such that insulative
guard 441 can be retracted as electrodes 424a and 424b are inserted
into the tissue. More particularly, in at least one embodiment, the
distal ends 443a and 443b of the electrodes and the distal end 451
of guard 441 can be positioned against tissue wherein, as the
electrodes 424a and 424b enter into the tissue, the guard 441 may
not enter into the tissue and, instead, may be displaced
proximally, or relative to the distal ends 443a and 443b. Once the
guard has been displaced proximally, in various embodiments, a
voltage differential may be applied to the electrodes 424a and 424b
and current may flow from one electrode to the other through the
tissue.
[0078] When insulative guard 441 is displaced proximally, as
outlined above, the guard 441 can compress spring 445. When spring
445 is compressed, the spring 445 can store energy therein and
apply a biasing force to insulative guard 441 such that, as the
electrodes 424a and 424b are extracted from the tissue, the spring
445 can displace the guard 441 distally toward the distal ends 443a
and 443b of electrodes 424a and 424b. In at least one such
embodiment, the distal end 451 of guard 441 can remain in contact
with the tissue as the electrodes 424a and 424b are inserted into
and extracted from the tissue. In various embodiments, as a result,
the guard 441 can prevent, or at least reduce the possibility of,
current arcing between the electrodes without passing through the
tissue. Stated another way, the guard 441 can be sufficiently
retracted when the electrodes 424a, 424b are inserted into tissue
in order to permit current to flow between the portions of
electrodes 424a, 424b within the tissue but, at the same time,
sufficiently positioned against the tissue to prevent, or at least
reduce the possibility of, current from flowing between the
electrodes 424a, 424b at a location outside of the tissue. In
various embodiments, as a result of the above, the insulative guard
441 and spring 445 arrangement can provide for a self-regulating,
or self-retracting, system. In other embodiments, although not
illustrated, the surgical instrument 400 can comprise an actuator
configured to displace the insulative guard 441. In certain
embodiments, other biasing means can be used in addition to or in
lieu of a spring. In at least one embodiment, for example, a
surgical instrument can comprise a motor mounted within a shaft of
the surgical instrument, wherein the motor can apply a biasing
force to an insulative guard in order to keep the guard biased
against the tissue and yet the permit the guard to move relative to
the electrodes.
[0079] In various embodiments, further to the above, surgical
instrument 400 can further comprise means for controlling or
defining the movement of insulative guard 441 as it is moved
between its proximal and distal positions. In at least one
embodiment, referring to FIGS. 9 and 10, the sheath 426 can
comprise at least one elongate slot 453 and the guard 441 can
comprise at least one projection 455 extending therefrom, wherein
the projection 455 can be configured to slide within the slot 453.
The slot 453 can be configured to limit the movement of projection
455 such that the guard 441 can move along a predetermined path
relative to sheath 426, for example. In at least one embodiment,
the slot 453 and projection 455 can be configured such that guard
441 is guided along an axial, or longitudinal, path between its
proximal and distal positions. In at least one such embodiment, the
slot 453 can comprise a linear, or at least substantially linear,
profile and can be parallel to, substantially parallel to,
collinear with, or substantially collinear with a longitudinal axis
of sheath 426. Although not illustrated, other embodiments are
envisioned in which slot 453 can comprise a curved configuration, a
curvilinear configuration, and/or any other suitable configuration
in order to provide or define a suitable path for guard 441. In
various embodiments, although not illustrated, the sheath 426 can
comprise at least one projection extending therefrom which can be
configured to slide within at least groove in the insulative guard.
In various embodiments, referring again to FIGS. 9 and 10, the
insulative guard 441 can comprise one or more recesses or grooves,
such as recesses 457a and 457b, for example, which can be
configured to receive at least a portion of the electrodes 424a and
424b, respectively. More particularly, in at least one embodiment,
the electrode 424a can extend through recess 457a in guard 441 and,
in addition, the electrode 424b can extend through the recess 457b,
wherein, in at least one embodiment, the electrodes 424a, 424b can
be closely received in the recesses 457a, 457b such that guard 441
is guided therebetween.
[0080] In various embodiments, a surgical instrument can include an
electrode comprising a flexible portion which can be configured to
conform to the surface of an organ, such as a patient's liver, for
example, and/or any other suitable tissue to be treated. In certain
embodiments, referring now to FIG. 12, a surgical instrument, such
as surgical instrument 500, for example, can comprise a shaft 526
and an electrode 524, wherein the electrode 524 can be comprised of
a flexible, conductive mesh 525. In at least one embodiment, the
surgical instrument 500 can further comprise an electrode support
561 which can be mounted to the shaft 526. The electrode support
561 can comprise a wire, or rod, having a first end and a second
end mounted to the shaft 526 and an intermediate portion 565
extending between the first end and the second end. The first end
and the second end of electrode support 561 can be mounted to shaft
526 in any suitable manner, such as by welding and/or fasteners,
for example. In various embodiments, the intermediate portion 565
can define a perimeter configured to support the edge of the
flexible mesh 525. The edge of the flexible mesh 525 can be mounted
to the electrode support 561 by any suitable means such as an
adhesive and/or fasteners, for example. In certain embodiments, the
edge of the flexible mesh 525 can be wrapped around the electrode
support 561 such that the edge of the flexible mesh 525 can be
attached to itself. In any event, the electrode mesh 525 can be
configured such that a central portion of the electrode mesh 525
can move relative to its edge. In at least one embodiment, the
central portion of the electrode mesh 525 can be configured to
deflect relative to the electrode support 561 in order to create a
pocket, or pouch. The electrode mesh 525 can comprise a concave or
convex configuration which can receive at least a portion of the
targeted tissue therein. In various embodiments, the surgical
instrument 500 can comprise a liver retractor wherein the flexible
mesh 525 can deflect to receive at least a portion of a patient's
liver. In at least one such embodiment, the electrode 524 may be
sufficiently rigid to allow a surgeon to manipulate the patient's
liver with the surgical instrument 500 and hold the electrode 524
in position.
[0081] In various embodiments, further to the above, the flexible
mesh 525 can be comprised of a conductive material, such as copper
and/or stainless steel, for example, wherein the flexible mesh can
be operably connected with at least one conductor, such as
conductor 518, for example, of the surgical instrument 500. In use,
the flexible mesh 525 can be positioned relative to the tissue to
be treated wherein, in at least one embodiment, a second electrode,
such as electrode 524b, for example, can also be positioned
relative to the tissue. Referring now to FIG. 13, the flexible
electrode of surgical instrument 500 can be positioned on one side
of the tissue to be treated and the second electrode can be
inserted into the tissue and/or a tumor within the tissue, for
example. In at least one such embodiment, the conductor 518 of
surgical instrument 500 and the second electrode 524b can be
operably coupled with a power source such that current can flow
between the electrodes. In various embodiments, the second
electrode 524b can be operably connected with a cathode, or
positive pole, of the power source while the conductor 518 can be
operably connected to an anode, or negative pole, of the power
source and/or a suitable ground. In various other embodiments, the
second electrode 524b can be operably connected to the anode of the
power source and/or ground while the conductor 518 can be operably
connected to the cathode of the power source. In any event,
referring to FIGS. 14 and 15, the voltage potential applied to the
electrode 524 and the second electrode 524b, and/or the current
passing between the electrodes 524, 524b, can cause necrosis in the
tissue which is in contact with and/or surrounding the electrodes
524, 524b. Such necrotic tissue can comprise necrotic tissue
portion 563a and necrotic tissue portion 563b wherein, referring to
FIG. 14, the necrotic tissue portion 563b can be associated with
the second electrode 524b and can comprise a volume of
substantially ablated and/or necrotic tissue while the necrotic
tissue portion 563a can be associated with electrode 524 and can
comprise a volume of only partially ablated and/or necrotic tissue,
for example.
[0082] In various circumstances, further to the above, it may be
desirable to control or limit the size of necrotic tissue region
563a and/or the density of the necrotic tissue within region 563a.
In certain embodiments, the amount and/or density of the necrotic
tissue created around the electrode 524 can depend on the
intensity, or density, of the current flowing from and/or to the
electrode 524. In various circumstances, the field density of the
current can depend on the size of the electrode 524. More
particularly, a larger electrode 524 can produce a lower current
field density surrounding the electrode 524 and, as a result,
generate a smaller amount of necrotic tissue, whereas a smaller
electrode 524 can produce a larger current field density and, as a
result, generate a larger amount of necrotic tissue. In various
embodiments, referring again to FIG. 14, the necrotic tissue region
563a can be largely positioned under and/or around the electrode
support 561. In view of the above, the perimeter or diameter of
electrode support 561 can be increased such that a smaller amount
of, and/or less dense volume of, necrotic tissue is created around
electrode 524, whereas the perimeter or diameter of electrode
support 561 can be decreased such that a larger amount of, and/or
more dense volume of, necrotic tissue is created around electrode
524. Correspondingly, a larger perimeter or diameter of electrode
support 561 can generally accommodate a larger electrode mesh 525,
wherein the larger electrode mesh 525 can, as a result, contact a
larger surface area of tissue. Such a larger surface area can
further reduce the amount and/or density of necrotic tissue
produced by electrode 524. By comparison, the amount and/or density
of necrotic tissue surrounding second electrode 524b, which may
comprise a needle electrode, for example, can be larger, and
possibly substantially larger, than the amount and/or density of
necrotic tissue surrounding electrode 524.
[0083] As outlined above, referring again to FIG. 12, the electrode
mesh 525 can comprise a conductive material. In at least one
embodiment, the electrode mesh 525 can be attached to shaft 526 by
a mounting collar 541, wherein the mounting collar 541 can secure
an end of mesh 525 in position. In at least one embodiment, the
electrode mesh 525 can comprise a bag having an open end which can
be slid over electrode support 561 and at least a portion of shaft
526 wherein the mounting collar 541 can be slid over at least a
portion of mesh 525 to mount mesh 525 to shaft 526. In certain
embodiments, the electrode mesh can comprise at least one substrate
material perfused with at least one electrically-conductive
material, such as saline, for example, wherein the perfused
material and the substrate material can permit current to flow
throughout the mesh 525 and/or between conductor 518 and electrode
support 561, for example. In various embodiments, the substrate
material and the perfused material can both be comprised of one or
more electrically-conductive materials. In at least one embodiment,
the mesh 525 can be comprised of a non-conductive, or at least
substantially non-conductive, substrate material, wherein a
conductive material perfused within the substrate material can
conduct the current within the mesh 525. In at least one
embodiment, the substrate material of mesh 525 can be porous such
that the substrate material can absorb the conductive material. In
various embodiments, the electrode mesh 525 can comprise at least
one substrate material and, in addition, at least one conductive
material coated onto the substrate material. In at least one
embodiment, the substrate material can be comprised of at least one
non-electrically conductive material while, in other embodiments,
the substrate material can be comprised of one or more electrically
conductive materials. In certain embodiments, the coated material
can be comprised of a multi-filament medical polyester yarn
available from ATEX Technologies, for example. As discussed above,
mesh 525 can be flexible such that it can readily deflect or change
shape when it contacts tissue, such as a patient's liver, for
example. In certain embodiments, the mesh 525 can comprise a
material having a plurality of apertures extending therethrough,
wherein the apertures can be arranged in any suitable pattern. In
at least one embodiment, mesh 525 can comprise a weaved material.
In certain embodiments, the mesh 525 can be rigid, or at least
substantially rigid, such that it does not substantially deflect
when it contacts tissue.
[0084] In various embodiments, referring now to FIG. 16, a surgical
instrument, such as surgical instrument 600, for example, can
comprise a flexible electrode, such as balloon electrode 624, for
example, wherein the electrode 624 can be configured to conform to
the contour of the tissue being treated. In certain embodiments,
the balloon electrode 624 can be delivered to a surgical site
percutaneously and/or laprascopically, wherein the balloon
electrode 624 can be positioned under and/or around the targeted
tissue, such as a patient's liver, for example. In at least one
embodiment, the balloon electrode 624 can be expanded in order to
increase the surface area of the electrode in contact with the
targeted tissue. Similar to the above, a larger surface area in
contact with the tissue can reduce the amount of, and/or the
density of, the necrotic tissue created. In various embodiments,
also similar to the above, a second electrode can be inserted into
the targeted tissue, wherein the second electrode can be operably
coupled with the cathode, or positive terminal, of a power source
and the balloon electrode 624 can comprise a return electrode which
can be operably coupled with the anode, or negative terminal, of
the power source and/or any suitable ground, for example. In other
embodiments, the electrode 624 can be operably coupled with the
cathode, or positive terminal, of the power source and the second
electrode can be operably coupled with the anode, or negative
terminal, of the power source and/or any other suitable ground. In
various alternative embodiments, a surgical instrument can include
an electrode comprising a flexible sheet which is positioned
against or relative to the targeted tissue.
[0085] In various embodiments, referring now to FIGS. 17 and 18, a
surgical instrument, such as surgical instrument 700, for example,
can comprise a plurality of electrodes, such as electrodes 724a,
724b, 724c, and 724d, for example, which can be configured and
arranged to treat tissue in a desired manner. Similar to the above,
the electrodes 724a-724d can extend distally from shaft 722 and
protective sleeve 726 such that the electrodes can be inserted into
tissue. In certain embodiments, also similar to the above, the
electrodes 724a and 724b can be operably coupled with a cathode, or
positive terminal, of a power source, whereas the electrodes 724c
and 724d can be operably coupled with an anode, or negative
terminal, of a power source. Referring primarily to FIG. 18, the
electrodes 724a-724d can be positioned and arranged with respect to
a central axis, such as axis 799, for example, wherein, in certain
embodiments, axis 799 can be defined by the center of shaft 722. In
various embodiments, the electrodes 724a-724d can each comprise a
columnar electrode having a central axis, wherein the central axes
of the electrodes 724a-724d can be positioned relative to axis 799.
For example, the central axis of electrode 724a can be positioned a
distance D1 away from axis 799, the central axis of electrode 724b
can be positioned a distance D2 away from axis 799, the central
axis of electrode 724c can be positioned a distance D3 away from
axis 799, and the central axis of electrode 724d can be positioned
a distance D4 away from axis 799. In certain embodiments, distance
D1 can be equal to, or at least substantially equal to, distance D2
while, in various embodiments, distance D3 can be equal to, or at
least substantially equal to, distance D4. Referring again to FIG.
18, distances D1 and D2 can be larger than distances D3 and D4 such
that electrodes 724a and 724b care positioned further away from
axis 799 than electrodes 724c and 724d. In various embodiments,
distances D1, D2, D3, and/or D4 can range between approximately
0.25 cm and approximately 1.0 cm, for example.
[0086] When electrodes 724a-724d are polarized by a power source,
referring again to FIG. 18, a voltage field can be created which
surrounds the electrodes. In various embodiments, the voltage field
can comprise one or more isolines, wherein each isoline can
represent portions of the voltage field which have the same
magnitude. For example, the voltage field generated by electrodes
724a-724d can be represented by a plurality of isolines, such as
isoline 798a, for example, wherein isoline 798a can represent a
perimeter surrounding the electrodes having a constant voltage
field magnitude. Similarly, the electrodes 724a-724d can produce an
isoline 798b which can represent a perimeter surrounding the
electrodes having a constant voltage field magnitude which is
different than the magnitude of isoline 798a, for example. In
various embodiments, the isoline 798b can represent a voltage field
magnitude which is greater than the magnitude represented by
isoline 798a. In various embodiments, referring now to FIG. 19, the
magnitude of the voltage field produced by the electrodes may not
be constant at all locations surrounding the electrodes; on the
contrary, the magnitude of the voltage field may be different at
various locations surrounding the electrodes. For example, the
voltage field, or at least a portion of the voltage field produced
by the surgical instrument 700 can be represented by graph 797a in
FIG. 19. More particularly, the graph 797a can represent the
magnitude of the voltage field measured in a plane which includes
the center axis of electrode 724c, center axis 799, and electrode
724d. Graph 797a, however, may not necessarily represent the
magnitude of the voltage field in other planes. Upon examining the
graph 797a, it can be seen that, in at least one embodiment, the
voltage field produced by the electrodes 724a-724d can comprise a
symmetrical, or at least substantially symmetrical, profile
centered about axis 799. Furthermore, it can be seen from graph
797a that the magnitude of the voltage field has two valleys 795c,
795d centered about, or at least positioned adjacent to, the
electrodes 724c and 724d, respectively. In various embodiments, the
magnitude of the voltage field at valleys 795c and/or 795d may be
zero or, alternatively, greater than zero.
[0087] In various embodiments, referring again to the graph 797a in
FIG. 19, the magnitude of the voltage field surrounding electrodes
724a-724d can be the same, or at least substantially the same, at
distances of between about 6 cm to about 10 cm away from axis 799
in the lateral directions, for example. Stated another way, the
change in magnitude, or gradient, of the voltage field produced by
surgical instrument 700 between about 6 cm and about 10 cm away
from the center of surgical instrument 700 may be very small. In at
least one embodiment, for example, the gradient, or rate of change
of the magnitude of the voltage field, between about 9 cm and about
10 cm may be about 0.04 VDC per millimeter, for example. In other
various embodiments, the gradient may be about 0.01 VDC/mm, about
0.02 VDC/mm, about 0.03 VDC/mm, about 0.05 VDC/mm, about 0.06
VDC/mm, about 0.07 VDC/mm, about 0.08 VDC/mm, about 0.09 VDC/mm,
about 0.10 VDC/mm, about 0.11 VDC/mm, about 0.12 VDC/mm, and/or
about 0.13 VDC/mm, for example. In various circumstances, it may be
desirable for surgical instrument 700 to produce a voltage field
having a gradient below about 0.14V/mm, wherein a voltage field
gradient at or larger than 0.14 V/mm may cause a contraction of
muscle, and/or other tissue, surrounding the surgical site.
Referring now to the graph 797b in FIG. 19, the graph 797b can
represent the magnitude of the voltage field measured in a plane
which includes the center axis of electrode 724a, center axis 799,
and electrode 724b, although the graph 797b may not necessarily
represent the magnitude of the voltage field in other planes. In
various circumstances, the planes used to establish graphs 797a and
797b may be orthogonal, or perpendicular, to one another. Upon
examining the graph 797b, it can be seen that, in at least one
embodiment, the voltage field produced by the electrodes 724a-724d
can comprise a symmetrical, or at least substantially symmetrical,
profile centered about axis 799. Furthermore, it can be seen from
graph 797b that the magnitude of the voltage field has two peaks
795a, 795b centered about, or at least positioned adjacent to, the
electrodes 724a and 724b, respectively. Similar to the above, it
can be seen from graph 797b that the gradient of the magnitude of
the voltage field between about 9 cm and about 10 cm away from axis
799 may be about 0.04 VDC per millimeter, for example. In other
various embodiments, the gradient may be about 0.01 VDC/mm, about
0.02 VDC/mm, about 0.03 VDC/mm, about 0.05 VDC/mm, about 0.06
VDC/mm, about 0.07 VDC/mm, about 0.08 VDC/mm, about 0.09 VDC/mm,
about 0.10 VDC/mm, about 0.11 VDC/mm, about 0.12 VDC/mm, and/or
about 0.13 VDC/mm, for example.
[0088] Viewing graphs 797a and 797b together, further to the above,
the voltage field produced by surgical instrument 700 between about
6 cm and about 10 cm away from axis 799 in all directions could be
represented by a single isoline, or isoplane, which surrounds the
electrodes 724a-724d. When electrodes 724a-724d are positioned in
tissue, such an isoplane can represent very little, if any, voltage
gradient through the tissue which, as a result, can result in
little, if any contraction of the tissue within the 6 cm to 10 cm
region, for example. As outlined above, referring against to graphs
797a and 797b in FIG. 19, the magnitude of the voltage field
produced by the surgical instrument 700 is a function of the
voltage potential, or differential, supplied to the electrodes
724a-724d. A lower voltage potential, or differential, supplied to
the electrodes can result in a voltage field having a lower average
magnitude as compared to when a higher voltage potential, or
differential, is supplied to the electrodes 724a-724d. In various
embodiments, further to the above, the same voltage potential, or
at least substantially the same voltage potential, supplied to
electrode 724a can be supplied to electrode 724b. In certain
embodiments, the same voltage potential, or at least substantially
the same voltage potential, supplied to electrode 724c can be
supplied to electrode 724d.
[0089] In various embodiments, referring now to FIGS. 20 and 21, a
surgical instrument, such as surgical instrument 900, for example,
can comprise a first array of electrodes, such as electrodes 924a,
924b, and 924c, for example, which can be operably coupled with a
first conductor. In addition, the surgical instrument 900 can
further comprise a second array of electrodes, such as electrodes
924d, 924e, and 924f, for example, which can be operably coupled
with a second conductor. Further to the above, the first conductor
can be operably coupled with a cathode, or positive terminal, of a
power source, whereas the second conductor can be operably coupled
with an anode, or negative terminal, of the power source, for
example. In various embodiments, referring primarily to FIG. 21,
the electrodes 924a-924f can be arranged along first and second
lines. More particularly, in at least one embodiment, electrodes
924a, 924e, and 924c can be positioned along a first line while
electrodes 924d, 924b, and 924f can be positioned along a second
line. In certain embodiments, the first line can be parallel to, or
at least substantially parallel to, the second line. With regard to
the first line of electrodes, in various embodiments, positive
electrode 924a can be positioned on one side of negative electrode
924e while positive electrode 924c can be positioned on the
opposite side of electrode 924e. Similarly, with regard to the
second line of electrodes, negative electrode 924d can be
positioned on one side of positive electrode 924b while negative
electrode 924f can be positioned on the opposite side of electrode
924b. In certain embodiments, electrodes 924a, 924b, and 924c can
have the same, or at least substantially the same, voltage
potential while, in at least one embodiment, electrodes 924d, 924e,
and 924f can have the same, or at least substantially the same,
voltage potential.
[0090] In various embodiments, further to the above, the first
array of electrodes comprising electrodes 924a, 924b, and 924c can
be set to a first polarity while the second array of electrodes
comprising electrodes 924d, 924e, and 924f can be set to a second
polarity. In certain embodiments, the polarity of the first array
of electrodes can be adjusted simultaneously while the polarity of
the second array of electrodes can be adjusted simultaneously, and
independently, of the first array of electrodes. In various
embodiments, the electrode 924a can be operably coupled to a first
conductor, the electrode 924b can be operably coupled to a second
conductor, the electrode 924c can be operably coupled to a third
conductor, the electrode 924d can be operably coupled with a fourth
conductor, the electrode 924e can be operably coupled with a fifth
conductor, and the electrode 924f can be operably coupled with a
sixth conductor. In at least one such embodiment, each of the
conductors can be operably coupled with an output of a voltage
source, wherein the voltage source can be configured to supply
different voltage potentials to one, some, and/or all of the
conductors and their corresponding electrodes. In the exemplary
embodiment of surgical instrument 900, such a voltage source could
supply six different voltage potentials, wherein, in at least one
embodiment, each of the voltage potentials could be adjusted
before, and/or during, the operation of the surgical
instrument.
[0091] In certain embodiments, referring again to FIG. 21, the
electrodes 924a, 924e, and 924c can be attached to and/or bonded to
one another with an insulator positioned intermediate the
electrodes 924a, 924e, and 924c. Similarly, electrodes 924d, 924b,
and 924f can be attached to and/or bonded to one another within an
insulator positioned intermediate the electrodes 924d, 924b, and
924f. In various embodiments, air gaps can be present between the
electrodes 924a-924f. In any event, although surgical instrument
900 is described and illustrated as comprising six electrodes,
other embodiments are envisioned which can comprise less than six
electrodes or more than six electrodes, such as embodiments
comprising eight electrodes arranged in two rows of four
electrodes, or embodiments comprising ten electrodes arranged in
two rows of five electrodes, for example. Furthermore, although
surgical instrument 900 is described and illustrated as comprising
two rows of electrodes, other embodiments are envisioned which can
comprise more than two rows of electrodes, such as embodiments
comprising nine electrodes arranged in three rows of three
electrodes, for example.
[0092] The embodiments of the devices described herein may be
introduced inside a patient using minimally invasive or open
surgical techniques. In some instances it may be advantageous to
introduce the devices inside the patient using a combination of
minimally invasive and open surgical techniques. Minimally invasive
techniques may provide more accurate and effective access to the
treatment region for diagnostic and treatment procedures. To reach
internal treatment regions within the patient, the devices
described herein may be inserted through natural openings of the
body such as the mouth, anus, and/or vagina, for example. Minimally
invasive procedures performed by the introduction of various
medical devices into the patient through a natural opening of the
patient are known in the art as NOTES.TM. procedures. Some portions
of the devices may be introduced to the tissue treatment region
percutaneously or through small-keyhole-incisions.
[0093] Endoscopic minimally invasive surgical and diagnostic
medical procedures are used to evaluate and treat internal organs
by inserting a small tube into the body. The endoscope may have a
rigid or a flexible tube. A flexible endoscope may be introduced
either through a natural body opening (e.g., mouth, anus, and/or
vagina) or via a trocar through a relatively small-keyhole-incision
incisions (usually 0.5-1.5 cm). The endoscope can be used to
observe surface conditions of internal organs, including abnormal
or diseased tissue such as lesions and other surface conditions and
capture images for visual inspection and photography. The endoscope
may be adapted and configured with working channels for introducing
medical instruments to the treatment region for taking biopsies,
retrieving foreign objects, and/or performing surgical
procedures.
[0094] Preferably, the various embodiments of the devices described
herein will be processed before surgery. First, a new or used
instrument is obtained and if necessary cleaned. The instrument can
then be sterilized. In one sterilization technique, the instrument
is placed in a closed and sealed container, such as a plastic or
TYVEK.RTM. bag. The container and instrument are then placed in a
field of radiation that can penetrate the container, such as gamma
radiation, x-rays, or high-energy electrons. The radiation kills
bacteria on the instrument and in the container. The sterilized
instrument can then be stored in the sterile container. The sealed
container keeps the instrument sterile until it is opened in the
medical facility. Other sterilization techniques can be done by any
number of ways known to those skilled in the art including beta or
gamma radiation, ethylene oxide, and/or steam.
[0095] Although the various embodiments of the devices have been
described herein in connection with certain disclosed embodiments,
many modifications and variations to those embodiments may be
implemented. For example, different types of end effectors may be
employed. Also, where materials are disclosed for certain
components, other materials may be used. The foregoing description
and following claims are intended to cover all such modification
and variations.
[0096] Any patent, publication, or other disclosure material, in
whole or in part, that is said to be incorporated by reference
herein is incorporated herein only to the extent that the
incorporated materials does not conflict with existing definitions,
statements, or other disclosure material set forth in this
disclosure. As such, and to the extent necessary, the disclosure as
explicitly set forth herein supersedes any conflicting material
incorporated herein by reference. Any material, or portion thereof,
that is said to be incorporated by reference herein, but which
conflicts with existing definitions, statements, or other
disclosure material set forth herein will only be incorporated to
the extent that no conflict arises between that incorporated
material and the existing disclosure material.
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