U.S. patent application number 10/400770 was filed with the patent office on 2003-10-16 for rf ablation system and method having automatic temperature control.
Invention is credited to Castellano, Thomas M., Lockwood, Kathryn E., Sherman, Marshall L..
Application Number | 20030195501 10/400770 |
Document ID | / |
Family ID | 24966286 |
Filed Date | 2003-10-16 |
United States Patent
Application |
20030195501 |
Kind Code |
A1 |
Sherman, Marshall L. ; et
al. |
October 16, 2003 |
RF ablation system and method having automatic temperature
control
Abstract
A plurality of electrodes are positioned at the distal end of a
catheter such that the electrodes may be positioned proximal
biological tissue. A select number of the electrodes have a
temperature sensing device associated with them for providing a
temperature signal indicative of the temperature at the interface
between the electrode and the tissue. A generator operates under
the control of a processor to apply power to each of the
electrodes. The power has an associated phase angle and, within a
time duration, a plurality of alternating on periods and off
periods, one set of adjacent on and off periods defining a duty
cycle. The processor is programmed to determine the temperature at
the electrode/tissue interface based on the temperature signals,
compare the temperature to a target temperature and to adjust the
power to the electrode accordingly. Such adjustments may comprise
an increase or decrease in the duty cycle, a setting of the duty
cycle to zero followed by an incremental increase in the duty cycle
or a power interrupt.
Inventors: |
Sherman, Marshall L.;
(Cardiff, CA) ; Lockwood, Kathryn E.; (Temecula,
CA) ; Castellano, Thomas M.; (Temecula, CA) |
Correspondence
Address: |
FULWIDER PATTON LEE & UTECHT, LLP
HOWARD HUGHES CENTER
6060 CENTER DRIVE
TENTH FLOOR
LOS ANGELES
CA
90045
US
|
Family ID: |
24966286 |
Appl. No.: |
10/400770 |
Filed: |
March 27, 2003 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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10400770 |
Mar 27, 2003 |
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09738032 |
Dec 13, 2000 |
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6558378 |
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09738032 |
Dec 13, 2000 |
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09501472 |
Feb 9, 2000 |
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6200314 |
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09501472 |
Feb 9, 2000 |
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09073392 |
May 5, 1998 |
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6059778 |
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Current U.S.
Class: |
606/34 ;
606/41 |
Current CPC
Class: |
A61B 2018/00875
20130101; A61B 2018/00726 20130101; A61B 2018/00654 20130101; A61B
18/1492 20130101; A61B 2018/126 20130101; A61B 2018/00821 20130101;
A61B 18/1206 20130101; A61B 2018/00797 20130101; A61B 2018/00755
20130101; A61B 2018/00702 20130101; A61B 2018/00714 20130101; A61B
2018/1273 20130101; A61B 2018/0075 20130101; A61B 2018/124
20130101; A61B 2018/00738 20130101; A61B 2018/00791 20130101; A61B
2018/00577 20130101; A61B 2018/0016 20130101; A61B 2018/1467
20130101; A61B 2018/00351 20130101 |
Class at
Publication: |
606/34 ;
606/41 |
International
Class: |
A61B 018/14 |
Claims
What is claimed is:
1. A system for delivering energy to biological tissue, said system
comprising: a plurality of electrodes adapted to be positioned at
the biological tissue; at least one temperature sensing device
located on at least one of the electrodes for providing a
temperature signal indicative of the temperature at the interface
between the at least one electrode and the tissue; and a power
control system adapted to: apply power to each of the electrodes
such that a voltage potential is established between at least two
of the electrodes, the power having a duty cycle; in response to
the temperature signal, determine the temperature at the at least
one electrode/tissue interface; compare the interface temperature
to a target temperature; and adjust the duty cycle of the power
provided to the at least one electrode in response to the
comparison.
2. The system of claim 1 wherein the power control system is
adapted to increase the duty cycle of the power to the at least one
electrode when the at least one electrode/tissue interface
temperature is less than the target temperature.
3. The system of claim 1 wherein the power control system is
adapted to decreases the duty cycle of the power to the at least
one electrode when the at least one electrode/tissue interface
temperature is greater than the target temperature.
4. The system of claim 1 wherein the power control system is
adapted to: set the power to the at least one electrode to zero
when the at least one electrode/tissue interface temperature is a
specified first number of degrees greater than the target
temperature; and incrementally increase the power level to the at
least one electrode until the interface temperature is near the
target temperature.
5. The system of claim 4 further comprising: a power interruption
device connected to the power control system; wherein the power
control system is further adapted to control the power interruption
device to interrupt power to the at least one electrode when the at
least one electrode/tissue interface temperature is a specified
second number of degrees greater than the target temperature, the
second number of degrees being greater than the first number of
degrees.
6. The system of claim 1 wherein: the system comprises a plurality
of temperature sensing devices, at least one device associated with
each of the electrodes, each device for providing a temperature
signal to the power control system indicative of the temperature at
the associated electrode; and the power control system provides
separate power to each of the plurality of electrodes with the
power being individually controllable as to duty cycle and the duty
cycle of each separate power is controlled in response to the
temperature signal from the associated electrode.
7. The system of claim 7 wherein the power has an associated phase
angle and the voltage potential is established between the at least
two electrodes by providing power with different phase angles to
the electrodes.
8. A method of delivering energy to biological tissue, said method
comprising: positioning a plurality of electrodes adjacent the
biological tissue, at least one of the electrodes carrying a
temperature sensing device for providing a temperature signal
indicative of the temperature at the interface between the
electrode and the tissue; establishing a voltage potential between
at least two of the electrodes using duty cycled power; determining
the temperature at the at least one electrode/tissue interface in
response to the temperature signal; comparing the at least one
electrode/tissue interface temperature to the target temperature;
and adjusting the duty cycle of the power provided to the at least
one electrode in response to the comparison.
9. The method of claim 8 wherein positioning a plurality of
electrodes comprises positioning a catheter carrying the electrodes
proximal the tissue such that a select number of the plurality of
electrodes are in contact with the tissue.
10. The method of claim 8 further comprising increasing the duty
cycle of the power to the at least one electrode when the at least
one electrode/tissue interface temperature is less than the target
temperature.
11. The method of claim 8 further comprising decreasing the duty
cycle of the power to the at least one electrode when the at least
one electrode/tissue interface temperature is greater than the
target temperature.
12. The method of claim 8 further comprising: setting the power to
the at least one electrode to zero when the at least one
electrode/tissue interface temperature is a specified first number
of degrees greater than the target temperature; and incrementally
increasing the power level to the at least one electrode until the
interface temperature is near the target temperature.
13. The method of claim 12 further comprising interrupting the
power to the at least one electrode when the at least one
electrode/tissue interface temperature is a specified second number
of degrees greater than the target temperature, the second number
of degrees being greater than the first number of degrees.
14. The method of claim 8 wherein each of the electrodes carries a
temperature sensing device and the method further comprises:
providing separate power to each of the plurality of electrodes;
and individually controlling the duty cycle of each separate power
in response to the temperature signal from the electrode.
15. The method of claim 8 wherein the power has an associated phase
angle and establishing the voltage potential between the at least
two electrodes comprises providing power with different phase
angles to the electrodes.
16. A system for delivering energy to biological tissue, said
system comprising: a plurality of electrodes adapted to be
positioned at the biological tissue; at least one temperature
sensing device located on at least one of the electrodes for
providing a temperature signal indicative of the temperature at the
interface between the at least one electrode and the tissue; and a
power control system adapted to: apply power to each of the
electrodes such that at least two of the electrodes are provided
power with different phase angles; in response to the temperature
signal, determine the temperature at the at least one
electrode/tissue interface; compare the interface temperature to a
target temperature; and adjust the power provided to the at least
one electrode in response to the comparison.
17. The system of claim 16 wherein the power control system is
adapted to increase the power to the at least one electrode when
the at least one electrode/tissue interface temperature is less
than the target temperature.
18. The system of claim 16 wherein the power control system is
adapted to decreases the power to the at least one electrode when
the at least one electrode/tissue interface temperature is greater
than the target temperature.
19. The system of claim 16 wherein the power control system is
adapted to: set the power to the at least one electrode to zero
when the at least one electrode/tissue interface temperature is a
specified first number of degrees greater than the target
temperature; and incrementally increase the power to the at least
one electrode until the interface temperature is near the target
temperature.
20. The system of claim 19 further comprising: a power interruption
device connected to the power control system; wherein the power
control system is further adapted to control the power interruption
device to interrupt power to the at least one electrode when the at
least one electrode/tissue interface temperature is a specified
second number of degrees greater than the target temperature, the
second number of degrees being greater than the first number of
degrees.
Description
RELATED APPLICATIONS
[0001] This is a continuation of application Ser. No. 09/738,032,
filed Dec. 13, 2000 which is a continuation-in-part of application
Ser. No. 09/501,472, filed Feb. 9, 2000, now U.S. Pat. No.
6,200,314, which is a division of application Ser. No. 09/073,392,
filed May, 5, 1998, now U.S. Pat. No. 6,059,778.
BACKGROUND OF THE INVENTION
[0002] The invention relates generally to an electrophysiological
("EP") apparatus and method for providing energy to biological
tissue, and more particularly, to a radio frequency ("RF") ablation
apparatus for controlling the flow of current through, and the
temperature of, a biological site so that the volume of ablation
lesions may be controlled.
[0003] The heart beat in a healthy human is controlled by the
sinoatrial node ("S-A node") located in the wall of the right
atrium. The S-A node generates electrical signal potentials that
are transmitted through pathways of conductive heart tissue in the
atrium to the atrioventricular node ("A-V node") which in turn
transmits the electrical signals throughout the ventricle by means
of the His and Purkinje conductive tissues. Improper growth of, or
damage to, the conductive tissue in the heart can interfere with
the passage of regular electrical signals from the S-A and A-V
nodes. Electrical signal irregularities resulting from such
interference can disturb the normal rhythm of the heart and cause
an abnormal rhythmic condition referred to as "cardiac
arrhythmia."
[0004] While there are different treatments for cardiac arrhythmia,
including the application of anti-arrhythmia drugs, in many cases
ablation of the damaged tissue can restore the correct operation of
the heart. Such ablation can be performed by percutaneous ablation,
a procedure in which a catheter is percutaneously introduced into
the patient and directed through an artery to the atrium or
ventricle of the heart to perform single or multiple diagnostic,
therapeutic, and/or surgical procedures. In such case, an ablation
procedure is used to destroy the tissue causing the arrhythmia in
an attempt to remove the electrical signal irregularities or create
a conductive tissue block to restore normal heart beat or at least
an improved heart beat. Successful ablation of the conductive
tissue at the arrhythmia initiation site usually terminates the
arrhythmia or at least moderates the heart rhythm to acceptable
levels. A widely accepted treatment for arrhythmia involves the
application of RF energy to the conductive tissue.
[0005] In the case of atrial fibrillation ("AF"), a procedure
published by Cox et al. and known as the "Maze procedure" involves
continuous atrial incisions to prevent atrial reentry and to allow
sinus impulses to activate the entire myocardium. While this
procedure has been found to be successful, it involves an intensely
invasive approach. It is more desirable to accomplish the same
result as the Maze procedure by use of a less invasive approach,
such as through the use of an appropriate EP catheter system.
[0006] There are two general methods of applying RF energy to
cardiac tissue, unipolar and bipolar. In the unipolar method a
large surface area electrode; e.g., a backplate, is placed on the
chest, back or other external location of the patient to serve as a
return. The backplate completes an electrical circuit with one or
more electrodes that are introduced into the heart, usually via a
catheter, and placed in intimate contact with the aberrant
conductive tissue. In the bipolar method, electrodes introduced
into the heart have different potentials and complete an electrical
circuit between themselves. In the bipolar method, the flux
traveling between the two electrodes of the catheter enters the
tissue to cause ablation.
[0007] During ablation, the electrodes are placed in intimate
contact with the target endocardial tissue. RF energy is applied to
the electrodes to raise the temperature of the target tissue to a
non-viable state. In general, the temperature boundary between
viable and non-viable tissue is approximately 48.degree.
Centigrade. Tissue heated to a temperature above 48.degree. C.
becomes non-viable and defines the ablation volume. The objective
is to elevate the tissue temperature, which is generally at
37.degree. C., fairly uniformly to an ablation temperature above
48.degree. C., while keeping both the temperature at the tissue
surface and the temperature of the electrode below 100.degree.
C.
[0008] A basic configuration of an ablation catheter for applying
RF energy includes a distal tip which is fitted with an electrode
device. The electrode device is the source of an electrical signal
that causes heating of the contacting and neighboring tissue. In
the unipolar method, the electrode device may include a single
electrode used for emitting RF energy. This single electrode acts
as one electrical pole. The other electrical pole is formed by the
backplate in contact with a patient's external body part. A RF
source is applied to the electrode. The RF source is typically in
the 500 kHz region and produces a sinusoidal voltage. When this is
delivered between the distal tip of a standard electrode catheter
and a backplate, it produces a localized RF heating effect and
produces a well defined, deep acute lesion slightly larger than the
tip electrode.
[0009] In some procedures a lesion having a larger surface area
than that produced by a single electrode in a unipolar arrangement
may be required. To this end numerous ablation catheters have been
designed. In one catheter designed to provide a larger surface
ablation area, an electrode device having four peripheral
electrodes which extend from a retracted mode is used. See U.S.
Pat. No. 5,500,011 to Desai. When extended, i.e., fanned out, the
four peripheral electrodes and the central electrode form an
electrode array that covers a larger surface area of the tissue
than a single electrode. When used with a conventional RF power
source, and in conjunction with a backplate, the five electrodes
produce five lesion spots distributed over the area spanned by the
electrode array. The lesions produced are discontinuous in relation
to each other and there are areas between the electrodes that
remain unablated. This device must be manipulated so that when
expanded, all electrodes are in contact with the endocardium. An
"end on" approach is required such that the end of the catheter, on
which all five electrodes are mounted, is in intimate contact with
the target tissue.
[0010] In another catheter an electrode device having a central
electrode and a number of peripheral electrodes which also fan out
from a retracted mode is used. During ablation a backplate is not
used; instead the central electrode functions as the reference
while the peripheral electrodes have multi-phase RF power applied
to them. For example, see U.S. Pat. No. 5,383,917 to Desai et al.
While this technique provides a more continuous lesion covering a
larger surface area of the tissue, the ablation volume is
relatively shallow with a nonuniform depth of the lesion. This
arrangement also requires the same manipulation of the catheter
such that an end-on contact is made by the expanded electrodes, as
discussed above. Lesions having a non-uniform ablation volume are
undesirable as the depth at one part of the lesion may not be
sufficient to stop the irregular signal pathways. Arrhythmia may
reoccur because the irregular signals may pass under such an
ablation volume and the procedure must then be repeated to once
again attempt to obtain an ablation volume having sufficient
depth.
[0011] The mechanical configuration of both of the above-described
techniques comprises an expanding approach. When used for ablation,
an electrode device is typically part of a catheter system.
Accordingly, it is desirable to minimize the diameter of the
electrode device during introduction to and withdrawal from the
patient to lessen trauma to the patient. Therefore, electrode
devices having peripheral expandable electrodes must be configured
so that the peripheral electrodes are expandable to a large size
yet are retractable to as small a size as practical. Such
requirements pose design and manufacturing difficulties due to the
movement of mechanical parts required for proper operation. Further
considerations are the undesirable complexity and increased
manufacturing cost associated with an expandable a catheter.
[0012] Hence, those skilled in the art have recognized a need for a
structurally stable invasive ablation apparatus and method that are
capable of controlling the flow of current through, and temperature
of, a biological site so that lesions with controllable surface and
depth characteristics may be produced and the ablation volume
thereby controlled. The invention fulfills these needs and
others.
SUMMARY OF THE INVENTION
[0013] Briefly, and in general terms, the invention is directed to
an apparatus and a method for controlling the application of energy
to, and the temperature of, a biological site during ablation.
[0014] In one aspect, the invention relates to an apparatus for
delivering energy to biological tissue while maintaining the
temperature of the biological tissue near a target temperature. The
apparatus includes a plurality of electrodes positionable proximal
the biological tissue and at least one temperature sensing device
located on at least one of the electrodes. The temperature sensing
device provides a temperature signal indicative of the temperature
at the interface between the at least one electrode and the tissue.
The apparatus also includes a generator that operates under the
control of a processor to apply power to each of the electrodes.
The power has an associated phase angle and, within a time
duration, a plurality of alternating on periods and off periods,
one set of adjacent on and off periods defining a duty cycle. The
processor is adapted to, during the on period of each duty cycle,
set the phase angles of the power provided to each electrode such
that at least two of the electrodes are provided power with
different phase angles. The processor is further adapted to, in
response to the temperature signal, determine the temperature at
the at least one electrode/tissue interface; compare the interface
temperature to the target temperature and adjust the duty cycle of
the power provided to the at least one electrode in response to the
comparison.
[0015] In a detailed aspect of the invention, the processor is
adapted to increase or decrease the duty cycle of the power to the
at least one electrode when the at least one electrode/tissue
interface temperature is less than or greater than the target
temperature. In another detailed facet the processor is adapted to
set the power to the at least one electrode to zero when the at
least one electrode/tissue interface temperature is a specified
first number of degrees greater than the target temperature to
thereby allow the electrode to cool off. The processor is further
adapted to incrementally increase the power to the electrode until
the interface temperature is near the target temperature. In
another detailed aspect, the apparatus further includes a power
interruption device connected to the processor. The processor is
adapted to control the power interruption device to interrupt power
to the at least one electrode when the at least one
electrode/tissue interface temperature is a specified second number
of degrees greater than the target temperature.
[0016] In another facet, the invention relates to an apparatus for
delivering energy to biological tissue while maintaining the
temperature of the biological tissue near a target temperature. The
apparatus includes a catheter having a plurality of electrodes at
its distal end. The distal end may be positioned so that the
electrodes are located proximal the biological tissue. The
apparatus also includes a plurality of temperature sensing devices.
At least one temperature sensing device is located on a select
number of the electrodes. These devices provide a temperature
signal indicative of the temperature at the interface between the
electrode and the tissue. The apparatus also includes a generator
operating under the control of a processor to apply power to each
of the electrodes. The power has an associated phase angle and,
within a time duration, a plurality of alternating on periods and
off periods. One set of adjacent on and off periods define a duty
cycle. The processor is adapted to, in response to each of the
temperature signals, determine the temperature at the
electrode/tissue interface and regulate the temperature of a
plurality of temperature zones. Each zone includes at least one
combination electrode/temperature sensing device. The temperature
is regulated by controlling the power to at least one electrode in
the zone. The processor is further adapted to regulate the power to
a plurality of phase groups. Each group includes at least one
electrode. The power is regulated by controlling the phase of the
power to each electrode in the group such that during the on
portion of a duty cycle the phase in one group is different then
the phase in another group.
[0017] In another aspect, the invention relates to a method for
delivering energy to biological tissue while maintaining the
temperature of the biological tissue near a target temperature. The
method comprises positioning a plurality of electrodes proximal the
biological tissue. At least one of the electrodes carries a
temperature sensing device for providing a temperature signal
indicative of the temperature at the interface between the
electrode and the tissue. The method also includes providing power
to each of the electrodes. The power has, within a time duration, a
plurality of alternating on periods and off periods, wherein one
set of adjacent on and off periods defines a duty cycle. Also
included in the method is, during the on period of each duty cycle,
providing power with different phase angles to at least two of the
electrodes; determining the temperature at the at least one
electrode/tissue interface in response to the temperature signal;
comparing the at least one electrode/tissue interface temperature
to the target temperature; and adjusting the duty cycle of the
power provided to the at least one electrode in response to the
comparison.
[0018] In another aspect, the invention relates to a method for
delivering energy to biological tissue while maintaining the
temperature of the biological tissue near a target temperature. The
method comprises positioning a catheter having a plurality of
electrodes at its distal end so that the electrodes are located
proximal the biological tissue. A select number of the electrodes
carry at least one temperature sensing device. The device provides
a temperature signal indicative of the temperature at the interface
between the electrode and the tissue. The method also includes
providing power having an associated phase and, within a time
duration, a plurality of alternating on periods and off periods,
one set of adjacent on and off periods defining a duty cycle. The
method further includes, in response to the temperature signals,
determining the temperature at the electrode/tissue interface;
individually regulating the temperature of a plurality of
temperature zones, wherein each zone comprises at least one
combination electrode/temperature sensing device. The temperature
is regulated by controlling the power to at least one electrode in
the zone. The method further includes regulating the power to a
plurality of phase groups, wherein each group comprises at least
one electrode. The power is regulated by controlling the phase of
the power to each electrode in the group such that during the on
portion of a duty cycle the phase in one group is different then
the phase in another group.
[0019] These and other aspects and advantages of the present
invention will become apparent from the following more detailed
description, when taken in conjunction with the accompanying
drawings which illustrate, by way of example, the preferred
embodiments of the invention.
BRIEF DESCRIPTION OF THE DRAWINGS
[0020] FIG. 1 is a schematic diagram of an ablation apparatus
including a power control system, electrode device and
backplate;
[0021] FIGS. 2-1 and 2-2 form a block diagram presenting more
detail of a power control system in accordance with aspects of the
invention, showing phase angle control, duty cycle control, and
impedance and temperature monitoring;
[0022] FIG. 3 is a diagram of a multi-channel ablation apparatus in
accordance with aspects of the invention wherein a single
microprocessor controls the phase angle and duty cycle of each
channel individually;
[0023] FIG. 4 depicts a first power waveform having a first phase
angle and alternating instances of peak power and very low
power;
[0024] FIG. 5 depicts a second power waveform having a second phase
angle different from the first phase angle and alternating
instances of peak power and very low power;
[0025] FIG. 6 presents a time frame (TF) diagram showing a
fifty-percent duty cycle;
[0026] FIG. 7A depicts the phase relationship and voltage potential
between the first and second power waveforms having first and
second phase angles respectively, as a function of time;
[0027] FIG. 7B depicts the phase relationship and voltage potential
between the first and second power waveforms having second and
first phase angles respectively, as a function of time;
[0028] FIGS. 8A, 8B, 8C, 8D, and 8E are schematic diagrams of an
embodiment of a power control system in accordance with aspects of
the invention with FIG. 8A showing how FIGS. 8B, 8C, 8D and 8E are
related;
[0029] FIG. 9A is a three dimensional representation of an ablation
apparatus having a linear array of band electrodes in contact with
a biological site with a backplate at the opposite side of the
biological site, in which the phase angle difference between
adjacent electrodes of the linear array is zero degrees;
[0030] FIGS. 9B through 9D depict, along the x, y, and z axes
shown, the depth of the lesions formed by the ablation apparatus of
FIG. 9A showing that the apparatus acts as a unipolar device with
multiple electrodes and the resulting lesions are
discontinuous;
[0031] FIG. 10A is a three dimensional representation of an
ablation apparatus having a linear array of band electrodes in
contact with a biological site with a backplate at the opposite
side of the biological site, in which the phase angle difference
between adjacent electrodes is 180 degrees;
[0032] FIGS. 10B through 10D depict, along the x, y, and z axes
shown, the continuity and depth of a lesion formed by the ablation
apparatus of FIG. 10A showing that the apparatus acts as a bipolar
device with no significant amount of current flowing to the
backplate;
[0033] FIG. 11A is a three dimensional representation of an
ablation apparatus having a linear array of band electrodes in
contact with a biological site with a backplate at the opposite
side of the biological site, in which the phase difference between
adjacent electrodes is approximately 90 degrees; and
[0034] FIGS. 11B through 11D depict, along the x, y, and z axes
shown, the continuity and depth of a lesion formed by the ablation
apparatus of FIG. 11A showing the greater depth of lesion resulting
from the phase angle difference.
[0035] FIG. 12 presents a block diagram of the current flow among
electrodes and the backplate through the biological site for
adjacent electrodes having different phase angles;
[0036] FIG. 13 presents the same block diagram as FIG. 12 with the
phase angles between adjacent electrodes reversed; and
[0037] FIGS. 14A through 14D present, along the x, y, and z axes
shown, the increased continuity, depth, and uniformity of a lesion
formed by the alternating phase apparatus and method shown in
previous figures.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
[0038] Turning now to the drawings, in which like reference
numerals are used to designate like or corresponding elements among
the several figures, in FIG. 1 there is shown an ablation apparatus
10 in accordance with aspects of the present invention. The
apparatus 10 includes a power control system 12 that provides power
or drive 14 to an electrode device 16. The power control system 12
comprises a power generator 18 that may have any number of output
channels through which it provides the power 14. The operation of
the power generator 18 is controlled by a controller 20 which
outputs control signals 21 to the power generator 18. The
controller 20 monitors the power 14 provided by the power generator
18. In addition, the controller 20 also receives temperature
signals 22 from the electrode device 16. Based on the power 14 and
temperature signals 22 the controller 20 adjusts the operation of
the power generator 18. A backplate 24 is located proximal to the
biological site 26 opposite the site from the electrode device 16,
and is connected by a backplate wire 28 to the power generator 18.
The backplate 24 is set at the reference level to the power
provided to the electrodes, as discussed in detail below.
[0039] The electrode device 16 is typically part of a steerable EP
catheter 30 capable of being percutaneously introduced into a
biological site 26, e.g., the atrium or ventricle of the heart. The
electrode device 16 is shown in schematic form with the components
drawn to more clearly illustrate the relationship between the
components and the relationship between the components and the
power control system 12. In this embodiment, the catheter 30
comprises a distal segment 34 and a handle 31 located outside the
patient. A preferred embodiment of the electrode device 16 includes
twelve band electrodes 32 arranged in a substantially linear array
along the distal segment 34 of the catheter 30. The electrode
device 16 may include a tip electrode 36. (For clarity of
illustration, only four band electrodes 32 are shown in the figures
although as stated, a preferred embodiment may include many more.)
The band electrodes 32 are arranged so that there is space 38
between adjacent electrodes. In one configuration of the electrode
device 16, the width of the band electrodes 32 is 3 mm and the
space 38 between the electrodes is 4 mm. The total length of the
electrode device 16, as such, is approximately 8 cm.
[0040] The arrangement of the band electrodes 32 is not limited to
a linear array and may take the form of other patterns. A
substantially linear array is preferred for certain therapeutic
procedures, such as treatment of atrial fibrillation, in which
linear lesions of typically 4 to 8 cm in length are desired. A
linear array is more easily carried by the catheter 30 and also
lessens the size of the catheter.
[0041] The band electrodes 32 are formed of a material having a
significantly higher thermal conductivity than that of the
biological tissue 26. Possible materials include silver, copper,
gold, chromium, aluminum, molybdenum, tungsten, nickel, platinum,
and platinum/10% iridium. Because of the difference in thermal
conductivity between the electrodes 32 and the tissue 26, the
electrodes 32 cool off more rapidly in the flowing fluids at the
biological site. The power supplied to the electrodes 32 may be
adjusted during ablation to allow for the cooling of the electrodes
while at the same time allowing for the temperature of the tissue
to build up so that ablation results. The electrodes 32 are sized
so that the surface area available for contact with fluid in the
heart, e.g., blood, is sufficient to allow for efficient heat
dissipation from the electrodes to the surrounding blood. In a
preferred embodiment, the electrodes 32 are 7 French (2.3 mm in
diameter) with a length of 3 mm.
[0042] The thickness of the band electrodes 32 also affects the
ability of the electrode to draw thermal energy away from the
tissue it contacts. In the present embodiment, the electrodes 32
are kept substantially thin so that the electrodes effectively draw
energy away from the tissue without having to unduly increase the
outer diameter of the electrode. In a preferred embodiment of the
invention, the thickness of the band electrodes is 0.05 to 0.13 mm
(0.002 to 0.005 inches).
[0043] Associated with the electrode device 16 are temperature
sensors 40 for monitoring the temperature of the electrode device
16 at various points along its length. In one embodiment, each band
electrode 32 has a temperature sensor 40 mounted to it. Each
temperature sensor 40 provides a temperature signal 22 to the
controller 20 which is indicative of the temperature of the
respective band electrode 32 at that sensor. In another embodiment
of the electrode device 16 a temperature sensor 40 is mounted on
every other band electrode 32. Thus for a catheter having twelve
electrodes, there are temperature sensors on six electrodes. In yet
another embodiment of the electrode device 16 every other electrode
has two temperature sensors 40. In FIG. 1, which shows an
embodiment having one temperature sensor for each electrode, there
is shown a single power lead 15 for each electrode 32 to provide
power to each electrode for ablation purposes and two temperature
leads 23 for each temperature sensor 40 to establish the
thermocouple effect.
[0044] In another approach, the drive wire may comprise one of the
thermocouple wires or may comprise a common wire for a plurality of
thermocouples mounted on the same electrode. The inventors hereby
incorporates by reference U.S. Pat. Nos. 6,049,737 and 6,045,550
both of which are assigned to the assignee of the present
invention.
[0045] Turning now to FIGS. 2-1 and 2-2, a block diagram of an
ablation apparatus 10 and method in accordance with aspects of the
invention is presented. In FIGS. 2-1 and 2-2, a single channel of
the power control system 12 is depicted. This channel controls the
application of power to a single electrode 32. As will be discussed
in relation to other figures, a channel may control a plurality or
group of electrodes. In FIG. 2-1, a microprocessor 42, which is
part of the controller 20 (FIG. 1), provides a duty cycle control
signal 44 to a duty cycle generator ("DCG") 45. In this case, the
duty cycle generator 45 receives the control signal 44 by an 8-bit
latch 46. The latch 46 provides an 8-bit signal 47 to a duty cycle
comparator 48. The comparator 48 compares the 8-bit signal 47 to a
count from an 8-bit duty cycle counter 50 and if the count is the
same, provides a duty cycle off signal 49 to the duty cycle gate
52. The gate 52 is connected to a frequency source ("FS") 54, such
as an oscillator that produces 500 kHz. When the gate 52 receives
the duty cycle off signal 49 from the comparator 48, it stops its
output of the frequency source signal through the gate and no
output exists.
[0046] At a frequency of 500 kHz, an 8-bit control has a period or
time frame of 0.5 msec. At a fifty-percent duty cycle, the
electrode is in the off period only 0.25 msec. To allow for greater
cooling of the electrode, the period or time frame 78 (FIG. 6) is
lengthened by use of a prescalar 56 interposed between the
frequency source 54 and the counter 50. In one embodiment, the
prescalar 56 lengthens the period to 4 msec thus allowing for a 2
msec off period during a fifty-percent duty cycle. This results in
a sufficient cooling time for the very thin band electrodes
discussed above. Other lengths of the period may be used depending
on the circumstances. It has been found that a ten percent duty
cycle is particularly effective in ablating heart tissue. The
combination of the application of high peak power, a ten percent
duty cycle, the use of high thermal conductivity material in the
band electrodes, and fluids flowing past the band electrodes which
have a cooling effect on the electrodes result in a much more
effective application of power to the tissue. Ablation occurs much
more rapidly.
[0047] A terminal count detector 58 detects the last count of the
period and sends a terminal count signal 59 to the gate 52 which
resets the gate for continued output of the frequency source
signal. This then begins the on period of the duty cycle and the
counter 50 begins its count again. In one preferred embodiment, the
duty cycle is set at fifty percent and the 8-bit latch is
accordingly set to 128. In another embodiment, the duty cycle is
set at ten percent.
[0048] A programmable logic array ("PLA") 60 receives phase control
signals 61 from the microprocessor 42 and controls the phase of the
frequency source 54 accordingly. In one embodiment, the PLA 60
receives the terminal count signal 59 from the terminal count
detector 58 and only permits phase changes after receiving that
terminal count signal.
[0049] The output signal from the gate 52 during the on period of
the duty cycle is provided to a binary power amplifier ("BPA") 62
that increases the signal to a higher level, in this case, 24
volts. The amplified signals are then filtered with a band pass
filter ("BPF") 64 to convert the somewhat square wave to a sine
wave. The band pass filter 64 in one embodiment is centered at 500
kHz. The filtered signal is then provided to an isolated output
transformer ("IOT") 66 that amplifies the signal to a much higher
level, for example 350 volts peak-to-peak. This signal is then sent
to a relay interconnect ("RI") 67 before it is provided as a power
output signal OUTn 14 to an electrode 32 at the biological site to
cause ablation.
[0050] The power output signal 14 from the isolated output
transformer 66 is monitored in one embodiment to determine the
impedance at the electrode 32. In the embodiment shown in FIGS. 2-1
and 2-2, a voltage and current monitor ("VCM")68 is used. The
monitor signal 69 is converted to digital form by an A-to-D
converter ("ADC") 70 and provided to the microprocessor 42. As
previously mentioned, some or all of the electrodes 32 may include
a temperature sensor 40 (FIG. 1) that provides temperature signals
22 (FIG. 2-2) which are used to determine the temperature at the
electrode 32. In one embodiment of the invention, the power 14, in
conjunction with the temperature signals 22, are used to determine
the temperature at the electrode 32. Both the temperature signals
22 and the power 14 pass through a temperature filter ("FL") 73
before being sent to the microprocessor 42. In the alternative, the
temperature filter 73 is contained in a printed circuit board
separate from the controller 20 and contains its own processor. In
either case, the filter 73 filters out any RF noise present in the
power 14 so that the signal may be used for temperature monitoring
purposes. In another embodiment, the microprocessor monitors the
power 14 and temperature signals 22 only during the off periods of
the power 14 duty cycle. Accordingly, negligible RF noise is
present in the power line and filtration is not necessary. In
either embodiment, the microprocessor 42 may alter the duty cycle
of the power 14 in response to either or both of the impedance or
temperature signals.
[0051] In a manual arrangement, the temperature sensed and/or the
determined impedance may be displayed to an operator. The operator
in response may then manually control the duty cycle or other power
parameters such as by rotating a knob mounted on a front panel of
an instrument. In the case of a multiple channel instrument and
catheter, as discussed below, multiple knobs may be provided in
this manual arrangement for control over each channel.
[0052] Referring now to FIG. 3, a multiple channel ablation
apparatus is shown. Although only three complete channels are
shown, the apparatus comprises many more as indicated by the
successive dots. Those channels are not shown in FIG. 3 to preserve
clarity of illustration. By providing different voltage levels
between two electrodes 32 in an array, current flows between those
electrodes in a bipolar electrode approach. By setting the
backplate 24 (FIG. 1) at a voltage level different from at least
one of those electrodes 32, current flows between that electrode
and the backplate. By controlling the voltage levels among the
three (two electrodes and backplate), the current flow through the
biological site 26 can be more precisely controlled. One technique
for setting different voltage levels between the electrodes 32 is
to maintain a phase difference between them in an AC approach. By
setting the backplate 24 at the reference level, current flows
between the electrodes 32 and the backplate.
[0053] The single microprocessor 42, which again is part of the
controller 20 (FIG. 1), controls the duty cycle and the phase of
each channel individually in this embodiment. Each channel shown
comprises the same elements and each channel produces its own power
output signal 14 (OUT1, OUT2, through OUTn where "n" is the total
number of channels) on respective electrode leads (LEAD 1, LEAD 2,
through LEAD n where "n" is the total number of leads) to the
electrodes 32. This multi-channel approach permits more individual
control over each electrode. For example, the duty cycle of the
power applied to each electrode can be individually controlled. One
electrode may have a ten percent duty cycle while another has a
thirty percent duty cycle.
[0054] Referring now to the first and second output signals OUT1
and OUT2 of FIG. 3, the signals, as shown in FIGS. 4, 5, and 6,
have alternating instances of peak power i.e., "on" periods 74, and
very low power 76, i.e., "off" periods. Typically, the output power
14 is a 500 kHz sine wave. In FIGS. 4 and 5, the number of cycles
of the sine wave contained within one on period 74 has been
substantially reduced in the drawing to emphasize the phase
difference between the first and second output signals OUT1, OUT2.
Preferably, the voltage of each power signal 14 during an off
period 76 is substantially zero and during an on period 74 is
approximately 350 volts peak-to-peak.
[0055] The power OUT1 and OUT2 also have a variable duty cycle for
controlling the length of the on period 74 and the off-period 76
within a time frame 78 (see FIG. 6). The duty cycle is the ratio of
the length of the on period 74 to the length of the entire time
frame 78. The effective power is the peak power times the duty
cycle. Thus, a signal having a peak power of 100 watts and a 50%
duty cycle has an effective power of 50 watts.
[0056] As shown in FIGS. 4, 5, and 6, the two power signals OUT1,
OUT2 are phased differently from each other. As discussed above,
the phase angle of each power signal is set and controlled by the
processor 42 and PLA 60. Each power signal OUT1 and OUT2 has a
respective phase angle and those phase angles differ between the
two of them. The phase angle difference between the power OUT1 and
OUT2 produces a voltage potential between the band electrodes 32
(FIG. 1) that receive the power. This voltage potential, in turn,
induces current flow between the band electrodes 32. The phase
angle relationship of the power and the voltage potential produced
as a function of time is shown in FIGS. 7A and 7B. The potential
between electrodes V.sub.e-e is defined by: 1 V e - e = 2 V sin ( 2
) sin ( 2 f t ) (Eq.1)
[0057] where: .DELTA..PHI.=phase angle difference between
electrodes
[0058] V=voltage amplitude of power
[0059] f=frequency in hertz
[0060] t=time
[0061] FIG. 7A shows first and second power OUT1 and OUT2 provided
to first and second electrodes respectively having a phase angle
difference .DELTA..PHI. with OUT1 leading OUT2 by 132 degrees. FIG.
7B shows the same power OUT1 and OUT2 but with the phase angles
reversed where OUT2 is now leading OUT 1 by 132 degrees.
[0062] With reference now to FIGS. 8A through 8E, schematic
diagrams of an embodiment of the ablation apparatus 10 of FIGS. 2-1
and 2-2 are presented in FIGS. 8B through 8E while FIG. 8A shows
how FIGS. 8B through 8E should be oriented in relation to each
other. The frequency source 54 provides a signal 80, typically at
500 kHz with a phase angle controlled by the microprocessor 42
through the PLA 60, to the duty cycle generator 45. The duty cycle
generator 45 modulates the frequency source signal 80 to produce
the selected duty cycle in accordance with the duty cycle control
signal 44 as previously described. The duty cycle generator 45
outputs two signals 82 and 84 to the binary power amplifier 62. A
dual MOSFET driver U2 receives the signals, converts their 5V level
to a 12V level, and sends each to a transformer T2 which transforms
the signals into 24 V peak-to-peak power.
[0063] The 24V power is then sent to a multi-state driver 86 which
includes a configuration of FETs Q2, Q3, Q4, and Q5. During a
conducting state of the driver 86, which is typically the on period
74 of the power, these FETs Q2 through Q5 conduct and forward the
power to a bandpass filter 64 comprising a series LC network.
During a high-impedance state of the driver 86, which is typically
during the off period 76 of the power, the FETs Q2 through Q5 are
nonconducting and no power is sent to the bandpass filter 64.
Instead the FETs Q2 through Q5 present a high impedance load to any
signals received through the electrode 32. Typically the load
impedance on the FETs Q2 through Q5 presented by the circuit
following the FETs, the electrode, and the tissue is approximately
150 .OMEGA. but transformed through the output transformer T3, it
presents a load impedance to the FETs Q2-Q5 of approximately 0.5 to
1 .OMEGA.. In the off state, the FETs present an impedance of
approximately 250 .OMEGA. which is large in comparison to the
transformed load impedance of approximately 0.5 to 1 .OMEGA..
Therefore, very little power flows when the FETs are in the off
state.
[0064] The bandpass filter 64 operates to shape the output signal
provided by the binary amplifier 62 from a square wave to a
sinusoidal wave. The filtered signal 85 then passes to the isolated
output section 66 where it is step-up transformed to 350 volt
peak-to-peak sinusoidal power at T3. The power is then split into
two identical power signals OUT1A, OUT1B and provided to two or
more respective band electrodes 32 on the output lines LEAD1A,
LEAD1B.
[0065] The isolated output section 66 also includes relays 88 that
may be individually opened to remove the power signals OUT1A, OUT1B
from the electrode leads LEAD 1A, LEAD 1B when an alert condition
is detected, such as high temperature or high impedance at the
respective electrode 32. As previously mentioned these conditions
are determined by the microprocessor 42 which receives signals
indicative of the temperature and impedance at each of the band
electrodes 32.
[0066] The power from the isolated output section 66 is monitored
and representative signals are supplied to an RF voltage and
current monitor 68 where in this case, the voltage and current of
each output signal are measured to determine the impedance of the
particular channel. The measured signals are sent to an A-to-D
converter 70 (FIG. 2-2) before being sent to the microprocessor 42
for impedance monitoring. If the impedance is above a threshold
level indicative of blood clotting or boiling, the microprocessor
42 sends a signal to the duty cycle generator 45 to reduce or
discontinue the duty cycle of the power OUT1A, OUT1B and thus lower
the effective power delivered to the band electrodes 32.
[0067] Similarly, the temperature at the electrodes 32 is
determined by monitoring the power 14 and temperature signals 22
and measuring the voltage difference between the signals. As
previously mentioned, in one embodiment of the invention, these
signals pass through a filter 73 (FIG. 2-2) before being sent to
the microprocessor 42. The voltage value is converted to a
temperature and if the temperature is above a threshold level the
duty cycle of the power 14 is reduced. In the case where a single
lead is used to provide a signal which is used to determine the
temperature as well as provide power to the electrode 32, the
signal from the lead is received on temperature leads 87, 89
connected at the output side of the relays 88.
[0068] As shown in FIG. 3, the duty cycle of each electrode 32 may
be individually controlled by the microprocessor 42. As previously
mentioned, based on the temperature at an electrode 32 and the
current and voltage of the output signal provided to an electrode,
the duty cycle of the output signal may be adjusted. For example,
one electrode 32 may have a temperature requiring a duty cycle of
ten percent, while another electrode may have a temperature which
allows for a fifty percent duty cycle. In an embodiment in which
every other electrode 32 has a temperature sensor 40, the
electrodes are grouped in pairs with each electrode in the pair
having the same duty cycle.
[0069] In operation, as depicted in FIGS. 9A through 11D, the
electrode device 16 and the backplate 24 are positioned proximal
the biological site 26 undergoing ablation such that the biological
site is interposed between the electrode device and the backplate.
The band electrodes 32 (only one of which is indicated by a numeral
32 for clarity of illustration) of the electrode device 16 each
receives power OUT1, OUT2, OUT3, OUT4 having a phase angle on LEAD
1 through LEAD 4. In one embodiment, every other electrode 32
receives the same phase angle. Therefore, the phase angle of
electrode A equals the phase angle of electrode C and the phase
angle of electrode B equals the phase angle of electrode D. The
advantages of this arrangement are described below. In a preferred
embodiment, the electrodes 32 are formed into a linear array as
shown. In addition, a thermocouple temperature sensor 40 is located
at each of the electrodes A, B, C, and D and uses the electrode
power lead LEADS 1 through 4 as one of the sensor leads. The
sensors 40 provide temperature sensor signals 22 for receipt by the
power control system 12.
[0070] In another embodiment, alternate electrodes 32 may be
grouped together and each may receive the same power having the
same phase angle and duty cycle. Another group or groups of
electrodes 32 may be interspaced with the first group such that the
electrodes of one group alternate with the electrodes of the other
group or groups. Each electrode 32 in a particular group of
electrodes has the same phase angle and duty cycle. For example,
electrodes A and C may be connected to the same power while
interspaced electrodes B and D may be connected to a different
power output signal.
[0071] The use of individual power signals also provides the
ability to disable any combination of electrodes 32 and thereby
effectively change the length of the electrode device 16. For
example, in one configuration of the present invention an electrode
device 16 with twelve electrodes 32 receives twelve power signals
from a twelve channel power control system 12. The electrodes 32
are 3 mm in length and are 4 mm apart. Accordingly, by disabling
various electrodes, a virtual electrode of any length from 3 mm to
8 cm may be produced by the electrode device 16. In either
arrangement the backplate 24 is maintained at the reference voltage
level in regard to the voltage level of the power OUT1 through
OUTn.
[0072] As previously described, by varying the phase angles between
the power OUT1, OUT2 supplied to each electrode 32, a phase angle
difference is established between adjacent band electrodes. This
phase angle difference may be adjusted to control the voltage
potential between adjacent band electrodes 32 and thus to control
the flow of current through the biological site 26. The flow of
current Ie-e between adjacent band electrodes 32 is defined by: 2 I
e - e = 2 V sin ( 2 ) sin ( 2 f t ) Z e - e e (Eq.2)
[0073] where: .DELTA..OMEGA.=phase angle difference between
electrodes
[0074] V=voltage amplitude of power
[0075] Z.sub.e-e=impedance between electrodes
[0076] f=frequency in hertz
[0077] t=time
[0078] In addition to the current flow between the band electrodes
32 there is current flow between the band electrodes and the
backplate 24. When the backplate 24 is set at the reference level,
this current flow I.sub.e-b is defined by: 3 I e - b = V sin ( 2 f
t ) Z e - b (Eq.3)
[0079] where: .DELTA..OMEGA.=phase angle difference between
electrodes
[0080] V=voltage amplitude of power
[0081] Z.sub.e-b=impedance between electrode and backplate
[0082] f=frequency in hertz
[0083] t=time
[0084] Assuming Z.sub.e-b and Z.sub.e-e are equal, the ratio of the
current flowing between the band electrodes 32 I.sub.e-e to the
current flowing between the band electrodes 32 and the backplate 24
I.sub.e-b is defined by: 4 I e - e I e - b = 2 sin ( 2 ) (Eq.4)
[0085] where: .DELTA..OMEGA.=phase angle difference between
electrodes
[0086] FIGS. 9A through 11D illustrate various current flow
patterns within a biological site. The depths and widths of the
lesions depicted in FIGS. 9 through 11 are not necessarily to scale
or in scalar proportion to each other but are provided for clarity
in discerning the differences between the various power application
techniques. When the phase difference between adjacent electrodes
32 is zero degrees, no current flows between the electrodes in
accordance with Eq. 2 above, and the apparatus operates in a
unipolar fashion with the current flowing to the backplate 24 as
shown in FIGS. 9A through 9D. Substantially all current flows from
the band electrodes 32 to the backplate 24 forming a series of
relatively deep, acute lesions 90 along the length of the electrode
device 16. As seen in the top view of FIG. 9B and the side view of
FIG. 9D, the lesions are discrete. The lesions 90 are discontinuous
in regard to each other.
[0087] When the phase difference between adjacent electrodes 32 is
180 degrees the apparatus operates in both a unipolar and bipolar
fashion and the current flow pattern is as shown in FIG. 10A. With
this phase difference, approximately twice as much current flows
between adjacent band electrodes 32 than flows from the band
electrodes to the backplate 24. The resulting lesion 92 is shallow
but is continuous along the length of the electrode device 16. The
continuity and shallow depth of the lesion 92 are illustrated in
FIGS. 10B through 10D. Nevertheless, the lesion depth is still
greater than that created by prior bipolar ablation methods
alone.
[0088] When the phase difference between adjacent electrodes 32 is
set within the range of a value greater than zero to less than 180
degrees, the current flow varies from a deep, discontinuous
unipolar pattern to a more continuous, shallow bipolar pattern. For
example, when the phase difference between adjacent electrodes 32
is around 90 degrees, the current flows as shown in FIG. 11A. With
this phase difference, current flows between adjacent band
electrodes 32 as well as between the band electrodes and the
backplate 24. Accordingly, a lesion which is both deep and
continuous along the length of the electrode device 16 is produced.
The continuity and depth of the lesion 94 is illustrated in FIGS.
11B through 11D. In one embodiment of FIG. 1A, adjacent electrodes
alternated in phase but were provided with power in groups.
Electrodes A and C were provided with power at a first phase angle
and electrodes B and D were provided with power at a second phase
angle, different from the first.
[0089] Thus, in accordance with the present invention the phase
angle of the power may be adjusted in order to produce a lesion
having different depth and continuity characteristics. In selecting
the phase angle difference necessary to produce a continuous lesion
having the greatest possible depth, other elements of the electrode
device 16 are considered. For example, the width of the band
electrodes 32 and the spacing between the electrodes are factors in
selecting an optimum phase angle. In a preferred embodiment of the
present invention, as pointed out above, the width of the band
electrodes is 3 mm, the spacing between the electrodes is 4 mm and
the electrodes receive power which establish a phase difference of
132 degrees between adjacent electrodes. With this configuration a
long continuous lesion having a length of between approximately 3
mm and 8 cm and a depth of 5 mm or greater was produced depending
on the number of electrodes energized, the duty cycle employed, and
the duration of power application.
[0090] In another embodiment of the invention, energy is applied to
the biological tissue 26 during the on period of the duty cycle in
an alternating unipolar-bipolar manner. During the unipolar mode
segment a voltage potential is established between the electrodes
32 and the backplate 24. Thus current flows through the tissue 26
between the electrodes 32 and the backplate 24.
[0091] During the bipolar mode segment a voltage potential is
established between at least two of the electrodes 32 rather than
between the electrodes and the backplate 24. Thus current flows
through the tissue 26 between the electrodes 32. While operating in
this mode the voltage difference between the electrodes 32 may be
established by providing power with different phase angles to the
electrodes as previously mentioned. Alternatively, some of the
electrodes 32 may be connected to a reference potential while
others are maintained at a different voltage level.
[0092] By adjusting the duration of the unipolar and bipolar mode
segments within the on period of the duty cycle, the continuity and
depth of the lesion produced may be controlled. For example,
operating in the unipolar mode for one-fourth of the on period and
in the bipolar mode for three-fourths of the on period produces a
lesion having a continuity and depth similar to the lesion 94
illustrated in FIGS. 11B through 11D.
[0093] Referring to FIGS. 8B through and 8E, the following devices
are shown:
1 Device Part No. Manufacturer U1 GAL6002B Lattice U2 SN75372
numerous Q1 1RFZ34N numerous Q2, Q3, Q4, Q5 1RFZ44N numerous Q7,
Q8, Q9 MPF6601 numerous R3, R5 1 .OMEGA. numerous T1, T4 CMI-4810
Corona Magnetics, Inc. T2 GFS97-0131-1 GFS Manufacturing T5
CMI-4809 Corona Magnetics, Inc.
[0094] The transformer denoted by "T3" is a 1:12 turns ratio,
single turn primary, step up transformer wound on a TDK core
PC50EER23Z.
[0095] FIG. 12 presents a block diagram of the current flow among
electrodes 32 and the backplate 24 through the biological site 26
for adjacent electrodes having different phase angles where the
phase angles of the A and C electrodes lead the phase angles of the
B and D electrodes. It has been noted that with the approach shown
in FIG. 12, the vector sum of the currents flowing through the site
26 is such that more current flows at one or more electrodes than
at others. This is shown figuratively with shorter arrows leading
to the backplate from the B and D electrodes. Although the ablation
volume is greater than in the prior techniques, the ablation volume
appears irregular or nonuniform as shown in FIG. 11D. It is
desirable to have a more uniform ablation volume, especially as to
depth, so that irregular electrical signals do not pass under the
ablation volume at a point having less depth and require a repeat
of the ablation procedure.
[0096] FIG. 13 presents the same block diagram as FIG. 12 with the
phase angles between adjacent electrodes reversed. In FIG. 13, the
phase angles of the power at the B and D electrodes 32 now lead the
phase angles of the power at the A and C electrodes 32. The change
in current flow due to this opposite phasing is represented
figuratively with shorter arrows now at the A and C electrodes thus
balancing the current flow pattern of FIG. 12. It has been found
that by alternating the phase angles such as shown in FIGS. 12 and
13, a much more uniform current flow and much more uniform ablation
volume result. A cumulative effect of the current flow causes the
tissue between all the band electrodes 32 and the backplate 24 to
become ablated, depth-wise through the biological site 26, at a
substantially even rate and thus a lesion having substantially
uniform depth is produced. This is shown in FIGS. 14A through 14D
where an ablation volume 96 is shown, which has much greater
uniformity in shape. In particular, the ablation lesion 96 has a
uniform depth and gives rise to a high level of confidence that the
ablation volume created with the ablation apparatus in accordance
with the invention will successfully destroy the tissue causing the
arrhythmia.
[0097] In one embodiment, the phase between the electrodes was
alternated as shown in FIGS. 12 and 13 only during the off period
of the duty cycle. That is, and with reference to FIG. 6, during
the entire on period 74 of the duty cycle of one time frame 78, the
phase angles of the power at the A and C electrodes 32 led the
phase angles of the power at the B and D electrodes 32 by 132
degrees. During the following off period 76 of the same time frame
78, the phase angles of the power to be supplied was changed to be
opposite those phase angles used during the on period 74, in
preparation for the next on period. Then at the next on period 74,
the phase angles of the power provided to electrodes B and D led
the phase angles of the power provided to the A and C electrodes by
132 degrees during that entire on period. During the immediately
subsequent off period, the phase angles were again changed so that
electrodes A and C would lead electrodes B and D.
[0098] During an ablation procedure, the processor 42 monitors the
temperatures at the electrodes/tissue interface and automatically
makes power adjustments in view of these temperatures. As
previously mentioned, in order to effectively ablate tissue it is
desirable to uniformly elevate the tissue temperature to a target
ablation temperature. For biological tissue this target temperature
may range from 50.degree. C. to 65.degree. C.
[0099] In one configuration of the system, the temperature of each
electrode/tissue interface is monitored and the power applied to
each electrode 32 is individually adjusted to maintain the
electrode/tissue interface temperature at or near the target
temperature. An interface temperature within 5.degree. C. degrees
of the target temperature is considered to be "near" the target
temperature. Adjustments to the power are made by changing the duty
cycle of the power being applied to the electrode 32. When the
electrode/tissue interface temperature is less than the target
temperature, the duty cycle is increased. Conversely, when the
interface temperature is greater than the target temperature, the
duty cycle is decreased.
[0100] Under certain electrode/tissue interface temperature
conditions, the processor 42 may institute a "soft cutoff." During
a soft cutoff the processor temporarily sets the power to an
electrode 32 to zero by setting the duty cycle of the power such
that there is no on portion of the duty cycle. During this
continuous off period, the electrode/tissue interface is able to
cool off to a temperature less than the temperature that caused the
cutoff and usually to a temperature less than the target
temperature. Once the interface cools off, the processor 42
incrementally increases the power to the electrode 32 until the
interface temperature settles to a temperature near the target
temperature. The incremental increase in power may be achieved by
programming the processor, using well known proportional integral
derivative (PID) algorithms, to increase the duty cycle in either a
step like or smooth, continuous manner. Conditions which
necessitate a soft cutoff may be programmed into the processor 42.
Such condition may include an interface temperature that is greater
than the target temperature by a first specified number of degrees.
For example, if the target temperature is 65.degree. C. and the
measured interface temperature is at least 5 degrees greater than
65.degree. C., then the electrode may be subject to a soft
cutoff.
[0101] Under more severe electrode/tissue interface temperature
conditions, the processor 42 may institute a "hard cutoff." During
a hard cutoff, power to an electrode 32 may be interrupted by
opening the relay 88 (FIG. 80) associated with the power output
providing the power to the electrode 32. Conditions which
necessitate a hard cutoff may be programmed into the processor 42.
Such conditions may include an interface temperature that is
greater than the target temperature by a second specified number of
degrees that is greater than the specified number of degrees
associated with a soft cutoff. For example, if the target
temperature is 65.degree. C. and the measured interface temperature
is at least 10 degrees greater than 65.degree. C., then the power
to the electrode may be interrupted.
[0102] In another configuration of the system, the electrodes 32
are grouped into electrode zones, with each zone including one or
more electrodes. In a preferred embodiment, the electrodes within a
zone are adjacent each other. At least one of the electrodes 32
within each zone includes a temperature sensor 40. The processor 42
monitors the interface temperatures of each electrode 32 having a
temperature sensor 40 and adjusts the power to each of the
electrodes within an electrode zone based on the maximum interface
temperature in that zone. Accordingly, if the electrode 32 having
the maximum interface temperature provides an interface temperature
sufficient to warrant a duty cycle increase, duty cycle decrease,
soft cutoff or hard cutoff, each electrode 32 within the zone is
subject to the same adjustment.
[0103] The inventors hereby incorporate by reference application
Ser. No. 09/073,112, now U.S. Pat. No. 6,171,305 and U.S. Pat. No.
6,050,994 both of which are assigned to the assignee of the present
invention.
[0104] While several particular forms of the invention have been
illustrated and described, it will be apparent that various
modifications can be made without departing from the spirit and
scope of the invention. For example, the controller 20 is shown in
FIG. 1 as forming a part of the power control system 12. However,
it may take other forms such as an external processor in a separate
computer for example. Likewise, duty cycle control and phase
control may be performed by circuits other than those shown here.
Accordingly, it is not intended that the invention be limited,
except as by the appended claims.
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