U.S. patent application number 15/451765 was filed with the patent office on 2017-06-22 for system and method for detecting bending of an electrosurgical device.
The applicant listed for this patent is COVIDIEN LP. Invention is credited to JOSEPH D. BRANNAN, RICHARD A. WILLYARD.
Application Number | 20170172689 15/451765 |
Document ID | / |
Family ID | 48047869 |
Filed Date | 2017-06-22 |
United States Patent
Application |
20170172689 |
Kind Code |
A1 |
BRANNAN; JOSEPH D. ; et
al. |
June 22, 2017 |
SYSTEM AND METHOD FOR DETECTING BENDING OF AN ELECTROSURGICAL
DEVICE
Abstract
A system for detecting bending of an electrosurgical device
includes a strain relief configured to be coupled to a shaft of an
electrosurgical device, a piezoelectric actuator disposed within
the strain relief and configured to bend upon bending of the
electrosurgical device, and a bending detection circuit in
electrical communication with the piezoelectric actuator and
configured to detect a bending of the piezoelectric actuator.
Inventors: |
BRANNAN; JOSEPH D.; (LYONS,
CO) ; WILLYARD; RICHARD A.; (LOVELAND, CO) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
COVIDIEN LP |
MANSFIELD |
MA |
US |
|
|
Family ID: |
48047869 |
Appl. No.: |
15/451765 |
Filed: |
March 7, 2017 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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14599604 |
Jan 19, 2015 |
9597151 |
|
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15451765 |
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13440690 |
Apr 5, 2012 |
8945113 |
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14599604 |
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Current U.S.
Class: |
1/1 |
Current CPC
Class: |
A61B 2090/0807 20160201;
A61B 2018/00023 20130101; A61B 2018/1823 20130101; A61B 2018/1861
20130101; A61B 18/00 20130101; A61B 2018/1853 20130101; A61B
2018/1846 20130101; A61B 2018/00791 20130101; A61B 18/1815
20130101; A61B 90/08 20160201; A61B 2018/1838 20130101; A61B
2018/00577 20130101; A61B 90/06 20160201 |
International
Class: |
A61B 90/00 20060101
A61B090/00; A61B 18/18 20060101 A61B018/18 |
Claims
1-20. (canceled)
21. A system for detecting bending of an electrosurgical device,
comprising: a strain relief configured to be coupled to a shaft of
an electrosurgical device; a piezoelectric actuator disposed within
the strain relief and configured to bend upon bending of the
electrosurgical device; and a bending detection circuit in
electrical communication with the piezoelectric actuator and
configured to detect a bending of the piezoelectric actuator.
22. The system according to claim 21, wherein the piezoelectric
actuator includes a first layer configured to stretch upon bending
of the electrosurgical device and a second layer configured to
compress upon bending of the electrosurgical device.
23. The system according to claim 21, wherein the bending detection
circuit is configured to generate an alarm based on a detection of
bending of the piezoelectric actuator.
24. The system according to claim 21, wherein the bending detection
circuit is disposed within an electrosurgical energy source coupled
to the electrosurgical device.
25. The system according to claim 21, wherein the strain relief is
configured to be coupled to an outer surface of the shaft of the
electrosurgical device.
26. The system according to claim 21, wherein the first and second
layers of the piezoelectric actuator are configured to be coupled
to an outer surface of the shaft of the electrosurgical device.
27. The system according to claim 21, wherein the strain relief is
configured to couple to a hub of the electrosurgical device, the
hub configured to couple the electrosurgical device to an
electrosurgical energy source.
28. The system according to claim 21, wherein the electrosurgical
device is a microwave antenna.
29. The system according to claim 21, wherein the strain relief is
configured to be coaxially disposed around the shaft of the
electrosurgical device.
30. A system for detecting bending of an electrosurgical device,
comprising: a piezoelectric actuator configured to be coupled to a
shaft of an electrosurgical device, the piezoelectric actuator
including at least one layer configured to be disposed
circumferentially around the shaft of the electrosurgical device
and configured to bend upon bending of the electrosurgical device;
and a bending detection circuit in electrical communication with
the piezoelectric actuator and configured to detect a bending of
the piezoelectric actuator.
31. The system according to claim 30, wherein the piezoelectric
actuator includes two layers configured to be disposed
circumferentially around the shaft of the electrosurgical
device.
32. The system according to claim 30, further comprising a strain
relief coupled to the piezoelectric actuator.
33. The system according to claim 32, wherein the strain relief is
configured to be coupled to an outer surface of the shaft of the
electrosurgical device.
34. The system according to claim 32, wherein the strain relief is
configured to be coaxially disposed around the shaft of the
electrosurgical device.
35. The system according to claim 32, wherein the strain relief is
configured to couple to a hub of the electrosurgical device, the
hub configured to couple the electrosurgical device to an
electrosurgical energy source.
36. The system according to claim 30, wherein the electrosurgical
device is a microwave antenna.
37. An antenna assembly having a bending detection system,
comprising: an elongated shaft configured to deliver
electrosurgical energy to tissue; a strain relief coupled to a
proximal portion of the elongated shaft; and a bending detection
circuit in electrical communication with the strain relief and
configured to detect a bending of the strain relief.
38. The antenna assembly according to claim 37, further comprising
a piezoelectric actuator disposed within the strain relief and
configured to bend upon bending of the elongated shaft.
39. The antenna assembly according to claim 37, wherein the strain
relief is coupled to a hub of the antenna assembly, the hub coupled
to the proximal portion of the elongated shaft and configured to
couple the elongated shaft to an electrosurgical energy source.
40. The antenna assembly according to claim 37, wherein the strain
relief is coupled to an outer surface of the elongated shaft.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] The present application is a continuation application of
U.S. patent application Ser. No. 14/599,604 filed Jan. 19, 2015,
which is a continuation of U.S. patent application Ser. No.
13/440,690 filed Apr. 5, 2012, now U.S. Pat. No. 8,945,113, the
contents of each of which are incorporated herein by reference.
BACKGROUND
[0002] 1. Technical Field
[0003] The present disclosure relates to electrosurgical devices
and, more particularly, to electrosurgical tissue ablation systems
capable of detecting excessive bending of a probe shaft and
alerting a user.
[0004] 2. Discussion of Related Art
[0005] Energy-based tissue treatment is well known in the art.
Various types of energy (e.g., electrical, ultrasonic, microwave,
cryogenic, thermal, laser, etc.) are applied to tissue to achieve a
desired result. Electrosurgery involves application of high radio
frequency electrical current to a surgical site to cut, ablate,
coagulate or seal tissue. In monopolar electrosurgery, a source or
active electrode delivers radio frequency energy from the
electrosurgical generator to the tissue and a return electrode
carries the current back to the generator. In monopolar
electrosurgery, the source electrode is typically part of the
surgical instrument held by the surgeon and applied to the tissue
to be treated. A patient return electrode is placed remotely from
the active electrode to carry the current back to the generator. In
tissue ablation electrosurgery, the radio frequency energy may be
delivered to targeted tissue by an antenna or probe.
[0006] There are several types of microwave antenna assemblies in
use, e.g., monopole, dipole and helical, which may be used in
tissue ablation applications. In monopole and dipole antenna
assemblies, microwave energy generally radiates perpendicularly
away from the axis of the conductor. Monopole antenna assemblies
typically include a single, elongated conductor. A typical dipole
antenna assembly includes two elongated conductors, which are
linearly aligned and positioned end-to-end relative to one another
with an electrical insulator placed therebetween. Helical antenna
assemblies include a helically-shaped conductor connected to a
ground plane. Helical antenna assemblies can operate in a number of
modes including normal mode (broadside), in which the field
radiated by the helix is maximum in a perpendicular plane to the
helix axis, and axial mode (end fire), in which maximum radiation
is along the helix axis. The tuning of a helical antenna assembly
may be determined, at least in part, by the physical
characteristics of the helical antenna element, e.g., the helix
diameter, the pitch or distance between coils of the helix, and the
position of the helix in relation to the probe assembly to which it
is mounted.
[0007] The typical microwave antenna has a long, thin inner
conductor that extends along the longitudinal axis of the probe and
is surrounded by a dielectric material and is further surrounded by
an outer conductor around the dielectric material such that the
outer conductor also extends along the axis of the probe. In
another variation of the probe that provides for effective outward
radiation of energy or heating, a portion or portions of the outer
conductor can be selectively removed. This type of construction is
typically referred to as a "leaky waveguide" or "leaky coaxial"
antenna. Another variation on the microwave probe involves having
the tip formed in a uniform spiral pattern, such as a helix, to
provide the necessary configuration for effective radiation. This
variation can be used to direct energy in a particular direction,
e.g., perpendicular to the axis, in a forward direction (i.e.,
towards the distal end of the antenna), or combinations
thereof.
[0008] Invasive procedures and devices have been developed in which
a microwave antenna probe may be either inserted directly into a
point of treatment via a normal body orifice or percutaneously
inserted. Such invasive procedures and devices potentially provide
better temperature control of the tissue being treated. Because of
the small difference between the temperature required for
denaturing malignant cells and the temperature injurious to healthy
cells, a known heating pattern and predictable temperature control
is important so that heating is confined to the tissue to be
treated. For instance, hyperthermia treatment at the threshold
temperature of about 41.5.degree. C. generally has little effect on
most malignant growth of cells. However, at slightly elevated
temperatures above the approximate range of 43.degree. C. to
45.degree. C., thermal damage to most types of normal cells is
routinely observed. Accordingly, great care must be taken not to
exceed these temperatures in healthy tissue.
[0009] Because of the small temperature difference between the
temperature required for denaturing malignant cells and the
temperature normally injurious to healthy cells, a known heating
pattern and precise temperature control is needed to lead to more
predictable temperature distribution to eradicate the tumor cells
while minimizing the damage to surrounding normal tissue. Excessive
temperatures can cause adverse tissue effects. During the course of
heating, tissue in an overly-heated area may become desiccated and
charred. As tissue temperature increases to 100.degree. C., tissue
will lose water content due to evaporation or by the diffusion of
liquid water from treated cells, and the tissue becomes desiccated.
This desiccation of the tissue changes the electrical and other
material properties of the tissue, and may impede treatment. For
example, as the tissue is desiccated, the electrical resistance of
the tissue increases, making it increasingly more difficult to
supply power to the tissue. Desiccated tissue may also adhere to
the device, hindering delivery of power. At tissue temperatures in
excess of 100.degree. C., the solid contents of the tissue begin to
char. Like desiccated tissue, charred tissue is relatively high in
resistance to current and may impede treatment.
[0010] Microwave ablation probes may utilize fluid circulation to
cool thermally-active components and dielectrically load the
antenna radiating section. During operation of a microwave ablation
device, if proper cooling is not maintained, e.g., flow of coolant
fluid is interrupted or otherwise insufficient to cool device
components sensitive to thermal failure, the ablation device may be
susceptible to rapid failures due to the heat generated from the
increased reflected power. In such cases, the time to failure is
dependent on the power delivered to the antenna assembly and the
duration and degree to which coolant flow is reduced or
interrupted.
[0011] Cooling the ablation probe may enhance the overall heating
pattern of the antenna, prevent damage to the antenna and prevent
harm to the clinician or patient. During some procedures, the
amount of cooling may not be sufficient to prevent excessive
heating and resultant adverse tissue effects. Some systems for
cooling an ablation device may allow the ablation device to be
over-cooled, such as when the device is operating at low power
settings. Over-cooling may prevent proper treatment or otherwise
impede device tissue effect by removing thermal energy from the
targeted ablation site.
[0012] Microwave ablation probes come in many lengths with probes
exceeding 30 cm being considered. The probe shaft typically
includes a glass-fiber cooling jacket which is the main structural
member of the probe. There is a certain degree of flexibility
inherent in the jacket. However, excessive bending loads on the
shaft can cause a sudden failure to occur, resulting in the jacket
snapping at the point at which maximum load is placed on the
jacket.
[0013] In several designs of the shaft, a steel hypo-tube is fitted
inside the jacket in the proximal end which functions as a
stiffener. The hypo-tube presents design compromises to the cooling
system and it is not generally desirable. However, if the hypo-tube
were to be removed, bending loads on the shaft are likely to
approach a point at which fracture of the cooling jacket is likely
to occur. Even with the hypo-tube incorporated within the shaft or
other stiffener, it is desirable to prevent excessive bending of
the probe shaft during electrosurgical procedures.
SUMMARY
[0014] The present disclosure relates to an electrosurgical system
including an electrosurgical device having a probe, such as an
ablation probe, configured to direct energy to tissue, and
circuitry for detecting bending, including excessive bending, of
the probe. The circuitry alerts the user of bending, especially
excessive bending of the probe, by activating an alarm, such as an
audible alarm, lighting one or more LEDs or other light sources,
tactile feedback, or any other means.
[0015] Aspects of the present disclosure will be described with
reference to U.S. patent application Ser. No. 13/043,694 filed on
Mar. 9, 2011 having common assignee and inventors as the present
disclosure, the entire contents of which are incorporated herein by
reference. It is understood that the aspects of the present
disclosure and other features thereof can be incorporated in other
electrosurgical systems besides the systems described in U.S.
patent application Ser. No. 13/043,694.
[0016] In aspects described herein, the probe of the
electrosurgical system can have one or more temperature sensors
associated with the electrosurgical device, a fluid-flow path
leading to the electrosurgical device, and a flow-control device
disposed in fluid communication with the fluid-flow path. The
system can further include a processor unit communicatively-coupled
to the one or more temperature sensors and communicatively-coupled
to the flow-control device. The processor unit is configured to
control the flow-control device based on determination of a desired
fluid-flow rate using one or more electrical signals outputted from
the one or more temperature sensors. The processor unit in
embodiments described herein is also configured to determine the
amount of bending of the probe shaft and whether a predetermined
bending threshold has been met or exceeded. The probe can also
include at least one tissue sensor that is configured to sense a
tissue property, e.g., tissue impedance, at or near an ablation
surgical site.
[0017] With more particularity, the present disclosure relates to
an electrosurgical system including an electrosurgical device
having a probe configured to direct energy to tissue, circuitry for
detecting bending, including excessive bending, of the probe, and a
coolant supply system configured to provide coolant fluid to the
electrosurgical device. In one aspect, the bending detection
circuitry includes one or more bending detection members, such as a
piezo transducer (sometimes referred to as piezo sensor or
generator) capable of converting mechanical energy into electrical
energy. The piezo transducer is provided within an outer jacket of
the probe. The piezo transducer can also be provided within a
strain relief of the probe. The strain relief is at a proximal end
of the probe where the probe attaches to a handle. The one or more
piezo transducers sense a compression load or mechanical stress on
one side of the strain relief and/or outer jacket, such as a
glass-fiber cooling jacket, as the probe bends. The sensor outputs
an electrical signal which alerts a user once a threshold voltage
is reached. The user can be alerted by the circuitry activating an
audible alarm, lighting one or more LEDs or other light sources,
tactile feedback, or any other means. The electrical signal can be
fed to the processor unit for determining whether the threshold
voltage has been reached or surpassed prior to the circuitry
alerting the user.
[0018] In another aspect, the one or more bending detection members
are electrical contacts positioned on the outer jacket of the probe
and configured to contact a respective one of two or more
electrical contacts positioned in opposing surfaces of a stationary
fixture or protrusion of the electrosurgical system. Contact
between the electrical contacts is made when the probe is bent a
predetermined amount. A closed circuit is created by one of the
contacts positioned on the probe contacting one of the contacts
positioned on the stationary fixture. The closed circuit alerts the
user of the excessive bending of the probe by activating an audible
alarm, lighting one or more LEDs or other light sources, tactile
feedback, or any other means.
[0019] The coolant supply system can include, for example, as
described in U.S. patent application Ser. No. 13/043,694, a coolant
source, a first fluid-flow path fluidly-coupled to the
electrosurgical device to provide fluid flow from the coolant
source to the electrosurgical device, a second fluid-flow path
fluidly-coupled to the electrosurgical device to provide fluid flow
from the energy applicator to the coolant source, a third
fluid-flow path fluidly-coupled to the first fluid-flow path and
the second fluid-flow path, and a flow-control device disposed in
fluid communication with the third fluid-flow path. The system also
includes one or more temperature sensors associated with the
electrosurgical device and a feedback control system configured to
provide a thermal-feedback-controlled rate of fluid flow to the
electrosurgical device. The feedback control system includes a
processor unit communicatively-coupled to the one or more
temperature sensors and communicatively-coupled to the flow-control
device. The processor unit is configured to control the
flow-control device based on determination of a desired fluid-flow
rate using one or more electrical signals outputted from the one or
more temperature sensors.
[0020] The present disclosure also relates to methods of detecting
bending of a probe and alerting a user when a predetermined bending
threshold has been reached or surpassed. The bending may be
detected while directing energy to tissue using a fluid-cooled
antenna assembly and performing a tissue ablation procedure. The
tissue ablation procedure may include performing at least one
method as described, for example, in U.S. patent application Ser.
No. 13/043,694. One method described therein includes the initial
step of providing an energy applicator. The energy applicator
includes an antenna assembly and a hub providing at least one
coolant connection to the energy applicator. The method also
includes the steps of providing a coolant supply system including a
fluid-flow path fluidly-coupled to the hub for providing fluid flow
to the energy applicator, positioning the energy applicator in
tissue for the delivery of energy to tissue when the antenna
assembly is energized, and providing a thermal-feedback-controlled
rate of fluid flow to the antenna assembly when energized using a
feedback control system operably-coupled to a flow-control device
disposed in fluid communication with the fluid-flow path.
[0021] Another method described in U.S. patent application Ser. No.
13/043,694 includes the initial step of providing an energy
applicator and a coolant supply system configured to provide
coolant fluid to the energy applicator. The energy applicator
includes an antenna assembly and a coolant chamber configured to
circulate coolant fluid around at least a portion of the antenna
assembly. The coolant chamber is fluidly-coupled to the coolant
supply system. The method also includes the steps of positioning
the energy applicator in tissue for the delivery of energy to
tissue when the antenna assembly is energized, and providing a
thermal-feedback-controlled rate of fluid flow to the antenna
assembly when energized by using a feedback control system
including a processor unit configured to control a flow-control
device associated with the coolant supply system based on
determination of a desired fluid-flow rate using one or more
electrical signals outputted from one or more temperature sensors
associated with the energy applicator.
[0022] With more particularity, the present disclosure provides an
electrosurgical system which includes an electrosurgical device
having a probe configured to direct energy to tissue; and bending
detection circuitry having one or more bending detection members
positioned on the probe for detecting bending of the probe. The one
or more bending detection members include one or more actuators.
The one or more actuators are piezoelectric bending actuators
having two or more layers.
[0023] In one aspect, the probe includes a strain relief, and the
one or more bending detection members include one or more actuators
positioned in the strain relief. The one or more actuators are
piezoelectric bending actuators. The one or more piezoelectric
bending actuators include two or more layers.
[0024] In another aspect, the one or more bending detection members
include one or more electrical contacts positioned on the probe for
making contact with another electrical contact not positioned on
the probe when the probe is bent.
[0025] The bending detection circuitry comprises means for alerting
a user of bending of the probe.
[0026] The electrosurgical device further includes an antenna
assembly and a coolant chamber configured to circulate coolant
fluid around at least a portion of the antenna assembly. The
electrosurgical system further includes an electrosurgical
generator for activating the electrosurgical device, and one or
more temperature sensors associated with the electrosurgical
device. A processor unit is communicatively-coupled to the one or
more temperature sensors. The processor unit is configured to
control the flow-control device based on determination of a desired
fluid-flow rate using at least one electrical signal outputted from
the one or more temperature sensors.
[0027] The electrosurgical system further includes a fluid-flow
path leading to the electrosurgical device; a flow-control device
disposed in fluid communication with the fluid-flow path; and a
processor unit communicatively-coupled to the flow-control
device.
[0028] The present disclosure further provides a method for
detecting bending of a probe of an electrosurgical system. The
method includes positioning one or more bending detection members
on the probe; and detecting the bending of the probe by the one or
more bending detection members. The method further includes
alerting a user of the bending of the probe.
[0029] In one aspect, the one or more bending detection members
include one or more actuators. The one or more actuators are
positioned in a strain relief of the probe.
[0030] In another aspect, the one or more bending detection members
include one or more electrical contacts positioned on the probe for
making contact with another electrical contact not positioned on
the probe when the probe is bent.
[0031] As used herein and as is traditional when referring to
relative positioning on an object, the term "proximal" refers to
that portion of the apparatus, or component thereof, closer to the
user and the term "distal" refers to that portion of the apparatus,
or component thereof, farther from the user.
[0032] Electromagnetic energy is generally classified by increasing
energy or decreasing wavelength into radio waves, microwaves,
infrared, visible light, ultraviolet, X-rays and gamma-rays. As it
is used in this description, "microwave" generally refers to
electromagnetic waves in the frequency range of 300 megahertz (MHz)
(3.times.108 cycles/second) to 300 gigahertz (GHz) (3.times.1011
cycles/second).
[0033] As it is used in this description, "ablation procedure"
generally refers to any ablation procedure, such as, for example,
microwave ablation, radiofrequency (RF) ablation, or microwave or
RF ablation-assisted resection. As it is used in this description,
"energy applicator" generally refers to any device that can be used
to transfer energy from a power generating source, such as a
microwave or RF electrosurgical generator, to tissue. For the
purposes herein, the term "energy-delivery device" is
interchangeable with the term "energy applicator". As it is used in
this description, "transmission line" generally refers to any
transmission medium that can be used for the propagation of signals
from one point to another.
[0034] As it is used in this description, "fluid" generally refers
to a liquid, a gas, a liquid containing a dissolved gas or
dissolved gases, a mixture of gas and liquid, gas and suspended
solids, liquid and suspended solids, or a mixture of gas, liquid
and suspended solids. As it is used in this description, "rate of
fluid flow" generally refers to volumetric flow rate. Volumetric
flow rate may be defined as a measure of the volume of fluid
passing a point in a system per unit time, e.g., cubic meters per
second (m3 s-1) in SI units, or cubic feet per second (cu ft/s).
Generally speaking, volumetric fluid-flow rate can be calculated as
the product of the cross-sectional area for flow and the flow
velocity. In the context of mechanical valves, the fluid-flow rate,
in the given through-flow direction, may be considered to be a
function of the variable restriction geometry for a given flow
passage configuration and pressure drop across the restriction. For
the purposes herein, the term "fluid-flow rate" is interchangeable
with the term "rate of fluid flow".
[0035] As it is used in this description, "pressure sensor"
generally refers to any pressure-sensing device capable of
generating a signal representative of a pressure value. For the
purposes herein, the term "pressure transducer" is interchangeable
with the term "pressure sensor".
[0036] As it is used herein, the term "computer" generally refers
to anything that transforms information in a purposeful way. For
the purposes of this description, the terms "software" and "code"
should be interpreted as being applicable to software, firmware, or
a combination of software and firmware. For the purposes of this
description, "non-transitory" computer-readable media include all
computer-readable media, with the sole exception being a
transitory, propagating signal.
BRIEF DESCRIPTION OF THE DRAWINGS
[0037] Aspects and features of the presently-disclosed systems for
electrosurgical tissue ablation systems capable of detecting
excessive bending of a probe shaft and alerting a user will become
apparent to those of ordinary skill in the art when descriptions
thereof are read with reference to the accompanying drawings, of
which:
[0038] FIG. 1 is a schematic diagram of an electrosurgical system
including an energy-delivery device and circuitry for detecting
bending, including excessive bending, of an ablation probe of the
electrosurgical system in accordance with an embodiment of the
present disclosure;
[0039] FIG. 2 is a perspective, phantom view of the ablation probe
and a strain relief surrounding a portion of the ablation probe
having one or more piezoelectric bending actuators or generators
for detecting bending, including excessive bending, of the probe in
accordance with an embodiment of the present disclosure;
[0040] FIG. 3 is a cross-sectional view of the ablation probe and
the strain relief shown by FIG. 2 being bent in a first direction
causing a two-layer piezoelectric bending actuator or generator
within the strain relief to bend (one layer of the actuator is
compressed and the other layer is stretched);
[0041] FIG. 4 is a perspective, cut-away view of an ablation probe
of the electrosurgical system shown by FIG. 1 having one or more
piezoelectric bending actuators or generators for detecting
bending, including excessive bending, of the probe in accordance
with another embodiment of the present disclosure;
[0042] FIG. 5 is a cross-sectional view of the ablation probe shown
by FIG. 4 being bent in a first direction causing a two-layer
piezoelectric bending actuator or generator within the ablation
probe to bend (one layer of the actuator is compressed and the
other layer is stretched);
[0043] FIG. 6 is a perspective view of an alternative embodiment of
the ablation probe of the electrosurgical system shown by FIG. 1
having at least two electrical contacts on a shaft of the probe and
at least two electrical contacts in proximity to the shaft for
detecting bending, including excessive bending, of the probe in
accordance with the present disclosure; and
[0044] FIG. 7 is perspective view of the ablation probe of FIG. 6
showing an electrical contact on the shaft of the probe making
contact with an electrical contact in proximity to the shaft due to
bending of the probe.
DETAILED DESCRIPTION
[0045] Hereinafter, embodiments of the presently-disclosed systems
for thermal-feedback-controlled rate of fluid flow to a
fluid-cooled antenna assembly and methods of directing energy to
tissue using the same are described with reference to the
accompanying drawings. Like reference numerals may refer to similar
or identical elements throughout the description of the
figures.
[0046] This description may use the phrases "in an embodiment," "in
embodiments," "in some embodiments," or "in other embodiments,"
which may each refer to one or more of the same or different
embodiments in accordance with the present disclosure. For the
purposes of this description, a phrase in the form "A/B" means A or
B. For the purposes of the description, a phrase in the form "A
and/or B" means "(A), (B), or (A and B)". For the purposes of this
description, a phrase in the form "at least one of A, B, or C"
means "(A), (B), (C), (A and B), (A and C), (B and C), or (A, B and
C)".
[0047] Various embodiments of the present disclosure provide
systems for detecting bending, including excessive bending, of an
electrosurgical device, such as an ablation probe, of an
electrosurgical system. The ablation probe, for exemplary purposes
in describing the various embodiments of the present disclosure, is
an ablation probe including a fluid-cooled antenna assembly.
Additionally, the electrosurgical system includes a
thermal-feedback-controlled rate of fluid flow to control the fluid
flow to the ablation probe. It is contemplated that embodiments of
the present disclosure for detecting bending, including excessive
bending, of an ablation probe or other electrosurgical device can
be implemented, integrated and/or otherwise incorporated in other
systems and electrosurgical devices which are not described or
mentioned herein. The description of the embodiments of the present
disclosure to certain systems, especially electrosurgical systems,
is for exemplary purposes only and shall not be construed as
limiting the embodiments described herein to only these systems and
variants thereof. That is, for example, embodiments may be
implemented using electromagnetic radiation at microwave
frequencies or at other frequencies.
[0048] An electrosurgical system including a detection system for
detecting bending, including excessive bending, of an ablation
probe, a coolant supply system and a feedback control system
configured to provide a thermal-feedback-controlled rate of fluid
flow to an energy applicator, according to various embodiments, is
designed and configured to operate between about 300 MHz and about
10 GHz. Systems for detecting bending of the ablation probe and for
thermal-feedback-controlled rate of fluid flow to electrosurgical
devices, as described herein, may be used in conjunction with
various types of devices, such as microwave antenna assemblies
having either a straight or looped radiating antenna portion, etc.,
which may be inserted into or placed adjacent to tissue to be
treated.
[0049] Various embodiments of the presently-disclosed
electrosurgical systems including a detection system for detecting
bending, including excessive bending, of an ablation probe and
feedback control system configured to provide a
thermal-feedback-controlled rate of fluid flow to an energy
applicator disposed in fluid communication with a coolant supply
system are suitable for microwave ablation and for use to
pre-coagulate tissue for microwave ablation-assisted surgical
resection. Although various methods described hereinbelow are
targeted toward microwave ablation and the complete destruction of
target tissue, it is to be understood that methods for directing
electromagnetic radiation may be used with other therapies in which
the target tissue is partially destroyed or damaged, such as, for
example, to prevent the conduction of electrical impulses within
heart tissue. In addition, although the following description
describes the use of a dipole microwave antenna, the teachings of
the present disclosure may also apply to a monopole, helical, or
other suitable type of antenna assembly.
[0050] FIG. 1 shows an electrosurgical system 10 according to an
embodiment of the present disclosure that includes an energy
applicator or probe 100, an electrosurgical power generating source
28, e.g., a microwave or RF electrosurgical generator, detection
circuitry 84 for detecting bending, including excessive bending of
the probe 100 using at least one signal transmitted to the
detection circuitry 84 via transmission line 15, and a feedback
control system 14 operably associated with a coolant supply system
11. Probe 100 is operably-coupled to the electrosurgical power
generating source 28, and disposed in fluid communication with the
coolant supply system 11. In some embodiments, one or more
components of the coolant supply system 11 may be integrated fully
or partially into the electrosurgical power generating source 28.
Coolant supply system 11, which is described in more detail later
in this description, is configured to provide coolant fluid "F" to
the probe 100. Probe 100, which is described in more detail later
in this description, may be integrally associated with a hub 142
configured to provide electrical and/or coolant connections to the
probe.
[0051] The probe 100 includes a strain relief 200. The strain
relief 200 is fixed to a surface of the hub 142 to counter
mechanical stress when the probe 100 bends during an
electrosurgical procedure. The strain relief 200, as further
described below with reference to FIG. 2, includes one or more
piezoelectric bending actuators or generators for detecting
bending, including excessive bending, of the probe 100. In some
embodiments, the probe 100 may extend from a handle assembly (not
shown).
[0052] With reference to FIG. 2, there is shown a perspective,
phantom view of ablation probe 100 and strain relief 200 with the
bending detection circuitry 84 having one or more bending detection
members, such as one or more piezoelectric bending actuators or
generators 202, within the strain relief 200 for use in detecting
bending, including excessive bending, of the probe 100. FIG. 3
shows a cross-sectional view of the ablation probe 100 and strain
relief 200 shown by FIG. 2 being bent in a first direction causing
the two-layer piezoelectric bending actuator or generator 202
within the strain relief 200 to bend. That is, during bending of
the outer jacket 139 of the probe 100, the strain relief 200 also
bends. The bending of the strain relief 200 causes one layer 204 of
the actuator 202 to be stretched and the other layer 206 to be
compressed (see FIG. 3). The bending of the strain relief 200 and
the actuator therein 202 is detected by the detection circuitry 84.
If the bending is detected to be beyond a predetermined threshold,
i.e., excessive bending is detected by the detection circuitry 84,
the detection circuitry 84 generates a signal for activating an
audible alarm, lighting one or more LEDs or other light sources,
tactile feedback, or any other means for notifying the user of the
excessive bending.
[0053] With reference to FIGS. 4 and 5, there is shown a
perspective, cut-away view and a cross-sectional view,
respectively, of an alternate embodiment. In this embodiment, one
or more piezoelectric bending actuators or generators 202 are
placed within the ablation probe 100, such as, for example, under
the outer jacket 139 of the probe 100 instead of within the strain
relief 200. As with the embodiment described above with reference
to FIGS. 2 and 3, the bending detection circuitry 84 utilizes the
one or more piezoelectric bending actuators or generators 202
within the probe 100 to detect bending, including excessive
bending, of the probe 100.
[0054] FIG. 5 illustrates the ablation probe 100 shown by FIG. 4
being bent in a first direction causing the two-layer piezoelectric
bending actuator or generator 202 within the probe 100 to bend.
That is, during bending of the outer jacket 139 of the probe 100,
one layer 204' of the actuator 202 is stretched and the other layer
206' is compressed. The bending of the outer jacket 139 and the
actuator 202 therein is detected by the detection circuitry 84. If
the bending is detected to be beyond a predetermined threshold,
i.e., excessive bending is detected by the detection circuitry 84,
the detection circuitry 84 generates a signal for activating an
audible alarm, lighting one or more LEDs or other light sources,
tactile feedback, or any other means for notifying the user of the
excessive bending.
[0055] It is envisioned that the one or more piezoelectric bending
actuators or generators 202 can be replaced or used in conjunction
with any other device or apparatus capable of detecting bending of
the probe 100. It is also envisioned in an alternate embodiment
that a piezoelectric bending actuator or generator 202 may be
placed within the strain relief 200 and within the probe 100.
[0056] The actuator 202 shown in the embodiments of FIGS. 2-5 can
be a multilayer ceramic piezoelectric bending actuator available
from Noliac A/S based in Denmark or piezoelectric bending actuators
available from Piezo Systems, Inc., Woburn, Mass. Even though FIGS.
2 and 3, show a two-layer bending actuator 202, other types of
bending actuators can be used, such as 2-layer circular bending
disk actuators, 4-layer rectangular bending actuators, etc.
[0057] In another embodiment shown by FIGS. 6 and 7, two or more
electrical contacts 402, 404 are positioned in opposing surfaces of
two stationary fixtures, protrusions or extensions 406, 408
extending from the hub body 145. In this embodiment, the bending
detection members include two or more electrical contacts 410, 412
positioned on the outer jacket 139 of the probe 100 and configured
to contact a respective one of the two electrical contacts 402, 404
positioned on the two stationary fixtures 406, 408 when the probe
100 is bent a predetermined amount. A closed circuit is created by
one of the contacts 410, 412 positioned on the probe 100 contacting
one of the contacts 402, 404 positioned on the fixtures 406, 408 as
shown by FIG. 7. The closed circuit alerts the user of the
excessive bending of the probe 100 by activating an audible alarm,
lighting one or more LEDs or other light sources, tactile feedback,
or any other means.
[0058] In some embodiments, the electrosurgical system 10 includes
one or more sensors capable of generating a signal indicative of a
temperature of a medium in contact therewith (referred to herein as
temperature sensors) and/or one or more sensors capable of
generating a signal indicative of a rate of fluid flow (referred to
herein as flow sensors). In such embodiments, the feedback control
system 14 may be configured to provide a
thermal-feedback-controlled rate of fluid flow to the probe 100
using one or more signals output from one or more temperature
sensors and/or one or more flow sensors operably associated with
the probe 100 and/or conduit fluidly-coupled to the probe 100.
[0059] An embodiment of a feedback control system, such as the
feedback control system 14 of FIG. 1, in accordance with the
present disclosure, is shown in more detail in FIG. 2. It is to be
understood, however, that other feedback control system embodiments
(e.g., feedback control systems 414 and 514 shown in FIGS. 4 and 5,
respectively) may be used in conjunction with coolant supply
systems in various configurations. In some embodiments, the
feedback control system 14, or component(s) thereof, may be
integrated fully or partially into the electrosurgical power
generating source 28.
[0060] In the embodiment shown in FIG. 1, the feedback control
system 14 is operably associated with a processor unit 82 disposed
within or otherwise associated with the electrosurgical power
generating source 28. Processor unit 82 may be
communicatively-coupled to one or more components or modules of the
electro surgical power generating source 28, e.g., a user interface
121 and a generator module 86. Processor unit 82 may additionally,
or alternatively, be communicatively-coupled to one or more
temperature sensors (e.g., two sensors "TS1" and "TS2" shown in
FIG. 1) and/or one or more flow sensors (e.g., one sensor "FS1"
shown in FIG. 1) for receiving one or more signals indicative of a
temperature (referred to herein as temperature data) and/or one or
more signals indicative of a flow rate (referred to herein as flow
data). Transmission lines may be provided to electrically couple
the temperature sensors, flow sensors and/or other sensors, e.g.,
pressure sensors, to the processor unit 82.
[0061] Feedback control system embodiments may additionally, or
alternatively, be operably associated with a processor unit
deployed in a standalone configuration, and/or a processor unit
disposed within the probe 100 or otherwise associated therewith. In
some embodiments, where the probe 100 extends from a handle
assembly (not shown), the feedback control system may be operably
associated with a processor unit disposed within the handle
assembly. Examples of handle assembly embodiments are disclosed in
commonly assigned U.S. patent application Ser. No. 12/686,726 filed
on Jan. 13, 2010, entitled "ablation device with user interface at
device handle, system including same, and method of ablating tissue
using same".
[0062] Electrosurgical power generating source 28 may include any
generator suitable for use with electrosurgical devices, and may be
configured to provide various frequencies of electromagnetic
energy. In some embodiments, the electrosurgical power generating
source 28 is configured to provide microwave energy at an
operational frequency from about 300 MHz to about 10 GHz. In some
embodiments, the electrosurgical power generating source 28 is
configured to provide electrosurgical energy at an operational
frequency from about 400 KHz to about 500 KHz. An embodiment of an
electrosurgical power generating source, such as the
electrosurgical power generating source 28 of FIG. 1, in accordance
with the present disclosure, is shown in more detail in FIG. 3.
[0063] Probe 100 may include one or more antennas of any suitable
type, such as an antenna assembly (or antenna array) suitable for
use in tissue ablation applications. For ease of explanation and
understanding, the probe 100 is described as including a single
antenna assembly 112. In some embodiments, the antenna assembly 112
is substantially disposed within a sheath 138. Probe 100 generally
includes a coolant chamber 137 defined about the antenna assembly
112. In some embodiments, the coolant chamber 137, which is
described in more detail later in this description, includes an
interior lumen defined by the sheath 138.
[0064] Probe 100 may include a feedline 110 coupled to the antenna
assembly 112. A transmission line 16 may be provided to
electrically couple the feedline 110 to the electrosurgical power
generating source 28. Feedline 110 may be coupled to a connection
hub 142, which is described in more detail later in this
description, to facilitate the flow of coolant and/or buffering
fluid into, and out of, the probe 100.
[0065] In the embodiment shown in FIG. 1, the feedback control
system 14 is operably associated with a flow-control device 50
disposed in fluid communication with a fluid-flow path of the
coolant supply system 11 (e.g., first coolant path 19)
fluidly-coupled to the probe 100. Flow-control device 50 may
include any suitable device capable of regulating or controlling
the rate of fluid flow passing though the flow-control device 50,
e.g., a valve of any suitable type operable to selectively impede
or restrict flow of fluid through passages in the valve. Processor
unit 82 may be configured to control the flow-control device 50
based on determination of a desired fluid-flow rate using
temperature data received from one or more temperature sensors
(e.g., "TS1", "TS2" through "TSN" shown in FIG. 1).
[0066] In some embodiments, the flow-control device 50 includes a
valve 52 including a valve body 54 and an electromechanical
actuator 56 operatively-coupled to the valve body 54. Valve body 54
may be implemented as a ball valve, gate valve, butterfly valve,
plug valve, or any other suitable type of valve. In the embodiment
shown in FIG. 1, the actuator 56 is communicatively-coupled to with
the processor unit 82 via a transmission line 32. Processor unit 82
may be configured to control the flow-control device 50 by
activating the actuator 56 to selectively adjust the fluid-flow
rate in a fluid-flow path (e.g., first coolant path 19 of the
coolant supply system 11) fluidly-coupled to the connection hub 142
to achieve a desired fluid-flow rate. The desired fluid-flow rate
may be determined by a computer program and/or logic circuitry
associated with the processor unit 82. The desired fluid-flow rate
may additionally, or alternatively, be selected from a look-up
table "TX,Y" (shown in FIGS. 2 and 5) or determined by a computer
algorithm stored within a memory device 8 (shown in FIGS. 2 and
5).
[0067] Embodiments including a suitable pressure-relief device 40
disposed in fluid communication with the diversion flow path 21 may
allow the fluid-movement device 60 to run at a substantially
constant speed and/or under a near-constant load (head pressure)
regardless of the selective adjustment of the fluid-flow rate in
the first coolant path 19. Utilizing a suitable pressure-relief
device 40 disposed in fluid communication with the diversion flow
path 21, in accordance with the present disclosure, may allow the
fluid-movement device 60 to be implemented as a single speed
device, e.g., a single speed pump.
[0068] Feedback control system 14 may utilize data "D" (e.g., data
representative of a mapping of temperature data to settings for
properly adjusting one or more operational parameters of the
flow-control device 50 to achieve a desired temperature and/or a
desired ablation) stored in a look-up table "TX,Y" (shown in FIGS.
2 and 5), where X denotes columns and Y denotes rows, or other data
structure, to determine the desired fluid-flow rate. In the
embodiment shown in FIG. 1, the electrosurgical system 10 includes
a first temperature sensor "TS1" capable of generating a signal
indicative of a temperature of a medium in contact therewith and a
second temperature sensor "TS2" capable of generating a signal
indicative of a temperature of a medium in contact therewith.
Feedback control system 14 may be configured to utilize signals
received from the first temperature sensor "TS1" and/or the second
temperature sensor "TS2" to control the flow-control device 50.
[0069] In some embodiments, the electrosurgical system 10 includes
a flow sensor "FS1" communicatively-coupled to the processor unit
82, e.g., via a transmission line 36. In some embodiments, the flow
sensor "FS1" may be disposed in fluid communication with the first
coolant path 19 or the second coolant path 20. Processor unit 82
may be configured to control the flow-control device 50 based on
determination of a desired fluid-flow rate using one or more
signals received from the flow sensor "FS1". In some embodiments,
the processor unit 82 may be configured to control the flow-control
device 50 based on determination of a desired fluid-flow rate using
one or more signals received from the flow sensor "FS1" in
conjunction with one or more signals received from the first
temperature sensor "TS1" and/or the second temperature sensor
"TS2". Although the electrosurgical system 10 shown in FIG. 1
includes one flow sensor "FS1", alternative embodiments may be
implemented with a plurality of flow sensors (e.g., "FS1", "FS2"
through "FSM" shown in FIG. 1) adapted to provide a measurement of
the rate of fluid flow into and/or out of the probe 100 and/or
conduit fluidly-coupled to the probe 100.
[0070] Electrosurgical system 10 may additionally, or
alternatively, include one or more pressure sensors configured to
provide a measurement of the fluid pressure in the probe 100 and/or
conduit fluidly-coupled the probe 100. In some embodiments, the
electrosurgical system 10 includes one or more pressure sensors
(e.g., pressure sensor 70) disposed in fluid communication with one
or more fluid-flow paths (e.g., first coolant path 19) of the
coolant supply system 11 as opposed to a pressure sensor disposed
within the probe 100, reducing cost and complexity of the probe
100.
[0071] In the embodiment shown in FIG. 1, the processor unit 82 is
operably associated with a pressure sensor 70 disposed in fluid
communication with a fluid-flow path of the coolant supply system
11. Processor unit 82 may be communicatively-coupled to the
pressure sensor 70 via a transmission line 30 or wireless link.
Processor unit 82 may additionally, or alternatively, be operably
associated with one or more pressure sensors disposed within the
probe 100, e.g., disposed in fluid communication with the coolant
chamber 137.
[0072] Pressure sensor 70 may include any suitable type of pressure
sensor, pressure transducer, pressure transmitter, or pressure
switch. Pressure sensor 70 (also referred to herein as "pressure
transducer") may include a variety of components, e.g., resistive
elements, capacitive elements and/or piezo-resistive elements, and
may be disposed at any suitable position in the coolant supply
system 11. In some embodiments, the pressure transducer 70 is
disposed in fluid communication with the first coolant path 19
located between the fluid-movement device 60 and the flow-control
device 50, e.g., placed at or near the flow-control device 50.
[0073] In some embodiments, the processor unit 82 may be configured
to control the flow-control device 50 based on determination of a
desired fluid-flow rate using pressure data received from one or
more pressure sensors. In some embodiments, the processor unit 82
may be configured to control the flow-control device 50 based on
determination of a desired fluid-flow rate using one or more
signals received from the first temperature sensor "TS1" and/or the
second temperature sensor "TS2" and/or the flow sensor "FS1" in
conjunction with one or more signals received from the pressure
transducer 70.
[0074] In some embodiments, the processor unit 82 may be configured
to control the amount of power delivered to the antenna assembly
112 based on time and power settings provided by the user in
conjunction with sensed temperature signals indicative of a
temperature of a medium, e.g., coolant fluid "F", in contact with
one or one temperature sensors operably associated with the antenna
assembly 112 and/or the connection hub 142. In some embodiments,
the processor unit 82 may be configured to increase and/or decrease
the amount of power delivered to the antenna assembly 112 when
sensed temperature signals indicative of a temperature below/above
a predetermined temperature threshold are received by processor
unit 82, e.g., over a predetermined time interval.
[0075] Processor unit 82 may be configured to control one or more
operating parameters associated with the electrosurgical power
generating source 28 based on determination of whether the pressure
level of fluid in the probe 100 and/or conduit fluidly-coupled to
the probe 100 is above a predetermined threshold using pressure
data received from one or more pressure sensors, e.g., pressure
transducer 70. Examples of operating parameters associated with the
electrosurgical power generating source 28 include without
limitation temperature, impedance, power, current, voltage, mode of
operation, and duration of application of electromagnetic
energy.
[0076] In some embodiments, the output signal of the pressure
transducer 70, representing a pressure value and possibly amplified
and/or conditioned by means of suitable components (not shown), is
received by the processor unit 82 and used for determination of
whether the pressure level of fluid in the probe 100 and/or conduit
fluidly-coupled to the probe 100 is above a predetermined threshold
in order to control when power is delivered to the antenna assembly
112. In some embodiments, in response to a determination that the
pressure level of fluid in the probe 100 and/or conduit
fluidly-coupled to the probe 100 is below the predetermined
threshold, the processor unit 82 may be configured to decrease the
amount of power delivered to the antenna assembly 112 and/or to
stop energy delivery between the electrosurgical power generating
source 28 and the probe 100. In some embodiments, the processor
unit 82 may be configured to enable energy delivery between the
electrosurgical power generating source 28 and the probe 100 based
on determination that the pressure level of fluid in the probe 100
and/or conduit fluidly-coupled to the probe 100 is above the
predetermined threshold.
[0077] In some embodiments, the pressure transducer 70 is adapted
to output a predetermined signal to indicate a sensed pressure
below that of the burst pressure of the pressure-relief device 40.
A computer program and/or logic circuitry associated with the
processor unit 82 may be configured to enable the electrosurgical
power generating source 28 and the flow-control device 50 in
response to a signal from the pressure transducer 70. A computer
program and/or logic circuitry associated with the processor unit
82 may be configured to output a signal indicative of an error code
and/or to activate an indicator unit 129 if a certain amount of
time elapses between the point at which energy delivery to the
probe 100 is enabled and when the pressure signal is detected,
e.g., to ensure that the fluid-movement device 60 is turned on
and/or that the probe 100 is receiving flow of fluid before the
antenna assembly 112 can be activated.
[0078] As shown in FIG. 1, a feedline 110 couples the antenna
assembly 112 to a connection hub 142. Connection hub 142 may have a
variety of suitable shapes, e.g., cylindrical, rectangular, etc.
Connection hub 142 generally includes a hub body 145 defining an
outlet fluid port 177 and an inlet fluid port 179. Hub body 145 may
include one or more branches, e.g., three branches 164, 178 and
176, extending from one or more portions of the hub body 145. In
some embodiments, one or more branches extending from the hub body
145 may be configured to house one or more connectors and/or ports,
e.g., to facilitate the flow of coolant and/or buffering fluid
into, and out of, the connection hub 142.
[0079] In the embodiment shown in FIG. 1, the hub body 145 includes
a first branch 164 adapted to house a cable connector 165, a second
branch 178 adapted to house the inlet fluid port 179, and a third
branch 176 adapted to house the outlet fluid port 177. It is to be
understood, however, that other connection hub embodiments may also
be used. Examples of hub embodiments are disclosed in commonly
assigned U.S. patent application Ser. No. 12/401,268 filed on Mar.
10, 2009, entitled "COOLED DIELECTRICALLY BUFFERED MICROWAVE DIPOLE
ANTENNA", and U.S. Pat. No. 7,311,703, entitled "DEVICES AND
METHODS FOR COOLING MICROWAVE ANTENNAS".
[0080] In some embodiments, the flow sensor "FS1" is disposed in
fluid communication with the first coolant path 19, e.g., disposed
within the inlet fluid port 179 or otherwise associated with the
second branch 178, and the second temperature sensor "TS2" is
disposed in fluid communication with the second coolant path 20,
e.g., disposed within the outlet fluid port 177 or otherwise
associated with the third branch 176. In other embodiments, the
second temperature sensor "TS2" may be disposed within the inlet
fluid port 179 or otherwise associated with the second branch 178,
and the flow sensor "FS1" may be disposed within the outlet fluid
port 177 or otherwise associated with the third branch 176.
[0081] Coolant supply system 11 generally includes a substantially
closed loop having a first coolant path 19 leading to the probe 100
and a second coolant path 20 leading from the probe 100, a coolant
source 90, and a fluid-movement device 60, e.g., disposed in fluid
communication with the first coolant path 19. In some embodiments,
the coolant supply system 11 includes a third coolant path 21 (also
referred to herein as a "diversion flow path") disposed in fluid
communication with the first coolant path 19 and the second coolant
path 20. The conduit layouts of the first coolant path 19, second
coolant path 20 and third coolant path 21 may be varied from the
configuration depicted in FIG. 1.
[0082] In some embodiments, a pressure-relief device 40 may be
disposed in fluid communication with the diversion flow path 21.
Pressure-relief device 40 may include any type of device, e.g., a
spring-loaded pressure-relief valve, adapted to open at a
predetermined set pressure and to flow a rated capacity at a
specified over-pressure. In some embodiments, one or more
flow-restrictor devices (not shown) suitable for preventing
backflow of fluid into the first coolant path 19 may be disposed in
fluid communication with the diversion flow path 21.
Flow-restrictor devices may include a check valve or any other
suitable type of unidirectional flow restrictor or backflow
preventer, and may be disposed at any suitable position in the
diversion flow path 21 to prevent backflow of fluid from the
diversion flow path 21 into the first coolant path 19.
[0083] In some embodiments, the first coolant path 19 includes a
first coolant supply line 66 leading from the coolant source 90 to
the fluid-movement device 60, a second coolant supply line 67
leading from the fluid-movement device 60 to the flow-control
device 50, and a third coolant supply line 68 leading from the
flow-control device 50 to the inlet fluid port 179 defined in the
second branch 178 of the connection hub body 145, and the second
coolant path 20 includes a first coolant return line 95 leading
from the outlet fluid port 177 defined in the third branch 176 of
the hub body 145 to the coolant source 90. Embodiments including
the diversion flow path 21 may include a second coolant return line
94 fluidly-coupled to the second coolant supply line 67 and the
first coolant return line 95. Pressure-relief device 40 may be
disposed at any suitable position in the second coolant return line
94. The spacing and relative dimensions of coolant supply lines and
coolant return lines may be varied from the configuration depicted
in FIG. 1.
[0084] Coolant source 90 may be any suitable housing containing a
reservoir of coolant fluid "F". Coolant fluid "F" may be any
suitable fluid that can be used for cooling or buffering the probe
100, e.g., deionized water, or other suitable cooling medium.
Coolant fluid "F" may have dielectric properties and may provide
dielectric impedance buffering for the antenna assembly 112.
Coolant fluid "F" may be a conductive fluid, such as a saline
solution, which may be delivered to the target tissue, e.g., to
decrease impedance and allow increased power to be delivered to the
target tissue. A coolant fluid "F" composition may vary depending
upon desired cooling rates and the desired tissue impedance
matching properties. Various fluids may be used, e.g., liquids
including, but not limited to, water, saline, perfluorocarbon, such
as the commercially available Fluorinert.RTM. perfluorocarbon
liquid offered by Minnesota Mining and Manufacturing Company (3M),
liquid chlorodifluoromethane, etc. In other variations, gases (such
as nitrous oxide, nitrogen, carbon dioxide, etc.) may also be
utilized as the cooling fluid. In yet another variation, a
combination of liquids and/or gases, including, for example, those
mentioned above, may be utilized as the coolant fluid "F".
[0085] In the embodiment shown in FIG. 1, the fluid-movement device
60 is provided in the first coolant path 19 to move the coolant
fluid "F" through the first coolant path 19 and into, and out of,
the probe 100. Fluid-movement device 60 may include valves, pumps,
power units, actuators, fittings, manifolds, etc. The position of
the fluid-movement device 60, e.g., in relation to the coolant
source 90, may be varied from the configuration depicted in FIG. 1.
Although the coolant supply system 11 shown in FIG. 1 includes a
single, fluid-movement device 60 located in the first coolant path
19, various combinations of different numbers of fluid-movement
devices, variedly-sized and variedly-spaced apart from each other,
may be provided in the first coolant path 19 and/or the second
coolant path 20.
[0086] In some embodiments, the probe 100 includes a feedline 110
that couples the antenna assembly 112 to a hub, e.g., connection
hub 142, that provides electrical and/or coolant connections to the
probe 100. Feedline 110 may be formed from a suitable flexible,
semi-rigid or rigid microwave conductive cable. Feedline 110 may be
constructed of a variety of electrically-conductive materials,
e.g., copper, gold, or other conductive metals with similar
conductivity values. Feedline 110 may be made of stainless steel,
which generally offers the strength required to puncture tissue
and/or skin.
[0087] In some variations, the antenna assembly 112 includes a
distal radiating portion 105 and a proximal radiating portion 140.
In some embodiments, a junction member (not shown), which is
generally made of a dielectric material, couples the proximal
radiating section 140 and the distal radiating section 105. In some
embodiments, the distal and proximal radiating sections 105, 140
align at the junction member and are also supported by an inner
conductor (not shown) that extends at least partially through the
distal radiating section 105.
[0088] Antenna assembly 112 may be provided with an end cap or
tapered portion 120, which may terminate in a sharp tip 123 to
allow for insertion into tissue with minimal resistance. One
example of a straight probe with a sharp tip that may be suitable
for use as the energy applicator 100 is commercially available
under the trademark EVIDENT.TM. offered by Covidien. The end cap or
tapered portion 120 may include other shapes, such as, for example,
a tip 123 that is rounded, flat, square, hexagonal, or
cylindroconical. End cap or tapered portion 120 may be formed of a
material having a high dielectric constant, and may be a
trocar.
[0089] Sheath 138 generally includes an outer jacket 139 defining a
lumen into which the antenna assembly 112, or portion thereof, may
be positioned. In some embodiments, the sheath 138 is disposed over
and encloses the feedline 110, the proximal radiating portion 140
and the distal radiating portion 105, and may at least partially
enclose the end cap or tapered portion 120. The outer jacket 139
may be formed of any suitable material, such as, for example,
polymeric or ceramic materials. The outer jacket 139 may be a
water-cooled catheter formed of a material having low electrical
conductivity.
[0090] In accordance with the embodiment shown in FIG. 1, a coolant
chamber 137 is defined by the outer jacket 139 and the end cap or
tapered portion 120. Coolant chamber 137 is disposed in fluid
communication with the inlet fluid port 179 and the outlet fluid
port 177 and adapted to circulate coolant fluid "F" therethrough,
and may include baffles, multiple lumens, flow restricting devices,
or other structures that may redirect, concentrate, or disperse
flow depending on their shape. Examples of coolant chamber
embodiments are disclosed in commonly assigned U.S. patent
application Ser. No. 12/350,292 filed on Jan. 8, 2009, entitled
"CHOKED DIELECTRIC LOADED TIP DIPOLE MICROWAVE ANTENNA", commonly
assigned U.S. patent application Ser. No. 12/401,268 filed on Mar.
10, 2009, entitled "COOLED DIELECTRICALLY BUFFERED MICROWAVE DIPOLE
ANTENNA", and U.S. Pat. No. 7,311,703, entitled "DEVICES AND
METHODS FOR COOLING MICROWAVE ANTENNAS". The size and shape of the
sheath 138 and the coolant chamber 137 extending therethrough may
be varied from the configuration depicted in FIG. 1.
[0091] During microwave ablation, e.g., using the electrosurgical
system 10, the probe 100 is inserted into or placed adjacent to
tissue and microwave energy is supplied thereto. Ultrasound or
computed tomography (CT) guidance may be used to accurately guide
the probe 100 into the area of tissue to be treated. Probe 100 may
be placed percutaneously or atop tissue, e.g., using conventional
surgical techniques by surgical staff. A clinician may
pre-determine the length of time that microwave energy is to be
applied. Application duration may depend on many factors such as
tumor size and location and whether the tumor was a secondary or
primary cancer. The duration of microwave energy application using
the probe 100 may depend on the progress of the heat distribution
within the tissue area that is to be destroyed and/or the
surrounding tissue. Single or multiple probes 100 may be used to
provide ablations in short procedure times, e.g., a few seconds to
minutes, to destroy cancerous cells in the target tissue
region.
[0092] A plurality of probes 100 may be placed in variously
arranged configurations to substantially simultaneously ablate a
target tissue region, making faster procedures possible. Multiple
probes 100 can be used to synergistically create a large ablation
or to ablate separate sites simultaneously. Tissue ablation size
and geometry is influenced by a variety of factors, such as the
energy applicator design, number of energy applicators used
simultaneously, time and wattage.
[0093] In operation, microwave energy having a wavelength, lambda
(.lamda.), is transmitted through the antenna assembly 112, e.g.,
along the proximal and distal radiating portions 140, 105, and
radiated into the surrounding medium, e.g., tissue. The length of
the antenna for efficient radiation may be dependent on the
effective wavelength .lamda.eff which is dependent upon the
dielectric properties of the medium being radiated. Antenna
assembly 112, through which microwave energy is transmitted at a
wavelength .lamda., may have differing effective wavelengths
.lamda.eff depending upon the surrounding medium, e.g., liver
tissue as opposed to breast tissue.
[0094] In some embodiments, the electrosurgical system 10 includes
a first temperature sensor "TS1" disposed within a distal radiating
portion 105 of the antenna assembly 112. First temperature sensor
"TS1" may be disposed within or contacting the end cap or tapered
portion 120. It is to be understood that the first temperature
sensor "TS1" may be disposed at any suitable position to allow for
the sensing of temperature. Processor unit 82 may be electrically
connected by a transmission line 34 to the first temperature sensor
"TS1". Sensed temperature signals indicative of a temperature of a
medium in contact with the first temperature sensor "TS1" may be
utilized by the processor unit 82 to control the flow of
electrosurgical energy and/or the flow rate of coolant to attain
the desired ablation.
[0095] Electrosurgical system 10 may additionally, or
alternatively, include a second temperature sensor "TS2" disposed
within the outlet fluid port 177 or otherwise associated with the
third branch 176 of the hub body 145. Processor unit 82 may be
electrically connected by a transmission line 38 to the second
temperature sensor "TS2". First temperature sensor "TS1" and/or the
second temperature sensor "TS2" may be a thermocouple, thermistor,
or other temperature sensing device. A plurality of sensors may be
utilized including units extending outside the tip 123 to measure
temperatures at various locations in the proximity of the tip
123.
[0096] As described in described in U.S. patent application Ser.
No. 13/043,694, a memory device 8 in operable connection with the
processor unit 82 can be provided. In some embodiments, the memory
device 8 may be associated with the electrosurgical power
generating source 28. In some embodiments, the memory device 8 may
be implemented as a storage device integrated into the
electrosurgical power generating source 28. In some embodiments,
the memory device 8 may be implemented as an external device
communicatively-coupled to the electrosurgical power generating
source 28.
[0097] In some embodiments, the processor unit 82 is
communicatively-coupled to the flow-control device 50, e.g., via a
transmission line "L5", and may be communicatively-coupled to the
fluid-movement device 60, e.g., via a transmission line "L6". In
some embodiments, the processor unit 82 may be configured to
control one or more operational parameters of the fluid-movement
device 60 to selectively adjust the fluid-flow rate in a fluid-flow
path (e.g., first coolant path 19) of the coolant supply system 11.
In one non-limiting example, the fluid-movement device 60 is
implemented as a multi-speed pump, and the processor unit 82 may be
configured to vary the pump speed to selectively adjust the
fluid-flow rate to attain a desired fluid-flow rate.
[0098] Processor unit 82 may be configured to execute a series of
instructions to control one or more operational parameters of the
flow-control device 50 based on determination of a desired
fluid-flow rate using temperature data received from one or more
temperature sensors, e.g., "TS1", "TS2" through "TSN", where N is
an integer. The temperature data may be transmitted via
transmission lines "L1", "L2" through "LN" or wirelessly
transmitted. One or more flow sensors, e.g., "FS1", "FS2" through
"FSM", where M is an integer, may additionally, or alternatively,
be communicatively-coupled to the processor unit 82, e.g., via
transmission lines "L3", "L4" through "LM". In some embodiments,
signals indicative of the rate of fluid flow into and/or out of the
probe 100 and/or conduit fluidly-coupled the probe 100 received
from one or more flow sensors "FS1", "FS2" through "FSM" may be
used by the processor unit 82 to determine a desired fluid-flow
rate. In such embodiments, flow data may be used by the processor
unit 82 in conjunction with temperature data, or independently of
temperature data, to determine a desired fluid-flow rate. The
desired fluid-flow rate may be selected from a look-up table "TX,Y"
or determined by a computer algorithm stored within the memory
device 8.
[0099] In some embodiments, an analog signal that is proportional
to the temperature detected by a temperature sensor, e.g., a
thermocouple, may be taken as a voltage input that can be compared
to a look-up table "TX,Y" for temperature and fluid-flow rate, and
a computer program and/or logic circuitry associated with the
processor unit 82 may be used to determine the needed duty cycle of
the pulse width modulation (PWM) to control actuation of a valve
(e.g., valve 52) to attain the desired fluid-flow rate. Processor
unit 82 may be configured to execute a series of instructions such
that the flow-control device 50 and the fluid-movement device 60
are cooperatively controlled by the processor unit 82, e.g., based
on determination of a desired fluid-flow rate using temperature
data and/or flow data, to selectively adjust the fluid-flow rate in
a fluid-flow path (e.g., first coolant path 19) of the coolant
supply system 11.
[0100] Feedback control system 14 may be adapted to control the
flow-control device 50 to allow flow (e.g., valve 52 held open) for
longer periods of time as the sensed temperature rises, and shorter
periods of time as the sensed temperature falls. Electrosurgical
system 10 may be adapted to override PWM control of the
flow-control device 50 to hold the valve 52 open upon initial
activation of the antenna assembly 112. For this purpose, a timer
may be utilized to prevent the control device 50 from operating for
a predetermined time interval (e.g., about one minute) after the
antenna assembly 112 has been activated. In some embodiments, the
predetermined time interval to override PWM control of the
flow-control device 50 may be varied depending on setting, e.g.,
time and power settings, provided by the user. In some embodiments,
the electrosurgical power generating source 28 may be adapted to
perform a self-check routine that includes determination that the
flow-control device 50 is open before enabling energy delivery
between the electrosurgical power generating source 28 and the
probe 100.
[0101] The above-described systems including circuitry for
detecting excessive bending of a probe may be used in conjunction
with a variety of electrosurgical devices adapted for treating
tissue. Embodiments may be used in conjunction with electrosurgical
devices adapted to direct energy to tissue, such as ablation
probes, e.g., placed percutaneously or surgically, and/or ablation
devices suitable for use in surface ablation applications.
[0102] The above-described systems including circuitry for
detecting excessive bending of a probe may be suitable for a
variety of uses and applications, including medical procedures,
e.g., tissue ablation, resection, cautery, vascular thrombosis,
treatment of cardiac arrhythmias and dysrhythmias, electrosurgery,
etc.
[0103] It is envisioned that various aspects and features of the
embodiments shown by the various figures and/or described herein
can be combined to form additional embodiments of the
electrosurgical system 10.
[0104] Although embodiments have been described in detail with
reference to the accompanying drawings for the purpose of
illustration and description, it is to be understood that the
inventive processes and apparatus are not to be construed as
limited thereby. It will be apparent to those of ordinary skill in
the art that various modifications to the foregoing embodiments may
be made without departing from the scope of the disclosure.
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