U.S. patent application number 13/350659 was filed with the patent office on 2012-05-10 for systems and methods for determining an optimal defibrillation shock waveform.
This patent application is currently assigned to PACESETTER, INC.. Invention is credited to Michael R. Pittaro.
Application Number | 20120116472 13/350659 |
Document ID | / |
Family ID | 39170758 |
Filed Date | 2012-05-10 |
United States Patent
Application |
20120116472 |
Kind Code |
A1 |
Pittaro; Michael R. |
May 10, 2012 |
SYSTEMS AND METHODS FOR DETERMINING AN OPTIMAL DEFIBRILLATION SHOCK
WAVEFORM
Abstract
Methods and systems for determining an optimal defibrillation
shock waveform for application to the heart of a patient may
include measuring and/or collecting information for a cardiac
waveform of a patient, produced as a result of either an electrical
stimulus applied to a heart of the patient, which may be a pacing
shock/stimulus and/or a defibrillation shock waveform, or as the
result of intrinsic cardiac activation; determining a
characteristic of the cardiac waveform; comparing the determined
characteristic of the cardiac waveform to a plurality of values for
the characteristic with optional reference to the defibrillator
system impedance, wherein each value of the characteristic is
associated with a predetermined value for a parameter of an optimal
defibrillation shock waveform; and selecting the predetermined
value for the parameter of the optimal defibrillation shock
waveform based on the comparison.
Inventors: |
Pittaro; Michael R.; (New
Canaan, CT) |
Assignee: |
PACESETTER, INC.
Sylmar
CA
|
Family ID: |
39170758 |
Appl. No.: |
13/350659 |
Filed: |
January 13, 2012 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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11824278 |
Jun 28, 2007 |
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13350659 |
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60818063 |
Jun 29, 2006 |
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Current U.S.
Class: |
607/7 |
Current CPC
Class: |
A61N 1/3906
20130101 |
Class at
Publication: |
607/7 |
International
Class: |
A61N 1/39 20060101
A61N001/39 |
Claims
1. A method for determining an optimal defibrillation shock
waveform for use by an implantable defibrillation system, said
method comprising: obtaining a cardiac electrogram of a patient's
heart, wherein the cardiac electrogram is a measure of the varying
electrical potential between two electrodes positioned adjacent the
heart and is characterized by one or more of a baseline, at least
one peak above a baseline, and at least one trough below a
baseline; determining a value of at least one characteristic of the
cardiac electrogram; and selecting a predetermined value for at
least one parameter of an optimal defibrillation shock waveform,
wherein the at least one parameter is based on the determined value
of the at least one characteristic of the cardiac electrogram;
wherein the at least one parameter defines the optimal
defibrillation shock waveform and is selected from a group
consisting of: a total energy of an optimal defibrillation shock
waveform, a voltage of an optimal defibrillation shock waveform, a
current of an optimal defibrillation shock waveform, a time period
for a first phase of an optimal defibrillation shock waveform, a
time period for second phase of an optimal defibrillation shock
waveform for the patient, a time period for a third phase of a
defibrillator shock waveform, a tilt of an optimal defibrillation
shock waveform, and a polarity of a phase of a defibrillator shock
waveform.
2. The method of claim 1, wherein selecting the predetermined value
for the at least one parameter of the optimal defibrillation shock
waveform includes making reference to a measured defibrillator
system impedance.
3. The method of claim 1, wherein selecting the predetermined value
for the at least one parameter of the optimal defibrillation shock
waveform comprises comparing the determined value of the at least
one characteristic of the cardiac electrogram to a plurality of
values of the at least one characteristic of the cardiac
electrogram, wherein each value is associated with a specific
predetermined value for the at least one parameter of an optimal
defibrillation shock waveform.
4. The method of claim 1, further comprising applying the selected
predetermined value for the at least one parameter to the
defibrillation system.
5. The method of claim 1, wherein prior to determining the value of
the at least one characteristic of the cardiac electrogram, the
method further comprises measuring and/or collecting information of
the cardiac electrogram.
6. The method of claim 1, wherein the cardiac electrogram is
produced either as the result of an electrical stimulus applied to
the heart of the patient, which may be from a pacing shock/stimulus
and/or a defibrillation shock waveform, or as the result of
intrinsic cardiac activation.
7. The method of claim 1, further comprising determining one or
more of the predetermined values of the at least one parameter for
an optimal defibrillation shock waveform.
8. The method of claim 7, wherein the one or more predetermined
values of the at least one parameter for an optimal defibrillation
shock waveform is determined substantially in real-time.
9. The method of claim 7, wherein the one or more predetermined
values of the at least one parameter for an optimal defibrillation
shock waveform is determined after measuring and/or collecting
information of the cardiac electrogram.
10. The method of claim 1, wherein the cardiac electrogram is an
intracardiac electrogram.
11. The method of claim 1, wherein the cardiac electrogram is a
surface electrocardiogram.
12. The method of claim 1, wherein the at least one characteristic
of the cardiac waveform is selected from a group consisting of: a
time period between points or portions of the cardiac electrogram,
a slope of a portion of the cardiac electrogram, an area under the
curve (AUC) of at least a portion of the cardiac electrogram, a
time period between a pacing stimulus and a point of the cardiac
electrogram, and a mathematical analysis of the electrogram.
13. The method of claim 1, wherein determining the optimal
defibrillation shock waveform includes determining an impedance of
an implanted defibrillator system for applying the defibrillation
shock waveform to the heart of the patient.
14. A system for determining an optimal defibrillation shock
waveform for use by an implantable defibrillation system, said
system comprising: means for obtaining a cardiac electrogram of a
patient's heart, wherein the cardiac electrogram is a measure of
the varying electrical potential between two electrodes positioned
adjacent the heart and is characterized by one or more of a
baseline, at least one peak above a baseline, and at least one
trough below a baseline; determining means for determining a value
of at least one characteristic of the cardiac electrogram; and
selecting means for selecting a predetermined value for at least
one parameter of an optimal defibrillation shock waveform, wherein
the at least one parameter is based on the determined value of the
at least one characteristic of the cardiac electrogram; wherein the
at least one parameter defines the optimal defibrillation shock
waveform and is selected from a group consisting of: a total energy
of an optimal defibrillation shock waveform, a voltage of an
optimal defibrillation shock waveform, a current of an optimal
defibrillation shock waveform, a time period for a first phase of
an optimal defibrillation shock waveform, a time period for second
phase of an optimal defibrillation shock waveform for the patient,
a time period for a third phase of a defibrillator shock waveform,
a tilt of an optimal defibrillation shock waveform, and a polarity
of a phase of a defibrillator shock waveform.
15. The system of claim 14, wherein the selecting means comprises
comparing means for comparing the determined value of the at least
one characteristic of the cardiac electrogram and optionally a
defibrillator system impedance to a plurality of first values of
the at least one characteristic of the cardiac electrogram, wherein
each first value is associated with a specific predetermined value
for the at least one parameter of an optimal defibrillation shock
waveform.
16. The system of claim 14, further comprising application means
for applying the selected predetermined value for the at least one
parameter to the defibrillation system.
17. The system of claim 14, further comprising measuring and/or
collecting means for measuring and/or collecting information of the
cardiac electrogram.
18. The system of claim 14, further comprising electrical stimulus
means for applying an electrical stimulus to the heart of the
patient.
19. The system of claim 14, wherein determining means determines
one or more of the predetermined values of the at least one
parameter for an optimal defibrillation shock waveform.
20. The system of claim 19, wherein the one or more predetermined
values of the at least one parameter of an optimal defibrillation
shock waveform is determined substantially in real-time.
21. The system of claim 19, wherein the one or more predetermined
values of the at least one parameter of an optimal defibrillation
shock waveform is determined after measuring and/or collecting
information of the cardiac electrogram.
22. The system of claim 18, wherein the electrical stimulus
comprises a pacing stimulus or a defibrillation shock waveform.
23. The system of claim 14, wherein the cardiac electrogram is an
intracardiac electrogram.
24. The system of claim 14, wherein the cardiac electrogram is a
surface electrocardiogram.
25. The system of claim 14, wherein the at least one characteristic
of the cardiac electrogram is selected from a group consisting of:
a time period between points or portions of the cardiac
electrogram, a slope of a portion of the cardiac electrogram, an
area under the curve (AUC) of at least a portion of the cardiac
electrogram, a time period between a pacing stimulus and a point of
the cardiac electrogram, and a mathematical analysis of the
electrogram.
Description
CROSS REFERENCE
[0001] This application is a continuation of U.S. patent
application Ser. No. 11/824,278, filed Jun. 28, 2007, which claims
the benefit of U.S. Provisional Application No. 60/818,063, filed
Jun. 29, 2006.
FIELD OF THE INVENTION
[0002] Embodiments of the present invention are directed to
defibrillators and defibrillation, and more particularly, to
methods and systems for optimizing defibrillation shock waveforms
for defibrillation devices and more particularly, to implantable
defibrillation devices.
BACKGROUND
[0003] Defibrillation of a heart experiencing ventricular
fibrillation (VF) or ventricular tachycardia (VT) occurs by
applying a defibrillation shock waveform (DSW) to the heart which
presents a large enough voltage gradient across the heart to stop
the VF or VT. Such a voltage gradient not only enables the
cessation of ventricular fibrillation, but generally reestablishes
normal heart rhythm.
[0004] Currently, the medical device industry provides implantable
cardiac defibrillators (ICDs) from a variety of manufacturers
including Medtronic, Inc. and St. Jude Medical, Inc. For example,
St. Jude Medical markets ICDs identified by the Photon.RTM.,
Epicni, Epic.sup.-D"+ and Contour.RTM. families. Such examples may
be found at the St. Jude Medical website (e.g., www.sjm.com), the
information of which, pertaining to such devices, is herein
incorporated by reference in its entirety (see also,
http://en.wikipedia.org/wiki/Implantable cardioverterdefibrillator,
page was last modified 00:17, 18 Jun. 2006, the entire disclosure
of which is herein incorporated by reference in its entirety).
[0005] The defibrillation shock waveform (DSW) for such ICDs
typically comprises a biphasic waveform pulse, an example of which
is illustrated in FIG. 2. As shown, such a biphasic waveform pulse
generally comprises two portions: a first positive phase and a
second negative phase (though the polarities may be reversed). The
"tilt" of the waveform comprises the slope of the first phase and
is a function of the duration of that portion of the DSW. The tilt
may be viewed as the slope of the difference in voltage of the
leading edge compared with the trailing edge of each pulse.
Accordingly, as the duration of the first phase increases, for a
given impedance, so does the tilt value. Generally, in such ICDs,
the tilt or time period for each phase of the biphasic waveform
pulse can be adjusted to optimize the DSW for a particular patient.
The pulse width duration(s) may be fixed, yielding varying tilts
depending on the impedance of the system. Alternatively, the tilt
may be fixed, resulting in varying pulse widths depending on the
system impedance.
[0006] Realizing a "large enough" voltage gradient or threshold to
overcome VF using a DSW is dependent upon a number of factors
including capacitor size of the defibrillator, maximum voltage,
voltage duration of the defibrillator waveform, corresponding shape
of the defibrillator waveform, and the arrangement and/or
orientation of defibrillation electrodes. Furthermore,
characteristics of the cardiac tissue and defibrillator system
(ICD) impedance can also play an important role in determining the
defibrillation threshold.
[0007] The defibrillation threshold may be minimized upon an
accurate (i.e., measured) membrane time constant (or chronaxie) of
a particular patient's heart. The membrane time constant is a
measure of the time it takes for the membrane voltage to reach a
new value, and is independent of the strength (voltage, energy or
amps) of the shock of the DSW. However, the membrane time constant
of the cardiac tissue is not known with precision and cannot be
currently measured in vivo.
[0008] The impedance of the ICD shock is readily measured and may
also influence the time course of the voltage across the cardiac
tissue after the start of the shock (i.e., large voltage across the
heart). Accordingly, as impedance increases, so does the time for
the cardiac tissue to reach maximum value. In addition, the ideal
shock duration of the DSW, or other DSW properties, may change as
impedance changes.
[0009] In defibrillation, one aim is, with a shock of one polarity,
to depolarize substantially all the cardiac tissue cells
simultaneously or prolong refractoriness, and then remove the
charge with a shock of the opposite polarity. However, when longer
pulse widths are unneccessarily applied, re-initiation of
fibrillation may occur after defibrillation. If a long enough pulse
width is not applied, the tissue may not be simultaneously
depolarized or have refractoriness prolonged, and fibrillation may
persist.
BRIEF DESCRIPTION OF THE FIGURES
[0010] FIG. 1 is an illustration of a cardiac waveform, with noted
points of interest, which may be analyzed by some embodiments of
the invention.
[0011] FIG. 2 is a typical illustration of a biphasic waveform for
a defibrillation shock waveform typically used in implantable
cardiac devices.
[0012] FIGS. 3-1 and 3-2 together form a chart illustrating pulse
time values for positive and negative phases of a biphasic
defibrillation waveform, which may be set in an implantable cardiac
device.
[0013] FIGS. 4-1 through 4-6 together form a chart illustrating
patient data of some of the embodiments of the present
invention.
[0014] FIG. 5 is a depiction of a system of the invention.
SUMMARY OF THE EMBODIMENTS OF THE PRESENT INVENTION
[0015] Embodiments of the present invention are directed to ICDs,
examples of which are disclosed in published U.S. patent
application Ser. No. 10/437,110 (U.S. publication no. 20040002738),
the entire disclosure of which is herein incorporated by
reference.
[0016] Accordingly, some embodiments of the present invention are
able to determine an optimal DSW for a particular patient by
analyzing one or more characteristics of the cardiac waveform of
the patient. Moreover, in some embodiments, optimal durations for
one or both of each phase of the biphasic waveform of a DSW or the
optimal tilt of the DSW may be determined by analyzing the one or
more characteristics of the cardiac waveform.
[0017] By identifying optimal defibrillation waveform variables
prior to testing an ICD, a lower defibrillation threshold may be
determined. A lower defibrillation threshold may result in safer
and shortened defibrillation testing, smaller defibrillator units,
a greater margin of safety for successful defibrillation, and more
rapid delivery of therapy. In addition, there may be increased
device longevity, decreased myocardial tissue damage, improved
myocardial function, decreased patient pain, and improved device
performance should the optimal waveform change, over the life of
the device.
[0018] The cardiac waveform which is analyzed may be an intrinsic
waveform, that is, a waveform from a heart beat without
stimulation, or a waveform generated as a result of an applied
electrical stimulus. Such a stimulus may be a pacing
stimulus/shock, as well as from a DSW, either of which (of course)
may be applied via a ICD. A cardiac waveform generated as the
result of such pacing stimulus may be a repeatable, evoked, and/or
entrainable response.
[0019] For example, in one embodiment of the invention, an ICD
applies one or more stimuli/pacing shocks to the heart of a
patient. The resulting waveform(s) is then measured and/or the
corresponding information/data recorded and/or analyzed to
determine one or more characteristics of the cardiac waveform. A
cardiac waveform is illustrated in FIG. 1, although one of ordinary
skill in the art will recognize that there are many variations of a
cardiac waveform and the current waveform is for illustrative
purposes, and is not meant to limit the scope of the invention.
[0020] As shown, the illustrated cardiac waveform is graphically
plotted, where the x-axis comprises time, typically measured in
milliseconds, and the y-axis comprises voltage, typically measured
in millivolts (for example). Accordingly, in some embodiments of
the invention, the waveform data collected may yield the following
information in Table I:
TABLE-US-00001 TABLE I Point/Item Description A initial start of
deflection B first trough C peak D second trough E return to
baseline or zero crossing F slope of any portion of the line
between points B and C (in, for example, msec/millivolt) G time
period (msec) between points B and C H time period G divided by the
voltage differential (millivolts) between points B and C I time
period (msec) between stimulation to point A J time period (msec)
between stimulation to point B K time period (msec) between
stimulation to point C L time period (msec) between stimulation to
point D M time period (msec) between stimulation to point E N time
period (msec) between points C and D 0 time period (msec) between
points C and E P Slope of any portion of the line between points A
and B Q time period (msec) between points A and B R time period
(msec) between points A and C S time period (msec) between points A
and D T time period (msec) between points A and E U Area under the
curve (AUC) (e.g., points B, C and D) W Time period (msec) between
any E point and any other point noted. X An inflection point Y Time
period (msec) between points X and any other point noted
[0021] One of ordinary skill in the art will appreciate that other
characteristics of a cardiac waveform other than those listed above
may be measured and/or determined, including any mathematical
analysis of the waveform or mathematical analysis of
characteristics of the waveform. Such mathematical analysis may
include one or more of: a Fourier transformation, a Bartlett
transformation of the cardiac waveform, a wavelet analysis, and a
relationship between characteristics and/or a relationship of the
results of a mathematical analysis (e.g., at least any of the
foregoing) of the waveform. Based on the measured, collected and/or
determined data, a value of one or more parameters of a DSW for the
particular patient can be determined.
[0022] The following example of one embodiment of the present
invention will be discussed with reference to St. Jude Medical ICDs
having adjustable parameter settings for a DSW. In particular, the
following example is in reference to St. Jude Medical ICDs using
biphasic DSW, where the pulse durations of both phases (positive
and negative) or the tilt may be adjustable. In that regard, FIG. 3
is an exemplary chart illustrating the pulse durations P1 and P2
for different impedances of an ICD, as well as associated tilt
associated with the particular phase of the biphasic waveform. One
of ordinary skill in the art will appreciate that the following
described example is not meant to limit the scope of the present
invention, but merely to demonstrate at least one embodiment of the
invention which may be applicable to one or more other embodiments
of the present invention.
[0023] The chart illustrated in FIG. 3 is a chart listing pulse
durations for a biphasic DSW for one or more defibrillator devices
manufactured by St. Jude Medical, Inc. (for example), obtained from
a St. Jude document entitled, "ICD Alternative Defibrillation
Bi-Phasic Waveform Pulse Width Recommendations" (copyright St. Jude
Medical, Inc., 2004), the entire contents of which are herein
incorporated by reference ("Pulse Width Publication"). The pulse
widths listed in each block preferably correspond to particular
defibrillator system impedance values and other defibrillator
specific variables (e.g., capacitance), and list P1 (pulse
durations of the positive phase of the DSW) and P2 (pulse durations
of the negative phase of the DSW) values for three model membrane
time constants (t): 2.5, 3.5 and 4.5 msec (for example). These
model membrane time constants were chosen based on in vitro
mammalian tissue and cell studies and modeling. However, currently,
no information from any institution or manufacturer offers a way to
determine which model membrane time constant is optimum for the
heart of a particular patient.
[0024] The selection of optimal DSW parameters, for example pulse
widths or tilts, of some embodiments of the present invention, may
be based on matching a defibrillator waveform to one or more
defibrillation characteristics of cardiac tissue (e.g., such as the
membrane time constant or a measurement which correlates with the
membrane time constant) and additionally, in some embodiments, on
characteristics of a defibrillation system, such as impedance and
capacitance. Accordingly, if cardiac tissue can be depolarized
rapidly, a shorter pulse width is preferably the most efficient way
to defibrillate the cardiac tissue, of some embodiments of the
invention. In some embodiments, repolarization may also play an
important role in optimum P1 and P2.
[0025] Accordingly, in one embodiment of the present invention, for
example, G values (see Table I above) of the cardiac waveform
measured, of less than about 40 msecs for a particular patient,
correspond to shorter P1 and/or P2 durations (e.g., Block 2 of FIG.
3) which enable optimum defibrillation for a particular patient.
Slightly slower time periods of between about 40 msec and 70 msec
for item G of the cardiac waveform have been found to correspond to
mid-range values for P1 and P2 (e.g., Block 1 of FIG. 3). In
another example, F values of less than 3 msec/millivolt (see Table
I above) of the cardiac waveform measured correspond to shorter P1
and/or P2 durations (e.g., Block 2 of FIG. 3) which enable optimum
defibrillation for a particular patient. Greater values of F
(greater than 3 msec/millivolt) correspond with longer P1 and/or P2
durations (e.g., Block 1 or 3 of FIG. 3). Accordingly, FIG. 4 is a
chart summarizing collected data for a plurality of patients. In
the figure, the column headings comprise:
TABLE-US-00002 Heading Details No. Identifies a particular patient
G Time period (msec) between points B and C on the cardiac waveform
analyzed Block+ Minimum energy/voltage at which a DSW is successful
at defibrillating VF, corresponding to the noted Block (i.e., 1, 2
or 3) for table illustrated on FIG. 3 Block- Maximum energy/voltage
at which a DSW fails, corresponding to the noted Block (i.e., 1, 2
or 3) for table illustrated on FIG. 3 PW Pulse width for PI/P1 in
msec, corresponding to the noted Block (i.e., 1, 2 or 3) for table
illustrated on FIG. 3, or for 65% tilt Imp Impedance of the DSW,
corresponding to the noted Block (i.e., 1, 2 or 3) for table
illustrated on FIG. 3, or for 65% tilt 65+ Minimum energy/voltage
at which a DSW is successful at defibrillating VF using fixed tilt
of 65% 65- Maximum energy/voltage at which a DSW fails at
defibrillating VF using fixed tilt of 65% Pred Best G Predicted
Block for values for optimal DSW. The measurement and observation
conducted related to a G value of less than 40 msec predicting that
values in Block 2 were optimal or equal than values of other Blocks
or 65% tilt, and 40 msec or greater predicting that other than
Block 2 values were optimal or equal to Block 2 values (see FIG. 3
for Block values). Pred Best F Predicted Block for values for
optimal DSB. The measurement and observation conducted related to
an F value of less than 3 msec/millivolt predicting that values in
Block 2 were optimal or equal than values of other Blocks or 65%
tilt, and 3 msec/millivolt or greater predicting that other than
Block 2 values were optimal or equal to Block 2 values (see FIG. 3
for Block values). Best Block (FIG. 3) or tilt associated with
values of actual optimal DSW for a particular patient. Results Did
predicted Block or tilt selection for optimal DSW meet actual Block
or tilt for optimal DSW? Separate columns for G and F.
[0026] As can be readily apparent by a review of the patient data
in FIG. 4, the predicted Block or tilt for selection of values for
an optimal DSW, of some of the embodiments of the present
invention, for example using G values, was the actual Block or tilt
for selection of values for the actual optimal DSW in 43 out of 48
cases. For example using F values, the predicted Block or tilt for
selection of values for an optimal DSW, of some of the embodiments
of the present invention, was the actual Block or tilt for
selection of values for the actual optimal DSW in 44 out of 47
cases.
[0027] Accordingly, pulse width or tilt selections for such optimal
waveforms, e.g., for either or both of the biphasic wave phases, as
well as voltage, amperage and energy may be automatically or
manually determined and set of some embodiments of the present
invention. For example, cardiac waveform characteristics may be
measured and may also be stored by an ICD, by an ICD programmer or
other similar device, or by hand and then compared to stored or
listed values for such characteristics (e.g., lookup table). The
stored/listed values for such characteristics may also include one
or more corresponding optimal DSW/defibrillator
parameters/variables (e.g., pulse values, peak voltage, peak
amperage, energy, tilt). Thus, upon matching, or substantially
matching, a measured cardiac waveform characteristic to a stored
value for that characteristic, a value for one or more parameters
for the optimal DSW/defibrillator may be obtained and then applied
to the ICD for application a next time a DSW is necessary for the
heart of the particular patient to eliminate VF. As stated earlier,
the optimal DSW or parameters thereof, may also depend on the
determination of other variables, such as the impedance of the
defibrillator/ICD.
[0028] A defibrillator/ICD may then be programmed for an optimal
DSW and/or optimum parameters either manually (e.g., surgical
technician, and the like), for example, with reference to a
generated chart or a reference chart, programmed automatically, or
programmed via prompts to an operator. Means to accomplish
automatic programming (or any of the foregoing) may include
software and/or hardware included with the ICD, and/or another
device, internal or external to the patient. To that end, the
software and/or hardware may be established to conduct cardiac
waveform measurements at predetermined, programmed intervals and
either automatically program new DSW/defibrillator parameters, or
provide an alert to a surgeon/specialist upon patient follow up,
for example during direct interrogation or during remote follow up,
or provide an alert to the patient. If an alert type system is
used, the DSW/defibrillator parameters may be changed by
programming during direct interrogation or via communications
(e.g., trans-telephonically or other form of remote follow up).
[0029] Other aspects of the device, such as the leads and ICD
generator (including but not limited to the casing, battery, pulse
generator, capacitors, circuitry to provide pacing and a biphasic
defibrillator waveform with programmable parameters, e.g., P1
duration and P2 duration, and fixed tilt, and ability to record a
waveform) are analogous to commercially available ICD devices, as
stated above, such as the St. Jude model V-243.
[0030] Accordingly, in one embodiment of the present invention, a
method for determining an optimal defibrillation shock waveform for
application to the heart of a patient may include: determining a
value of at least one characteristic of a cardiac waveform of a
patient and selecting, with optional reference to the impedance of
the system, a predetermined value for at least one parameter of an
optimal defibrillation shock waveform corresponding to the
determined value of the at least one characteristic of the cardiac
waveform.
[0031] Hence, in certain embodiments, the determining of the
optimal defibrillation shock waveform includes determining an
impedance of an implanted defibrillator system, such as the one
described below, for applying the defibrillation shock waveform to
the heart of the patient. Further, in certain embodiments, the at
least one parameter of an optimal defibrillation shock waveform
includes one or more of a total energy of an optimal defibrillation
shock waveform, a voltage of an optimal defibrillation shock
waveform, a current of an optimal defibrillation shock waveform, a
time period for a first phase of an optimal defibrillation shock
waveform, a time period for second phase of an optimal
defibrillation shock waveform for the patient (e.g., where the
first phase is a positive polarity of the defibrillation shock
waveform and the second phase is a negative polarity of the
defibrillation shock waveform), a time period for a third phase of
a defibrillator shock waveform, a tilt of an optimal defibrillation
shock waveform, and a polarity of a phase of the defibrillator
shock waveform.
[0032] In certain embodiments, the cardiac waveform may be an
intracardiac electrogram or a surface electrocardiogram. Further,
in certain embodiments, the at least one characteristic of the
cardiac waveform may be one or more of: a time period between
points or portions of the cardiac waveform, such as the waveform
provided in FIG. 1, for instance, a slope of a portion of the
cardiac waveform, an area under the curve (AUC) of at least a
portion of the cardiac waveform, the time period between a pacing
stimulus and a point of the cardiac waveform, and a mathematical
analysis of the waveform, such as a Fourier transformation, a
Bartlett transformation, a wavelet analysis, a relationship between
characteristics, and a combination of any of the foregoing.
[0033] For example, where the at least one characteristic includes
a time period between points or portions of the cardiac waveform,
the points may include a peak, a trough, a return to baseline or
zero crossing, an inflection point, the initial start of the
deflection, and the end of the waveform. In certain embodiments,
the time period may include the period between particular points on
the cardiac waveform and a height of the cardiac waveform. For
instance, the time period between particular points of the cardiac
waveform may include the time period between any peak of the
cardiac waveform and any trough of the cardiac waveform.
Specifically, in certain embodiments, the time period between
particular points of the cardiac waveform may include the time
period between a first or second peak and/or a first or second
trough, for instance, a trough of the cardiac waveform and a
subsequent peak of the cardiac waveform. Accordingly, the time
period may include the time period between an initial peak of the
cardiac waveform and a point at which the cardiac waveform reaches
baseline after a first or second trough of the cardiac waveform.
Additionally, the time period may include the time period between a
first or second peak or first or second trough subsequent to the
application of an electrical stimulus.
[0034] Specifically, the time period may include a period between
particular points of the cardiac waveform such as the time period
between the electrical stimulus and a first trough or peak or
second trough or second peak of the cardiac waveform. For instance,
the time period between particular points of the cardiac waveform
may include the time period between the electrical stimulus and a
point at which the cardiac waveform reaches baseline after a second
trough of the cardiac waveform. In certain embodiments, the time
period between particular points of the cardiac waveform may
include the time period between a peak of the cardiac waveform and
a second trough of the cardiac waveform.
[0035] Additionally, the time period may include the time period
between an electrical stimulus and a point substantially
corresponding to an initial start of deflection of the cardiac
waveform. The time period may also include the time period between
a point of initial deflection of the cardiac waveform to a
subsequent trough or to a subsequent peak of the cardiac waveform.
For instance, the time period may include the time period between a
point of initial deflection of the cardiac waveform to a first or
second trough of the cardiac waveform. Further, the time period may
include the time period between a point of initial deflection of
the cardiac waveform to a point at which the cardiac waveform
substantially reaches baseline, or a point at which the cardiac
waveform substantially reaches baseline after a second trough of
the cardiac waveform. Accordingly, the time period between
particular points of the cardiac waveform may include the time
period between an inflection point and another point of the cardiac
waveform, wherein the other point is a member may be a peak, a
trough, a return to baseline or zero crossing, an inflection point,
the initial start of the deflection, and the end of the
waveform.
[0036] In another embodiment of the present invention, a method for
determining an optimal defibrillation shock waveform for
application to the heart of a patient to stop ventricular
fibrillation or ventricular tachycardia is provided, which may
include measuring and/or collecting information for a cardiac
waveform of a patient, produced as a result of either an electrical
stimulus applied to a heart of the patient (pacing shock/stimulus
or DSW) or as the result of intrinsic cardiac activation,
determining a characteristic of the waveform, comparing the
determined characteristic of the cardiac waveform to a plurality of
values for the characteristic, with optional reference to the
impedance of the system, wherein each value of the characteristic
is associated with a predetermined value for a parameter of an
optimal defibrillation shock waveform, and selecting the
predetermined value for the parameter of the optimal defibrillation
shock waveform based on the comparison.
[0037] In yet another embodiment of the present invention, as set
forth in FIG. 5, a system for determining an optimal defibrillation
.shock waveform for application to the heart of a patient is
provided. The system may include determining means (50) for
determining a value of at least one characteristic of a cardiac
waveform of a patient and selecting means (52) for selecting a
predetermined value for at least one parameter of an optimal
defibrillation shock waveform corresponding to the determined value
of the at least one characteristic of the cardiac waveform, with
optional reference to the impedance of the system. In certain
embodiments, the determining means (50) determines one or more of
the predetermined values of the at least one parameter for an
optimal defibrillation shock waveform, for instance, substantially
in real-time and/or after measuring and/or collecting information
of the cardiac waveform.
[0038] In certain embodiments of the system, the selecting means
may be associated with and/or include a comparing means (54) for
comparing the determined value of the at least one characteristic
of the cardiac waveform and optionally a defibrillator system
impedance to a plurality of first values of the at least one
characteristic of the cardiac waveform, wherein each first value
may be associated with a specific predetermined value for the at
least one parameter of an optimal defibrillation shock
waveform.
[0039] Accordingly, in certain embodiments, a system for
determining an optimal defibrillation shock waveform for
application to the heart of a patient is provided. The system may
include a measuring and/or collecting means for measuring and/or
collecting, respectively, information for a cardiac waveform of a
patient, produced as a result of either an electrical stimulus
applied to a heart of the patient, which may be a pacing shock
and/or a defibrillation shock waveform, or as the result of
intrinsic cardiac activation. The system may also include: a
determining means for determining a characteristic of the waveform;
a comparing means for comparing the determined characteristic of
the cardiac waveform to a plurality of first values for the
characteristic, wherein each first value of the characteristic is
associated with a predetermined value for a parameter of an optimal
defibrillation shock waveform; and a selecting means for selecting
the predetermined value for the parameter of the optimal
defibrillation shock waveform based on the comparison.
[0040] In certain embodiments, the system may include an
application means (56) for applying the selected predetermined
value for the at least one parameter to a defibrillation device
(58). Additionally, the system may include a measuring and/or
collecting means (42 and 44, respectively) for measuring and/or
collecting information of the cardiac waveform. The system may also
include an electrical stimulus means (40) for applying an electri61
stimulus to the heart of a patient, for instance, a means for
providing a pacing stimulus or a defibrillation shock waveform to
the heart.
[0041] In yet another embodiment of the present invention, a system
for determining an optimal defibrillation shock waveform for
application to the heart of a patient may include measuring and/or
collecting means for measuring and/or collecting, respectively,
information for a cardiac waveform of a patient, produced as a
result of either an electrical stimulus applied to a heart of the
patient, which may be a pacing shock/stimulus and/or a DSW, or as
the result of intrinsic cardiac activation, determining means for
determining a characteristic of the waveform, and comparing means
for comparing the determined characteristic of the cardiac waveform
and optional system impedance to a plurality of first values for
the characteristic. Each first value of the characteristic is
associated with a predetermined value for a parameter of an optimal
defibrillation shock waveform. The system may also include
selecting means for selecting the predetermined value for the
parameter of the optimal defibrillation shock waveform based on the
comparison.
[0042] In yet another embodiment of the present invention, an
implantable cardiac defibrillation device is provided which may
include electrical shock means for generating and/or applying a
defibrillation shock waveform to the heart of a patient, measuring
and/or collecting means for measuring and/or collecting,
respectively, information for a cardiac waveform of a patient,
produced as a result of either an electrical stimulus applied to a
heart of the patient, which may be a pacing shock/stimulus and/or a
DSW, or as the result of intrinsic cardiac activation, determining
means for determining a characteristic of the waveform, and
comparing means for comparing the determined characteristic of the
cardiac waveform and optional system impedance to a plurality of
first values for the characteristic, where each first value of the
characteristic is associated with a predetermined value for a
parameter of an optimal defibrillation shock waveform.
[0043] The system may also include selecting means for selecting
the predetermined value for the parameter of the optimal
defibrillation shock waveform based on the comparison and
configuring means for configuring the electrical shock means to
apply the optimal defibrillation shock waveform based on the
selected defibrillation parameter.
[0044] In yet another embodiment of the present invention, a method
for determining an optimal defibrillation shock waveform for a
defibrillation device may include measuring and/or collecting
information of a cardiac waveform of a patient produced as a result
of either an electrical stimulus applied to a heart of the patient,
which may be a pacing shock/stimulus and/or a DSW, or as the result
of intrinsic cardiac activation, determining at least one
characteristic of the waveform, and using the characteristic or
combination of characteristics to calculate at least one value for
a parameter of an optimal defibrillation shock waveform for the
patient. The value for the parameter may also depend upon system
impedance.
[0045] Having now described a few embodiments of the invention, it
should be apparent to those skilled in the art that the foregoing
is merely illustrative and not limiting, and it should be
understood that numerous changes in analysis, components and
configuration of the disclosed embodiments may be introduced
without departing from the true spirit of the invention as defined
in the appended exemplary claims.
* * * * *
References