U.S. patent application number 11/534910 was filed with the patent office on 2007-01-18 for method and apparatus for temporarily varying a parameter in an implantable medical device.
Invention is credited to Earl E. Bakken, Rebecca M. Bergman, William J. Combs, H. Toby Markowitz.
Application Number | 20070016259 11/534910 |
Document ID | / |
Family ID | 33517505 |
Filed Date | 2007-01-18 |
United States Patent
Application |
20070016259 |
Kind Code |
A1 |
Bakken; Earl E. ; et
al. |
January 18, 2007 |
METHOD AND APPARATUS FOR TEMPORARILY VARYING A PARAMETER IN AN
IMPLANTABLE MEDICAL DEVICE
Abstract
A method and apparatus for varying a parameter in an implantable
medical device that includes a plurality of electrodes stimulating
heart tissue and sensing cardiac signals, a timing and control
device controlling the stimulation of heart tissue by the plurality
of electrodes and measuring intervals between the sensed cardiac
signals, a storage device storing the measured intervals, and a
microprocessor. The microprocessor determines heart rate
variability in response to the stored intervals, compares the
determined heart rate variability to a predetermined target rate
profile, adjusts the parameter from a first setting to a second
setting different from the first setting in response to the
comparing of the determined heart rate variability and the
predetermined target rate profile, and adjusts the parameter from
the second setting to a termination setting in response to a
termination event or expiration of a first predetermined time
period.
Inventors: |
Bakken; Earl E.; (North Kona
Coast, HI) ; Bergman; Rebecca M.; (North Oaks,
MN) ; Combs; William J.; (Minnetonka, MN) ;
Markowitz; H. Toby; (Roseville, MN) |
Correspondence
Address: |
MEDTRONIC, INC.
710 MEDTRONIC PARK
MINNEAPOLIS
MN
55432-9924
US
|
Family ID: |
33517505 |
Appl. No.: |
11/534910 |
Filed: |
September 25, 2006 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
|
|
10465351 |
Jun 19, 2003 |
7133718 |
|
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11534910 |
Sep 25, 2006 |
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Current U.S.
Class: |
607/9 |
Current CPC
Class: |
A61N 1/365 20130101;
A61N 1/36592 20130101 |
Class at
Publication: |
607/009 |
International
Class: |
A61N 1/362 20070101
A61N001/362 |
Claims
1. An implantable medical device, comprising: a plurality of
electrodes stimulating heart tissue and sensing cardiac signals; a
timing and control device controlling the stimulation of heart
tissue by the plurality of electrodes and measuring intervals
between the sensed cardiac signals; a storage device storing the
measured intervals; and a microprocessor determining heart rate
variability in response to the stored intervals, comparing the
determined heart rate variability to a predetermined target rate
profile, adjusting the parameter from a first setting to a second
setting different from the first setting in response to the
comparing of the determined heart rate variability and the
predetermined target rate profile, and adjusting the parameter from
the second setting to a termination setting in response to
expiration of a first predetermined time period.
2. The device of claim 1, further comprising a patient activator
generating a patient request for adjusting the parameter, wherein
the timing and control device generates an indication of a
programmed time of day for initiating the pacing rate variation of
the present invention, and the microprocessor initiates the
adjusting of the parameter in response to receipt of one of the
patient request from the patient activator and the indication of
the programmed time of day from the timing and control unit.
3. The device of claim 1, wherein the storage device stores a
predetermined heart rate profile, and the microprocessor compares
the determined heart rate variability to the target rate profile
and determines the adjusting of the parameter is appropriate in
response to the comparing of the determined heart rate variability
to the target rate profile.
4. The device of claim 3, wherein the microprocessor generates a
histogram of heart rates having a plurality of corresponding heart
rate bins, and determines the adjusting of the parameter is
appropriate in response to a percentage of time that heart rates
are within one or more of the plurality of heart rate bins.
5. The device of claim 3, wherein the microprocessor generates a
histogram of heart rates having a plurality of corresponding heart
rate bins, and determines the adjusting of the parameter is
appropriate in response to a number of beats within one or more of
the plurality of heart rate bins.
6. The device of claim 1, wherein the storage device includes a
predetermined heart rate profile, and the microprocessor compares
the determined heart rate variability to the target rate profile
and determines the adjusting of the parameter is appropriate in
response to change in heart rate variability being less than a
predetermined value.
7. The device of claim 1, wherein the storage device stores
exercise time profiles corresponding to variations in the second
setting, and the microprocessor selects a first exercise time
profile from the stored exercise time profiles in response to the
comparison of the determined heart rate variability to the
predetermined target rate profile.
8. The device of claim 7, wherein each of the stored exercise time
profiles include an acceleration portion corresponding to adjusting
the parameter from the first setting to the second setting, a
steady-state portion corresponding to the second setting, and a
deceleration portion corresponding to adjusting the parameter from
the second setting to the termination setting.
9. The device of claim 8, wherein the first setting corresponds to
a predetermined lower pacing rate and the second setting is greater
than the predetermined lower pacing rate.
10. The device of claim 7, wherein the microprocessor determines
whether the predetermined target rate profile would be exceeded in
response to the first exercise time profile, and selects a second
exercise time profile from the stored exercise time profiles in
response to the predetermined target profile being exceeded.
11. The device of claim 1, wherein the microprocessor adjusts the
parameter from the second setting to the termination setting, prior
to the first predetermined time period, in response to detecting
one of a programming session, a magnet, a cardiac arrhythmia,
spontaneous rate greater than the second setting, and rate response
greater than the second setting.
12. The device of claim 1, wherein the microprocessor generates a
histogram of heart rates and determines, prior to adjusting the
parameter from the first setting to the second setting, whether a
current generated histogram is consistent with a predetermined
number of previously generated histograms.
13. The device of claim 8, wherein the microprocessor determines
whether the target rate profile has been reached, repeats adjusting
of the parameter from the first setting to the second setting and
from the second setting to the termination setting in response to
the target rate profile not being reached, and updates one or more
of the acceleration portion, the steady state portion, and the
deceleration portion in response to the target rate profile being
reached.
14. The device of claim 1, wherein the termination setting
corresponds to one of a spontaneous rate, a rate response rate, and
the first setting.
15. The device of claim 7, further comprising an output device
outputting information corresponding to the selected exercise time
profiles.
16. A method for temporarily varying a parameter in an implantable
medical device, comprising: determining heart rate variability;
comparing the determined heart rate variability to a predetermined
target rate profile; adjusting the parameter from a first setting
to a second setting different from the first setting in response to
the comparing of the determined heart rate variability and the
predetermined target rate profile; and adjusting the parameter from
the second setting to a termination setting in response to
expiration of a first predetermined time period.
17. The method of claim 16, further comprising determining whether
to initiate the varying of a parameter in response to one of
receipt of a patient activation and an internal indication of a
predetermined time of day for initiating the varying of a
parameter.
18. The method of claim 16, further comprising determining whether
the varying of a parameter is appropriate in response to the
comparing the determined heart rate variability to a predetermined
target rate profile.
19. The method of claim 16, wherein determining heart rate
variability includes generating a histogram of heart rates having a
plurality of corresponding heart rate bins.
20. The method of claim 19, further comprising determining whether
the varying of a parameter is appropriate in response to the
comparing the determined heart rate variability to a predetermined
target rate profile, wherein the varying of a parameter is
determined to be appropriate in response to a percentage of time
that heart rates are within one or more of the plurality of heart
rate bins.
21. The method of claim 19, further comprising determining whether
the varying of a parameter is appropriate in response to the
comparing the determined heart rate variability to a predetermined
target rate profile, wherein the varying of a parameter is
determined to be appropriate in response to a number of beats
within one or more of the plurality of heart rate bins.
22. The method of claim 16, further comprising determining whether
the varying of a parameter is appropriate in response to the
comparing the determined heart rate variability to a predetermined
target rate profile, wherein the varying of a parameter is
determined to be appropriate in response to change in heart rate
variability being less than a predetermined value.
23. The method of claim 16, further comprising: storing exercise
time profiles corresponding to variations in the second setting;
and selecting a first exercise time profile from the stored
exercise time profiles in response to the comparing the determined
heart rate variability to a predetermined target rate profile.
24. The method of claim 23, wherein each of the stored exercise
time profiles include an acceleration portion corresponding to
adjusting the parameter from the first setting to the second
setting, a steady-state portion corresponding to the first
predetermined time period, and a deceleration portion corresponding
to adjusting the parameter from the second setting to the
termination setting.
25. The method of claim 24, wherein the first setting corresponds
to a predetermined lower pacing rate and the second setting is
greater than the predetermined lower pacing rate.
26. The method of claim 23, further comprising: determining whether
the predetermined target rate profile would be exceeded in response
to the first exercise time profile; and selecting a second exercise
time profile from the stored exercise time profiles in response to
the predetermined target profile being exceeded.
27. The method of claim 16, further comprising determining whether
to adjust the parameter from the second setting to the termination
setting prior to the first predetermined time period.
28. The method of claim 27, wherein the parameter is adjusted from
the second setting to the termination setting prior to the first
predetermined time period in response to one of a programming
session, a magnet, a cardiac arrhythmia, spontaneous rate greater
than the second setting, and rate response greater than the second
setting.
29. The method of claim 16, wherein determining heart rate
variability includes generating a histogram of heart rates having a
plurality of corresponding heart rate bins, and further comprising,
determining, prior to adjusting the parameter from the first
setting to the second setting, whether a current generated
histogram is consistent with a predetermined number of previously
generated histograms.
30. The method of claim 24, further comprising: determining whether
the target rate profile has been reached; repeating adjusting of
the parameter from the first setting to the second setting and from
the second setting to the termination setting in response to the
target rate profile not being reached; and updating one or more of
the acceleration portion, the steady state portion and the
deceleration portion in response to the target rate profile being
reached.
31. The method of claim 16, wherein the termination setting
corresponds to one of a spontaneous rate, a rate response rate, and
the first setting.
32. The method of claim 23, further comprising; storing information
corresponding to the selected exercise time profile; and outputting
the stored information to an external device.
33. An implantable medical device, comprising: means for
stimulating heart tissue and sensing cardiac signals; means for
controlling timing of the stimulation of heart tissue and measuring
intervals between the sensed cardiac signals; means for determining
heart rate variability in response to the stored intervals; means
for comparing the determined heart rate variability to a
predetermined target rate profile; means for adjusting the
parameter from a first setting to a second setting different from
the first setting in response to the comparing of the determined
heart rate variability and the predetermined target rate profile,
and adjusting the parameter from the second setting to a
termination setting in response to expiration of a first
predetermined time period; means for selecting a first exercise
time profile from stored exercise time profiles in response to the
comparison of the determined heart rate variability to the
predetermined target rate profile, each of the stored exercise time
profiles including an acceleration portion corresponding to
adjusting the parameter from the first setting to the second
setting, a steady-state portion corresponding to the first
predetermined time period, and a deceleration portion corresponding
to adjusting the parameter from the second setting to the
termination setting, wherein the adjusting means adjusts the
parameter from the second setting to the termination setting, prior
to the first predetermined time period, in response to detecting
one of a programming session, a magnet, a cardiac arrhythmia,
spontaneous rate greater than the second setting, and rate response
greater than the second setting.
34. The device of claim 33, further comprising means for generating
a patient request for adjusting the parameter, wherein the
controlling means generates an indication of a programmed time of
day for initiating the adjusting of the parameter, and the
adjusting means initiates adjusting of the parameter in response to
one of the patient request and the indication of the programmed
time of day for initiating the adjusting of the parameter.
35. The device of claim 34, wherein the determining means generates
a histogram of heart rates having a plurality of corresponding
heart rate bins, and determines the adjusting of the parameter is
appropriate in response to a percentage of time that heart rates
are within one or more of the plurality of heart rate bins.
36. The device of claim 33, wherein the determining means generates
a histogram of heart rates having a plurality of corresponding
heart rate bins, and determines the adjusting of the parameter is
appropriate in response to a number of beats within one or more of
the plurality of heart rate bins.
37. The device of claim 33, wherein the first setting corresponds
to a predetermined lower pacing rate and the second setting is
greater than the predetermined lower pacing rate.
38. The device of claim 33, wherein the comparing means determines
whether the predetermined target rate profile would be exceeded in
response to the first exercise time profile, and selects a second
exercise time profile from the stored exercise time profiles in
response to the predetermined target profile being exceeded.
39. The device of claim 33, wherein the determining means generates
a histogram of heart rates and determines, prior to the adjusting
of the parameter from the first setting to the second setting,
whether a current generated histogram is consistent with a
predetermined number of previously generated histograms.
40. The device of claim 33, wherein the comparing means determines
whether the target rate profile has been reached, and the adjusting
means repeats adjusting of the parameter from the first setting to
the second setting and from the second setting to the termination
setting in response to the target rate profile not being reached,
and updates one or more of the acceleration portion, the steady
state portion and the deceleration portion in response to the
target rate profile being reached.
41. The device of claim 33, wherein the termination setting
corresponds to one of a spontaneous rate, a rate response rate, and
the first setting.
42. The device of claim 35, further comprising means for outputting
information corresponding to the selected exercise time
profiles.
43. An implantable medical device, comprising: means for
determining heart rate variability; means for comparing the
determined heart rate variability to a predetermined target rate
profile; means for adjusting the parameter from a first setting to
a second setting different from the first setting in response to
the comparing of the determined heart rate variability and the
predetermined target rate profile; and means for adjusting the
parameter from the second setting to a termination setting in
response to expiration of a first predetermined time period.
44. A computer readable medium having computer executable
instructions for performing a method comprising: determining heart
rate variability; comparing the determined heart rate variability
to a predetermined target rate profile; adjusting the parameter
from a first setting to a second setting different from the first
setting in response to the comparing of the determined heart rate
variability and the predetermined target rate profile; and
adjusting the parameter from the second setting to a termination
setting in response to expiration of a first predetermined time
period.
Description
RELATED APPLICATION
[0001] This application is a continuation of U.S. patent
application Ser. No. 10/465,351 filed on Jun. 19, 2003, entitled
"METHOD AND APPARATUS FOR TEMPORARILY VARYING A PARAMETER IN AN
IMPLANTABLE MEDICAL DEVICE", to Bakken, et al., incorporated herein
by reference in its entirety.
FIELD OF INVENTION
[0002] The present invention relates generally to implantable
medical devices, and in particular, the present invention relates
to an implantable medical device that provides variations of a
baseline heart rate to reflect activities of daily living and
circadian variation in patients who are sedentary to improve the
strength and functioning of the heart.
BACKGROUND OF THE INVENTION
[0003] Several advances in pacing have occurred over the years by
providing improved methods in sensing natural pacing rhythms. For
instance, in demand pacing devices, the objective is to provide
stimulatory pulses in the absence of the natural heartbeat. That
is, the pacemaker or pacemaker/cardioverter/defibrillator is
designed to deliver a pulse at a fixed rate as long as no natural
heartbeat is sensed. Sensing of the natural frequency of heartbeats
can be done to accommodate changes in the natural pacing frequency
such as during natural rhythms of sleep or exercise.
[0004] Benefits have recently been identified that tend to promote
introducing a circadian variation to the rate-adaptive pacemaker
base rate, i.e., lowering the base heart rate during sleep or
during prolonged periods of inactivity. Several pacemakers or
pacemaker/cardioverter/defibrillator are currently available that
have two basal rates to more closely match diurnal or circadian
heart rate variations (by programming two resting rates). U.S. Pat.
No. 3,921,642 to Preston et al. discusses the advantages of
providing a pacemaker capable of searching for and detecting the
occurrence of natural resting basal heart rates within a
predetermined range. U.S. Pat. No. 3,593,718 and in European Patent
Application No. 0 089 014 describe pacemakers that respond to
changes in respiration rate, for instance during exercise.
Alternate means for sensing physical activity and adjusting the
pacemaker rate accordingly are described in U.S. Pat. No.
4,776,338.
[0005] Clinical evidence is available that tends to show that
patients with decreased heart rate variability die earlier than
those with normal variability and are a predictor of arrhythmic
cardiac death, myocardial infarction, rapid progression of
atheroscerosis and death from heart failure. A possible correlation
has been identified between sedentary lifestyle and risk of
ventricular arrhythmias based on a comparison of occurrences of
ventricular arrhythmias in healthy active vs. sedentary men, and
men with previous myocardial infarction. Accordingly, the greatest
number and highest grades of ventricular arrhythmias during
exercise were found in healthy sedentary men.
[0006] It is also well know that naturally the heart goes through
varied basal rates. For instance, during normal sleep patterns, the
heart rate changes depending on the sleep state (e.g., REM sleep,
etc.). That is, normally the heart rate is not fixed at a
particular rate during sleep.
[0007] There is a growing population of patients having implantable
pacemaker or pacemaker/cardioverter/defibrillator devices who are
largely sedentary and who are therefore likely to be paced at their
basal rate for much of the day, since they are unable to achieve
any measurable amount of exercise on their own. However, since
current adaptive rate pacemakers or
pacemaker/cardioverter/defibrillators are designed to find a range
of natural rhythms occurring in the patient, whether to slow them
during sleep, or to increase the rate during physical activity,
with the goal of sensing and establishing a pacing rate within a
controlled range of preexisting rates, currently available
pacemakers or pacemaker/cardioverter/defibrillators do not address
the benefit of having periods of elevated pacing designed into the
pacemaker, particularly where no natural rhythm for the elevated
pacing rate has been established.
SUMMARY OF THE INVENTION
[0008] The present invention is directed to a method and apparatus
for varying a parameter in an implantable medical device that
includes a plurality of electrodes stimulating heart tissue and
sensing cardiac signals, a timing and control device controlling
the stimulation of heart tissue by the plurality of electrodes and
measuring intervals between the sensed cardiac signals, a storage
device storing the measured intervals, and a microprocessor
determining heart rate variability in response to the stored
intervals, comparing the determined heart rate variability to a
predetermined target rate profile, adjusting the parameter from a
first setting to a second setting different from the first setting
in response to the comparing of the determined heart rate
variability and the predetermined target rate profile, and
adjusting the parameter from the second setting to a termination
setting in response to expiration of a first predetermined time
period.
[0009] According to an embodiment of the present invention, an
implantable medical device includes means for stimulating heart
tissue and sensing cardiac signals, means for controlling timing of
the stimulation of heart tissue and measuring intervals between the
sensed cardiac signals, means for determining heart rate
variability in response to the stored intervals, means for
comparing the determined heart rate variability to a predetermined
target rate profile, means for adjusting the parameter from a first
setting to a second setting different from the first setting in
response to the comparing of the determined heart rate variability
and the predetermined target rate profile, and adjusting the
parameter from the second setting to a termination setting in
response to expiration of a first predetermined time period, and
means for selecting a first exercise time profile from stored
exercise time profiles in response to the comparison of the
determined heart rate variability to the predetermined target rate
profile. Each of the stored exercise time profiles include an
acceleration portion including a second time period and a first
shape corresponding to adjusting the parameter from the first
setting to the second setting, a steady-state portion including a
first value corresponding to the second setting and a second value
corresponding to the first predetermined time period, and a
deceleration portion including a third time period and a second
shape corresponding to adjusting the parameter from the second
setting to the termination setting. The adjusting means adjusts the
parameter from the second setting to the termination setting, prior
to the first predetermined time period, in response to detecting
one of a programming session, a magnet, a cardiac arrhythmia,
spontaneous rate greater than the second setting, and rate response
greater than the second setting.
BRIEF DESCRIPTION OF THE DRAWINGS
[0010] Other advantages and features of the present invention will
be readily appreciated as the same becomes better understood by
reference to the following detailed description when considered in
connection with the accompanying drawings, in which like reference
numerals designate like parts throughout the figures thereof and
wherein:
[0011] FIG. 1 is a schematic diagram of a
pacemaker/cardioverter/defibrillator and lead set of a type in
which the present invention may usefully be practiced;
[0012] FIG. 2 is a schematic diagram of a cardiac pacemaker of a
type appropriate for use in practicing the present invention in
conjunction with its associated lead system, illustrated in
relation to a patient's heart;
[0013] FIG. 3 is a functional schematic diagram of an implantable
pacemaker/cardioverter/defibrillator of the type illustrated in
FIG. 1, in which the present invention may usefully be
practiced;
[0014] FIG. 4 is a functional schematic diagram of the pacemaker
120 illustrated in FIG. 2;
[0015] FIG. 5 is a plan view of an external programmer of a sort
appropriate for use in conjunction with the practice of the present
invention in conjunction with any of the devices of FIGS. 1 and
2;
[0016] FIG. 6 is a functional schematic of a programmer as
illustrated in FIG. 5 appropriate for use in conjunction with the
invention;
[0017] FIG. 7 is a schematic diagram of a patient activator of the
type which may be employed with the present invention;
[0018] FIG. 8 is a block functional diagram of a patient activator
of the type for use in conjunction with the present invention;
[0019] FIG. 9 is a flowchart of a method for varying a pacing rate
in an implantable medical device according to the present
invention;
[0020] FIG. 10A is a graphical representation of an example of a
histogram generated in accordance with the present invention;
[0021] FIG. 10B is a graphical representation of an exemplary
target rate profile stored in an implantable medical device
according to the present invention;
[0022] FIGS. 11A-11F are graphical representations of exemplary
exercise time profiles according to the present invention; and
[0023] FIG. 12 is a flowchart of a method for varying a pacing rate
in an implantable medical device according to the present
invention.
DETAILED DESCRIPTION OF THE INVENTION
[0024] FIG. 1 is a schematic diagram of a
pacemaker/cardioverter/defibrillator and lead set of a type in
which the present invention may usefully be practiced. The
ventricular lead includes an elongated insulative lead body 16,
carrying three mutually insulated conductors. Located adjacent the
distal end of the lead are a ring electrode 24, an extendable helix
electrode 26, mounted retractably within an insulative electrode
head 28, and an elongated coil electrode 20. Each of the electrodes
is coupled to one of the conductors within the lead body 16.
Electrodes 24 and 26 are employed for cardiac pacing and for
sensing ventricular depolarizations. At the proximal end of the
lead is a bifurcated connector 14, which carries three electrical
connectors, each coupled to one of the coiled conductors.
[0025] The atrial/SVC lead includes an elongated insulative lead
body 15, also carrying three mutually insulated conductors. Located
adjacent the J-shaped distal end of the lead are a ring electrode
21 and an extendible helix electrode 17, mounted retractably within
an insulative electrode head 19. Each of the electrodes is coupled
to one of the conductors within the lead body 15. Electrodes 17 and
21 are employed for atrial pacing and for sensing atrial
depolarizations. An elongated coil electrode 23 is provided,
proximal to electrode 21 and coupled to the third conductor within
the lead body 15. At the proximal end of the lead is a bifurcated
connector 13, which carries three electrical connectors, each
coupled to one of the coiled conductors.
[0026] The coronary sinus lead includes an elongated insulative
lead body 6, carrying one conductor, coupled to an elongated coiled
defibrillation electrode 8. Electrode 8, illustrated in broken
outline, is located within the coronary sinus and great vein of the
heart. At the proximal end of the lead is a connector plug 4 that
carries an electrical connector, coupled to the coiled
conductor.
[0027] The pacemaker/cardioverter/defibrillator 10 includes a
hermetic enclosure 11 containing the electronic circuitry used for
generating cardiac pacing pulses for delivering cardioversion and
defibrillation shocks and for monitoring the patient's heart
rhythm. Pacemaker/cardioverter/defibrillator 10 is shown with the
lead connector assemblies 4, 13 and 14 inserted into the connector
block 12, which serves as a receptacle and electrical connector for
receiving the connectors 4, 13 and 14 and interconnecting the leads
to the circuitry within enclosure 11. A sensor 30 is illustrated
schematically by broken outline, and may include one or more of an
activity sensor, respiration sensor (potentially from impedance),
accelerometer-based posture detector, heart rate detector, ischemia
detector and other available physiological sensor known in the art
for measuring heart hemodynamics and may be a piezoelectric
transducer as known in the art. Sensor 30 may be used for
regulation of pacing rate based upon demand for cardiac output and
is utilized to provide variations of a baseline heart rate to
reflect activities of daily living and circadian variation in
patients who are sedentary and unable to exercise to improve the
strength and functioning of the heart, as described below.
[0028] Optionally, insulation of the outward facing portion of the
housing 11 of the pacemaker/cardioverter/defibrillator 10 may be
provided or the outward facing portion may instead be left
uninsulated, or some other division between insulated and
uninsulated portions may be employed. The uninsulated portion of
the housing 11 optionally serves as a subcutaneous defibrillation
electrode, used to defibrillate either the atria or ventricles.
Other lead configurations and electrode locations may of course be
substituted for the lead set illustrated. For example, atrial
defibrillation and sensing electrodes might be added to either the
coronary sinus lead or the right ventricular lead instead of being
located on a separate atrial lead, allowing for a two lead
system.
[0029] FIG. 2 is a schematic diagram of a cardiac pacemaker of a
type appropriate for use in practicing the present invention in
conjunction with its associated lead system, illustrated in
relation to a patient's heart. The pacemaker 120 includes a
hermetic enclosure 124 containing the electronic circuitry used for
generating cardiac pacing pulses and for monitoring the patient's
heart rhythm. An activity sensor 126 is illustrated schematically
by broken outline, and may include one or more of an activity
sensor, respiration sensor (potentially from impedance),
accelerometer-based posture detector, heart rate detector, ischemia
detector and other available physiological sensor known in the art
for measuring heart hemodynamics and may be a piezoelectric
transducer as known in the art as discussed above in conjunction
with FIG. 1. Mounted to the enclosure 124 is a header 122 which
serves as a receptacle and electrical connector for receiving the
connectors 132 and 134 of pacing leads 128 and 130 and
interconnecting the leads to the circuitry within enclosure 124.
Lead 128 is a ventricular lead provided with electrodes 140 and 142
for monitoring right ventricular heart signals. Also illustrated on
lead 128 is a physiologic sensor 144, which may optionally be
included in addition to or as an alternative to sensor 126, and
which may take the form of an activity sensor, respiration sensor
(potentially from impedance), accelerometer-based posture detector,
heart rate detector, ischemia detector and other available
physiological sensor known in the art for measuring heart
hemodynamics and may be a piezoelectric transducer as known in the
art as discussed above in conjunction with FIG. 1. One or both of
sensors 126 and 144 can be utilized alone or in combination for
rate responsive pacing and to provide variations of a baseline
heart rate to reflect activities of daily living and circadian
variation in patients who are sedentary and unable to exercise to
improve the strength and functioning of the heart, as described
below. Atrial lead 130 carries electrodes 136 and 138 and is
employed for sensing and pacing the patient's atrium.
[0030] FIG. 3 is a functional schematic diagram of an implantable
pacemaker/cardioverter/defibrillator of the type illustrated in
FIG. 1, in which the present invention may usefully be practiced.
This diagram should be taken as exemplary of one type of
anti-tachyarrhythmia device in which the invention may be embodied,
and not as limiting, as it is believed that the invention may
usefully be practiced in a wide variety of device implementations,
including devices providing therapies for treating atrial
arrhythmias instead of or in addition to ventricular arrhythmias,
cardioverters and defibrillators which do not provide
anti-tachycardia pacing therapies, anti-tachycardia pacers which do
not provide cardioversion or defibrillation, and devices which
deliver different forms of anti-arrhythmia therapies such nerve
stimulation or drug administration.
[0031] The device is provided with a lead system including
electrodes, which may be as illustrated in FIG. 1. Alternate lead
systems may of course be substituted. If the electrode
configuration of FIG. 1 is employed, the correspondence to the
illustrated electrodes is as follows. Electrode 311 corresponds to
an electrode formed along the uninsulated portion of the housing of
the implantable pacemaker/cardioverter/defibrillator. Electrode 320
corresponds to electrode 20 and is a defibrillation electrode
located in the right ventricle. Electrode 310 corresponds to
electrode 8 and is a defibrillation electrode located in the
coronary sinus. Electrode 318 corresponds to electrode 28 and is a
defibrillation electrode located in the superior vena cava.
Electrodes 324 and 326 correspond to electrodes 24 and 26, and are
used for sensing and pacing in the ventricle. Electrodes 317 and
321 correspond to electrodes 19 and 21 and are used for pacing and
sensing in the atrium.
[0032] Electrodes 310, 311, 318 and 320 are coupled to high voltage
output circuit 234. Electrodes 324 and 326 are coupled to the
R-wave amplifier 200, which preferably takes the form of an
automatic gain controlled amplifier providing an adjustable sensing
threshold as a function of the measured R-wave amplitude. A signal
is generated on R-out line 202 whenever the signal sensed between
electrodes 324 and 326 exceeds the present sensing threshold.
[0033] Electrodes 317 and 321 are coupled to the P-wave amplifier
204, which preferably also takes the form of an automatic gain
controlled amplifier providing an adjustable sensing threshold as a
function of the measured R-wave amplitude. A signal is generated on
P-out line 206 whenever the signal sensed between electrodes 317
and 321 exceeds the present sensing threshold. The general
operation of the R-wave and P-wave amplifiers 200 and 204 may
correspond to that disclosed in U.S. Pat. No. 5,117,824, by Keimel,
et al., issued Jun. 2, 1992, for an Apparatus for Monitoring
Electrical Physiologic Signals, incorporated herein by reference in
its entirety. However, any of the numerous prior art sense
amplifiers employed in implantable cardiac pacemakers,
defibrillators and monitors may also usefully be employed in
conjunction with the present invention.
[0034] Switch matrix 208 is used to select which of the available
electrodes are coupled to wide band amplifier 210 for use in
digital signal analysis. Selection of electrodes is controlled by
the microprocessor 224 via data/address bus 218, which selections
may be varied as desired. Signals from the electrodes selected for
coupling to bandpass amplifier 210 are provided to multiplexer 220,
and thereafter converted to multi-bit digital signals by A/D
converter 222, for storage in random access memory 226 under
control of direct memory access circuit 228. Microprocessor 224 may
employ digital signal analysis techniques to characterize the
digitized signals stored in random access memory 226 to recognize
and classify the patient's heart rhythm employing any of the
numerous signal processing methodologies known to the art.
[0035] Telemetry circuit 330 receives downlink telemetry from and
sends uplink telemetry to the patient activator by means of antenna
332. Data to be uplinked to the activator and control signals for
the telemetry circuit are provided by microprocessor 224 via
address/data bus 218. Received telemetry is provided to
microprocessor 224 via multiplexer 220. The atrial and ventricular
sense amp circuits 200, 204 produce atrial and ventricular EGM
signals which also may be digitized and uplink telemetered to an
associated programmer on receipt of a suitable interrogation
command. The device may also be capable of generating so-called
marker codes indicative of different cardiac events that it
detects. A pacemaker with marker-channel capability is described,
for example, in U.S. Pat. No. 4,374,382 to Markowitz, incorporated
by reference herein in its entirety. The particular telemetry
system employed is not critical to practicing the invention, and
any of the numerous types of telemetry systems known for use in
implantable devices may be used. In particular, the telemetry
systems as disclosed in U.S. Pat. No. 5,292,343 issued to
Blanchette et al., U.S. Pat. No. 5,314,450, issued to Thompson,
U.S. Pat. No. 5,354,319, issued to Wyborny et al. U.S. Pat. No.
5,383,909, issued to Keimel, U.S. Pat. No. 5,168,871, issued to
Grevious, U.S. Pat. No. 5,107,833 issued to Barsness or U.S. Pat.
No. 5,324,315, issued to Grevious, all incorporated herein by
reference in their entireties, are suitable for use in conjunction
with the present invention. However, the telemetry systems
disclosed in the various other patents cited herein which are
directed to programmable implanted devices, or similar systems may
also be substituted. The telemetry circuit 330 is of course also
employed for communication to and from an external programmer, as
is conventional in implantable anti-arrhythmia devices.
[0036] The device of FIG. 3 includes an activity sensor 344,
mounted to the interior surface of the device housing or to the
hybrid circuit within the device housing and corresponds to sensor
30 of FIG. 1. The sensor 344 and sensor present in circuitry 342
may be employed in the conventional fashion described in U.S. Pat.
No. 4,428,378 issued to Anderson et al, incorporated herein by
reference in its entirety, to regulate the underlying pacing rate
of the device in rate responsive pacing modes. In addition, sensor
and circuitry 342 are utilized to provide variations of a baseline
heart rate to reflect activities of daily living and circadian
variation in patients who are sedentary and unable to exercise to
improve the strength and functioning of the heart, as described
below.
[0037] The remainder of the circuitry is dedicated to the provision
of cardiac pacing, cardioversion and defibrillation therapies, and,
for purposes of the present invention may correspond to circuitry
known in the prior art. An exemplary apparatus is disclosed for
accomplishing pacing, cardioversion and defibrillation functions as
follows. The pacer timing/control circuitry 212 includes
programmable digital counters which control the basic time
intervals associated with DDD, WI, DVI, VDD, MI, DDI, DDDR, VVIR,
DVIR, VDDR, MIR, DDIR and other modes of single and dual chamber
pacing well known to the art. Circuitry 212 also controls escape
intervals associated with anti-tachyarrhythmia pacing in both the
atrium and the ventricle, employing, any anti-tachyarrhythmia
pacing therapies known to the art.
[0038] Intervals defined by pacing circuitry 212 include atrial and
ventricular pacing escape intervals, the refractory periods during
which sensed P-waves and R-waves are ineffective to restart timing
of the escape intervals and the pulse widths of the pacing pulses.
The durations of these intervals are determined by microprocessor
224, in response to stored data in memory 226 and are communicated
to the pacing circuitry 212 via address/data bus 218. Pacer
circuitry 212 also determines the amplitude of the cardiac pacing
pulses under control of microprocessor 224.
[0039] During pacing, the escape interval counters within pacer
timing/control circuitry 212 are reset upon sensing of R-waves and
P-waves as indicated by signals on lines 202 and 206, and in
accordance with the selected mode of pacing on time-out trigger
generation of pacing pulses by pacer output circuits 214 and 216,
which are coupled to electrodes 317, 321, 324 and 326. The escape
interval counters are also reset on generation of pacing pulses,
and thereby control the basic timing of cardiac pacing functions,
including anti-tachyarrhythmia pacing.
[0040] The durations of the intervals defined by the escape
interval timers are determined by microprocessor 224, via
data/address bus 218. The value of the count present in the escape
interval counters when reset by sensed R-waves and P-waves may be
used to measure the durations of R-R intervals, P-P intervals, PR
intervals and R-P intervals, which measurements are stored in
memory 226 and are used in conjunction with the present invention
to measure heart rate variability and in conjunction with
tachyarrhythmia detection functions.
[0041] Microprocessor 224 operates as an interrupt driven device,
and is responsive to interrupts from pacer timing/control circuitry
212 corresponding to the occurrences of sensed P-waves and R-waves
and corresponding to the generation of cardiac pacing pulses. These
interrupts are provided via data/address bus 218. Any necessary
mathematical calculations to be performed by microprocessor 224 and
any updating of the values or intervals controlled by pacer
timing/control circuitry 212 take place following such interrupts.
Microprocessor 224 includes associated ROM in which the stored
program controlling its operation as described below resides. A
portion of the memory 226 may be configured as a plurality of
recirculating buffers, capable of holding series of measured
intervals, which may be analyzed in response to the occurrence of a
pace or sense interrupt to determine whether the patient's heart is
presently exhibiting atrial or ventricular tachyarrhythmia.
[0042] The arrhythmia detection method of the present invention may
include any of the numerous available prior art tachyarrhythmia
detection algorithms. One preferred embodiment may employ all or a
subset of the rule-based detection methods described in U.S. Pat.
No. 5,545,186 issued to Olson et al. or in U.S. Pat. No. 5,755,736
issued to Gillberg et al., both incorporated herein by reference in
their entireties. However, any of the various arrhythmia detection
methodologies known to the art might also usefully be employed in
alternative embodiments of the invention.
[0043] In the event that an atrial or ventricular tachyarrhythmia
is detected, and an anti-tachyarrhythmia pacing regimen is desired,
timing intervals for controlling generation of anti-tachyarrhythmia
pacing therapies are loaded from microprocessor 224 into the pacer
timing and control circuitry 212, to control the operation of the
escape interval counters therein and to define refractory periods
during which detection of R-waves and P-waves is ineffective to
restart the escape interval counters.
[0044] In the event that generation of a cardioversion or
defibrillation pulse is required, microprocessor 224 employs the
escape interval counter to control timing of such cardioversion and
defibrillation pulses, as well as associated refractory periods. In
response to the detection of atrial or ventricular fibrillation or
tachyarrhythmia requiring a cardioversion pulse, microprocessor 224
activates cardioversion/defibrillation control circuitry 230, which
initiates charging of the high voltage capacitors 246, 248 via
charging circuit 236, under control of high voltage charging
control line 240. The voltage on the high voltage capacitors is
monitored via VCAP line 244, which is passed through multiplexer
220 and in response to reaching a predetermined value set by
microprocessor 224, results in generation of a logic signal on Cap
Full (CF) line 254, terminating charging. Thereafter, timing of the
delivery of the defibrillation or cardioversion pulse is controlled
by pacer timing/control circuitry 212. Following delivery of the
fibrillation or tachycardia therapy the microprocessor then returns
the device to cardiac pacing and awaits the next successive
interrupt due to pacing or the occurrence of a sensed atrial or
ventricular depolarization. In the illustrated device, delivery of
the cardioversion or defibrillation pulses is accomplished by
output circuit 234, under control of control circuitry 230 via
control bus 238. Output circuit 234 determines whether a monophasic
or biphasic pulse is delivered, whether the housing 311 serves as
cathode or anode and which electrodes are involved in delivery of
the pulse.
[0045] FIG. 4 is a functional schematic diagram of the pacemaker
120 illustrated in FIG. 2. The pacemaker of FIGS. 2 and 4 is
essentially a set of subcomponents of the implantable
pacemaker/cardioverter/defibrillator illustrated in FIGS. 1 and 3.
Like the device of FIG. 3, the pacemaker is a microprocessor
controlled device with microprocessor 189 operating under control
of programming stored in Read Only Memory (ROM) 191. In the device
as illustrated, electrodes 136 and 138, intended for location in
the atrium of the patient's heart are coupled to an atrial
amplifier 181 which may correspond to atrial amplifier 204 in FIG.
3. Similarly, ventricular electrodes 140 and 142 are coupled to
ventricular amplifier 182, which may correspond to ventricular
amplifier 200 in FIG. 3. The outputs of atrial and ventricular
amplifiers 181 and 182 are input into timing and control circuitry
183 which conforms generally to the pacer timing and control
circuitry 212 of FIG. 3, and which measures intervals between
detected depolarizations and controls intervals between delivered
pacing pulses as well as generating interrupts via data/address 192
to awake microprocessor 189 in response to delivery of a pacing
pulse or sensing of a cardiac depolarization. Intervals between
depolarizations measured by timing control circuitry 183 are stored
in Random Access Memory (RAM) 190 until processed by microprocessor
189 to derive average heart rate values. Atrial and ventricular
pacing pulses delivered according to one or more of the standard
pacing modes described in conjunction with FIG. 3 are produced by
atrial and ventricular pulse generator circuits 184 and 185 which
may correspond to pulse generator circuits 214 and 216 in FIG. 3.
In addition, timing and control circuitry 183 includes a clock 180
used for determining when to perform an escape rate variation
session according to the present invention, as described below.
[0046] The sensor illustrated in FIG. 4 may correspond to either an
activity sensor 126 as described in conjunction with FIG. 2 above
or to a hemodynamic sensor 140, as described in conjunction with
FIG. 2. If the sensor is an activity sensor, then sensor processing
circuitry 186 may correspond to sensor processing circuitry 342
discussed in conjunction with FIG. 3. However, if the sensor is a
hemodynamic sensor, the sensor processing circuitry would
correspond to the sort of processing circuitry typically associated
with hemodynamic sensors. Telemetry circuitry 187 in conjunction
with antenna 188 serves to transmit information to and receive
information from an external programmer as described above in
conjunction with the device of FIG. 3, including information
related to stored median interval values and heart rate variability
measurements in RAM 190, as calculated by microprocessor 189.
[0047] FIG. 5 is a plan view of an external programmer of a sort
appropriate for use in conjunction with the practice of the present
invention in conjunction with any of the devices of FIGS. 1 and 2.
The programmer 420 is a microprocessor controlled device which is
provided with a programming head 422 for communicating with an
implanted device, a set of surface electrogram electrodes 459 for
monitoring a patient's electrogram, a display 455 which is
preferably a touch sensitive display, control buttons or keys 465,
and a stylist 456 for use in conjunction with the touch sensitive
screen 455. By means of the control keys 465 and the touch
sensitive screen 455 and stylus 456, the physician may format
commands for transmission to the implantable device. By means of
the screen 455, the physician may observe information telemetered
from the implantable device, including diagnostic information such
as sessions that were initiated, the time that they were initiated,
and whether they terminated upon normal completion of the session
or prior to completion of the session in response to a termination
event, as described below.
[0048] The programmer is further provided with a printer 463 which
allows for hard copy records of displays of signals received from
the implanted device such as electrograms, stored parameters,
programmed parameters, and information as to heart rate variability
and heart rate trends and other diagnostic information. While not
visible in this view, the device may also be provided with a floppy
disk or CD ROM drive and/or a port for insertion of expansion cards
such as P-ROM cartridges, to allow for software upgrades and
modifications to the programmer 420.
[0049] In the context of the present invention, programmer 420 may
serve simply as an input device, a display device, displaying
information with regard to heart rate variability as calculated by
the implanted device or instead may receive uplinked raw data
related to heart intervals and may calculate the heart rate trends
and heart rate variability values according to the present
invention. It is believed that it is preferable for the implanted
device to perform the bulk of the computations necessary to
practice the invention, and in particular that it is preferable for
the implanted device to at least calculate median rate values, to
reduce the storage requirements within the implanted device.
However, allocation of functions between the implanted device and
the programmer may differ from the preferred embodiments and still
result in a workable system.
[0050] FIG. 6 is a functional schematic of a programmer as
illustrated in FIG. 5 appropriate for use in conjunction with the
invention. Programmer 420 is a personal computer type,
microprocessor-based device incorporating a central processing unit
450, which may be, for example, an Intel 80386 or 80486 or Pentium
microprocessor or the like. A system bus 451 interconnects CPU 450
with a hard disk drive 452 storing operational programs and data
and with a graphics circuit 453 and an interface controller module
454. A floppy disk drive 466 or a CD ROM drive is also coupled to
bus 451 and is accessible via a disk insertion slot within the
housing of the programmer 420. Programmer 420 further includes an
interface module 457, which includes digital circuit 458,
non-isolated analog circuit 459, and isolated analog circuit 460.
Digital circuit 448 enables interface module 457 to communicate
with interface controller module 454.
[0051] In order for the physician or other caregiver or user to
communicate with the programmer 420, control buttons 465 or
optionally a keyboard coupled to CPU 50 are provided. However the
primary communication mode is through graphics display screen 455
of the well-known "touch sensitive" type controlled by graphics
circuit 453. A user of programmer 420 may interact therewith
through the use of a stylus 456, also coupled to graphics circuit
453, which is used to point to various locations on screen 455,
which display menu choices for selection by the user or an
alphanumeric keyboard for entering text or numbers and other
symbols.
[0052] Graphics display 455 also displays a variety of screens of
telemetered out data or real time data including measurements of
heart rate variability and heart rate trends according to the
present invention. Programmer 420 is also provided with a strip
chart printer 463 or the like coupled to interface controller
module 454 so that a hard copy of a patient's ECG, EGM, marker
channel or of graphics displayed on the display 455 can be
generated.
[0053] As will be appreciated by those of ordinary skill in the
art, it is often desirable to provide a means for programmer 420 to
adapt its mode of operation depending upon the type or generation
of implanted medical device to be programmed. Accordingly, it may
be desirable to have an expansion cartridge containing EPROMs or
the like for storing software programs to control programmer 420 to
operate in a particular manner corresponding to a given type or
generation of implantable medical device. In addition, in
accordance with the present invention, it is desirable to provide
the capability through the expansion cartridge or through the
floppy disk drive 66 or CD ROM drive.
[0054] The non-isolated analog circuit 459 of interface module 457
is coupled to a programming head 422 which is used to establish the
uplink and downlink telemetry links between the pacemaker 410 and
programmer 420 as described above. Uplink telemetered EGM signals
are received in programming head 422 and provided to non-isolated
analog circuit 459. Non-isolated analog circuit 459, in turn,
converts the digitized EGM signals to analog EGM signals and
presents these signals on output lines A EGM OUT and V EGM OUT.
These output lines may then be applied to a strip-chart recorder
463 to provide a hard-copy printout of the A EGM or V EGM for
viewing by the physician. Similarly, the markers be received by
programming head 422 are presented on the MARKER CHANNEL output
line from non-isolated analog circuit 459.
[0055] Isolated analog circuit 460 in interface module 547 is
provided to receive external ECG and electrophysiologic (EP)
stimulation pulse signals. In particular, analog circuit 460
receives ECG signals from patient skin electrodes 459 and processes
these signals before providing them to the remainder of the
programmer system in a manner well known in the art. Circuit 460
further operates to receive the EP stimulation pulses from an
external EP stimulator for the purposes of non-invasive EP studies,
as is also known in the art.
[0056] In order to ensure proper positioning of programming head
422 over the antenna of the associated implanted device, feedback
is provided to the physician that the programming head 422 is in
satisfactory communication with and is receiving sufficiently
strong RF signals. This feedback may be provided, for example, by
means of a head position indicator, e.g. a light-emitting diode
(LED) or the like that is lighted to indicate a stable telemetry
channel.
[0057] FIG. 7 is a schematic diagram of a patient activator of the
type which may be employed with the present invention. The
activator 300, which is similar to the patient activator described
in U.S. Pat. No. 5,836,975 to DeGroot, incorporated herein by
reference in its entirety, generally takes the form of a plastic
enclosure provided with a push button 302 by which the patient may
request delivery of predefined patient-initiated therapy, including
the escape rate variation therapy of the present invention
described in detail below. The device is battery powered, employing
batteries accessible by means of the battery cover 304. On the
reverse side of the device, not visible, are two indicator lights,
one green, one amber, which are used to provide information to the
patient with regard to the status and functioning of the
patient-initiated therapy.
[0058] FIG. 8 is a block functional diagram of a patient activator
of the type for use in conjunction with the present invention. This
device corresponds generally to patient activators presently
available commercially for use in conjunction with implanted
Medtronic pacemakers, and in particular, corresponds generally to
the Medtronic Model-9462 patient activator presently in commercial
distribution for use in conjunction with implanted bradycardia
pacers. Control functions are provided by microprocessor 308, based
upon programming stored in its associated read-only memory located
therein. Microprocessor 308 provides output signals for producing
audible patient alert signals by means of driver 310 and speaker
312. Microprocessor 308 also provides control signals to LED driver
314 to power the associated amber and green colored LEDs 316,
referred to above. The device is powered by a battery 318 which is
coupled to the microprocessor 308 by means of
power/switching/battery monitor circuitry 320, which also provides
the microprocessor with an indication that push button 322 has been
pressed.
[0059] Communication with microprocessor 308 is accomplished by
means of the antenna driver/switching circuit 324, the receiver
demodulator 326 and RF antenna 328. Transmissions from the
implanted device are received by antenna 328, and are demodulated
by receiver demodulator 326 to be provided to the microprocessor
189 (FIG. 4) via antenna 188. In response to received transmissions
from the implanted device, the microprocessor controls operation of
the audio and light drivers 310 and 314 to indicate the nature of
the communication received. Transmissions to the implanted device,
for example, in response to activation of the push button 302 are
provided by microprocessor 308 to the antenna drive/switching
circuit, which then communicates with the implanted device by means
of antenna 328.
[0060] FIG. 9 is a flowchart of a method for varying a parameter in
an implantable medical device according to the present invention.
Although the method for varying a parameter in an implantable
medical device illustrated in FIG. 9 is being described as being
utilized in cardiac pacemaker 120, it is understood that the method
of varying a parameter of the present invention is not intended to
be limited to use in pacemaker 120, and could similarly be employed
in other implantable medical devices, such as
pacemaker/cardioverter/defibrillator 10, for example.
[0061] As illustrated in FIGS. 4 and 9, at some point subsequent to
implant of the implantable medical device 120, information
regarding the patient, such as coronary artery disease status,
heart failure status, date of birth, sex, age, time of day to
initiate the escape rate variation method of the present invention,
and whether to turn the rate variation feature of the present
invention ON or OFF, for example, in addition to other programmable
features described below, is input by a physician or clinician,
Step 500, via programmer 420. Once the patient information is
initiated and the rate variation feature is turned ON,
microprocessor 189 determines whether a programmable predetermined
time period since the last generation of a histogram was performed
has expired, Step 502.
[0062] The programmable time period utilized in Step 502
corresponds to the amount of time between generated histograms and
should be chosen based on the desired time of day and number of
times that the rate variation featured is intended to be initiated.
Once the predetermined time period since the last generated
histogram has expired, microprocessor 189 generates a histogram of
the patient's heart rate, Step 504, described below in reference to
FIGS. 10A and 10B, restarts the predetermined time period utilized
in Step 502, and determines whether an initiation delay has
expired, Step 506. During the initiation delay, application of the
parameter variation feature of the present invention is delayed for
a predetermined period of time following programming of the device
in Step 500 in order for the device to accumulate heart rate data
over the predetermined time period and to establish consistency in
the accumulated heart rate data over the time period.
[0063] Once the rate variation feature initiation delay has
expired, microprocessor 189 determines that it is time to initiate
a session of the escape rate variation of the present invention in
response to a patient activation request being received from
patient activator 300 (FIG. 7), or an indication from clock 180
that it is the programmed time of day for initiating the parameter
variation of the present invention, Step 508. According to the
present invention, the specific number of times and times of the
day at which the escape rate variation therapy is to be employed is
programmable, and therefore can be set at any desired value, such
as two or three times a day, including a morning, afternoon and
evening session, for example.
[0064] Once it is determined that it is time to initiate a session
of the escape rate variation of the present invention,
microprocessor 189 compares the most recent generated histogram to
a predetermined target rate profile stored in ROM 191, Step
510.
[0065] A histogram presents heart activity data represented by
sensed QRS complexes obtained over a period of time in a compact
manner, wherein successive intervals between R-waves are computed
and classified as a heart rate associated with that interval. FIG.
10A is a graphical representation of an example of a histogram
generated in accordance with the present invention. FIG. 10B is a
graphical representation of a corresponding exemplary target rate
profile stored in an implantable medical device for comparison with
the graphical representation of FIG. 10A, according to the present
invention. As illustrated in FIGS. 10A and 10B, the x-axis of the
graphical display is divided into bins 600, 602 corresponding to a
range of beats per minute (BPM) for the R-R intervals, whereas the
y-axis provides the percentage of time that the patient's heart
rate is within each bin. As each ECG complex is detected over a
predetermined time period, the rate in beats per minute is
determined, and the percentage of time in the appropriate bin 600
is updated.
[0066] It is understood that the present invention is not intended
to be limited to generating a histogram based on percentage of time
the patient's heart rate is within a given bin, but rather is
intended to include displaying the patient's heart rate in terms of
quantities other than the percentage of time. For example, a rate
profile may be determined using the number of beats occurring in
each bin, rather than the percentage of time the heart rate is
within each range (bin).
[0067] Since patients having an implantable medical device
utilizing the escape rate variation of the present invention are
typically sedentary, such as patients who are elderly,
wheelchair-bound, bed-ridden or likely to spend a majority of the
day being paced by the implantable device at the lower or basal
rate programmed in the device, the initial generated histogram in
such patients will tend to appear as shown in FIG. 10A, with the
patient heart rate being very close to the programmed lower pacing
rate, i.e., between approximately 60-70 beats per minute, over a
large percentage of the time. Such patients typically experience no
change or minimal change in their heart rate for an extended period
of time. In addition, circadian variations in such patients tend to
be far less compared to normal, or non-sedentary patients.
[0068] On the other hand, as illustrated in FIG. 10B, the patient
heart rate is ideally more evenly distributed over the range of
heart rates of the target rate profile, with the percentage of time
that the heart rate is within the 60-70 beat per minute range being
approximately 30 percent, for example. It is understood that the
heart rate percentage values corresponding to the target rate
profile stored in ROM 191 are programmable and can be set at any
desired distribution in addition to the specific distribution
illustrated by example in FIG. 10B. Accordingly, the escape rate
variation feature of the present invention is not intended to be
limited specifically to the target rate profile as illustrated in
FIG. 10B, but rather, includes any desired target rate profile.
[0069] Returning to FIGS. 4 and 9, based on the comparison of the
generated histogram and the predetermined target rate profile (FIG.
10B) stored in ROM 191, Step 510, microprocessor 189 determines
whether a session of the rate variation feature would be
appropriate, Step 512. If the session would not be appropriate, the
process returns to Step 502, and microprocessor 189 generates an
updated histogram after waiting the predetermined time period, and
repeats the comparison of the updated histogram with the target
rate profile, Steps 502-512. For example, as illustrated in FIGS.
10A and 10B, a session of the rate variation feature of the present
invention would be determined to be inappropriate in Step 512 in
response to the value of the indicated percent of time that the
patient's heart rate within one or more or all of heart rate bins
600 of the generated histogram is approximately equal to
corresponding heart rate bins 602 of the target profile rate
histogram. On the other hand, a session of the rate variation
feature of the present invention would be determined to be
appropriate in Step 512 in response to the value of the indicated
percent of time that the patient's heart rate within one or more or
all of heart rate bins 600 of the generated histogram is less than
corresponding heart rate bins 602 of the target profile rate
histogram.
[0070] According to the present invention, the step of determining
whether a session of the rate variation feature would be
appropriate, Step 512, may include determining whether there is a
constant heart rate or a minimal change in heart rate variations
over a period of time, such as four hours, for example. The period
of time utilized for determining the constant heart rate or minimal
change in heart rate variation is not intended to be limited to
four hours, but is programmable and may include any desired period
of time that is most appropriate for the specific patient or
condition. In this way, the session is initiated when the heart
rate is at a constant rate or is less than a predetermined value in
order to introduce variability in the heart rate.
[0071] Returning again to FIGS. 4 and 9, once it is determined that
a session of the escape rate variation feature of the present
invention would be appropriate, microprocessor 189 selects an
exercise time profile from exercise time profiles stored in ROM
191, Step 514. FIGS. 11A and 11B are graphical representations of
exemplary exercise time profiles according to the present
invention. According to the present invention, exercise time
profile portion of ROM 191 contains information corresponding to
specific time domain rate profiles relating to variations in the
pacing rate to simulate numerous exercises, for example, and which
are appropriate for specific patients based on factors such as the
patient's sex and age. According to an embodiment of the present
invention, the exercise rate profile portion includes a number of
age appropriate programmable time profiles that vary the pacing
rate of the device for a predetermined time period in an attempt to
simulate activities of daily living (ADL), such as walking for
example, in addition to a number of age appropriate programmable
time profiles that vary the pacing rate of the device for a
predetermined time period in an attempt to simulate more vigorous
exercise. For each available stored exercise rate profile, once the
exercise rate profile is selected, microprocessor 189 increases the
lower pacing rate of the device from the programmed lower pacing
rate to a corresponding exercise simulation rate, indicated by the
time profile for that exercise rate profile, for a predetermined
period of time to simulate the effects of exercise activity on the
patient's heart.
[0072] For example, as illustrated in FIG. 11A, in order to
simulate an activity of daily living (ADL) time profile,
microprocessor 189 increases the programmed lower pacing rate LR to
an ADL exercise simulation rate, such as 85 beats per minute, for
example, for a predetermined time period, after which the rate is
reduced back to the original lower rate LR. In the same way, as
illustrated in FIG. 11B, in order to simulate a more vigorous
exercise time profile, microprocessor 189 increases the lower
pacing rate LR to a more vigorous exercise simulation rate, such as
120 beats per minute, for example, for a predetermined time period,
after which the rate is reduced to the original lower rate LR.
[0073] As illustrated in FIGS. 11A and 11B, each exercise time
profile includes a rate acceleration portion 604, corresponding to
a period of time T1 and a shape S1 corresponding to the rate at
which the pacing rate is increased from the lower rate LR to an
exercise simulation rate 610, a steady-state portion 606,
corresponding to a length of time T2 that the exercise simulation
rate 610 is maintained, and a rate deceleration portion 608,
corresponding to a period of time T3 and a shape S2 corresponding
to the rate at which the pacing rate is decreased from the exercise
simulation rate 610 to an exercise time profile termination
setting, such as a spontaneous rate, a rate response rate, or the
lower rate LR. While shape S1 and shape S2 are shown in FIGS. 11A
and 11B as being linear, shape S1 and shape S2 could also have a
convex, concave, sigmoidal, saw tooth, or stair step shape.
[0074] The values of exercise simulation rate 610, rate
acceleration portion 604, steady-state portion 606 and rate
deceleration portion 608 are patient dependent and are programmed
into the device by the clinician or physician, including such
factors as the age and sex of the patient, initially, and may
include other factors, such as the generated histograms and length
of time that the rate variation feature has been performed, as
described below. For example, as illustrated in the exemplary time
profile illustrated in FIG. 11A, times T1, T2 and T3 are initially
5 minutes, and shapes S1 and S2 are linear as indicated.
[0075] Returning again to FIGS. 4 and 9, once the exercise time
profile is chosen, microprocessor 189 determines whether the target
profile rate would be exceeded if the selected exercise time
profile is initiated by the device, Step 516, by determining
whether one or more or all bins 600 of the generated histogram
would exceed the corresponding one or more or all of bins 602 of
the target rate profile. If the target profile rate would be
exceeded, microprocessor 189 determines whether all available
stored exercise time profiles have been exhausted, Step 518, and if
not, selects another exercise time profile, step 514, and repeats
the determination of Step 516 for that exercise time profile. On
the other hand, if the target profile rate would not be exceeded,
microprocessor 189 activates the selected exercise time profile,
Step 520. Once the selected exercise time profile is activated,
microprocessor 189 continues to monitor the patient to determine
whether a termination event that would necessitate terminating the
rate variation function of the present invention, such as increased
sinus rhythm above the pacing rate, or an atrial or ventricular
tachycardia event, for example, is detected during the session,
Step 522. If a termination event is detected during the session,
the session is terminated, Step 524. According to the present
invention, conditions for termination in Step 522 prior to
completion of the session include detection of a programming
session, magnet, cardiac arrhythmia, or the spontaneous rate or the
rate response rate increasing to be greater than the exercise
stimulation rate 610.
[0076] Once the session is completed, YES in Step 524, or
terminated, Step 526, the pacing rate is returned from the exercise
simulation rate 610 back to a termination setting, which
corresponds to deceleration portion 608 reaching either the
spontaneous rate if greater than the lower pacing rate LR, the rate
response rate if greater than the lower pacing rate LR, or the
original lower pacing rate LR, for example, the process returns to
Step 502, and microprocessor 189 generates an updated histogram
after waiting the predetermined time period, and repeats the
comparison of the updated histogram with the target rate profile,
Steps 502-512. The session is determined to be completed in Step
524, for example, once the total of time periods T1, T2 and T3 has
expired.
[0077] Information corresponding to when a session has been
terminated, Step 526, completed Step 524, or when the profiles have
been exhausted Step 518, is stored for later retrieval as
diagnostic information. In this way, a physician may retrieve
diagnostic information related to what exercise sessions were
initiated by the device, when each of the initiated sessions
started, when the sessions were terminated, and whether the
sessions were terminated due to normal conditions, i.e.,
deceleration portion 608 reaching either the spontaneous rate, the
rate response rate, or the original lower pacing rate LR (Step
524), or were due to the detection of a termination event, such as
detection of a programming session, magnet, cardiac arrhythmia, or
the spontaneous rate or the rate response rate increasing to be
greater than the exercise stimulation rate 610 (Steps 522 and
526).
[0078] According to an embodiment of the present invention, in
determining whether exercise is appropriate based on the comparison
of the generated histogram and the target rate profile (Step 512 of
FIG. 9), microprocessor 189 compares the indicated percentage of
time that the patient's heart rate in the generated histogram of
FIG. 10A is within the 70-80 beat per minute and the 80-90 beat per
minute bins 600 with the indicated percentage of time for the
corresponding 70-80 and 80-90 beat per minute bins 602 of the
target rate profile of FIG. 10B. If either of bins 600 are greater
than or approximately equal to bins 602, microprocessor 189
determines that exercise would not be appropriate in Step 512,
generates an updated histogram after waiting the predetermined time
period, and repeats the comparison of the updated histogram with
the target rate profile, Steps 502-512. However, if microprocessor
189 determines that bins 600 are less than bins 602, exercise is
determined to be appropriate.
[0079] According to an alternate embodiment of the present
invention, in which the histogram is generated as a comparison of
the number of beats, rather than the percentage of time, the y-axis
in FIGS. 10A and 10B represents number of beats. In this
embodiment, when determining whether exercise is appropriate based
on the comparison of the generated histogram and the target rate
profile (Step 512 of FIG. 9), microprocessor 189 compares the
indicated number of beats in the generated histogram of FIG. 10A
within the 70-80 beat per minute and the 80-90 beat per minute bins
600 with the indicated number of beats in the corresponding 70-80
and 80-90 beat per minute bins 602 of the target rate profile of
FIG. 10B. If either of bins 600 are greater than or approximately
equal to bins 602, microprocessor 189 determines that exercise
would not be appropriate in Step 512, generates an updated
histogram after waiting the predetermined time period, and repeats
the comparison of the updated histogram with the target rate
profile, Steps 502-512. However, if microprocessor 189 determines
that bins 600 are less than bins 602, exercise is determined to be
appropriate.
[0080] FIG. 12 is a flowchart of a method for varying a pacing rate
in an implantable medical device according to the present
invention. Steps 500-512 in FIG. 12 are similar to Steps 500-512 of
FIG. 9 described above, and therefore will not be repeated for the
sake of brevity. According to the present invention, the rate
variation therapy may be gradually introduced and initiated by the
implantable medical device. For example, as illustrated in FIG. 12,
according to an embodiment of the present invention, once the
session of heart rate variation of the present invention is
determined to be appropriate in Step 512, microprocessor 189
determines whether the current generated histogram is consistent
with a predetermined number N of previously generated histograms,
Step 530. Predetermined number N can be set at any desired value,
such as 5 for example, and enables the device to verify that the
patient's heart rate consistently remains at approximately the same
rate below the target profile rate.
[0081] If the current generated histogram is not consistent with
the predetermined number N of previously generated histograms, NO
in Step 530, microprocessor 189 resets the initiation delay, Step
532, associated with Step 506 so that the implantable device delays
application of the escape rate variation feature of the present
invention over a predetermined period of time, such as five days as
described above, after which Step 530 is repeated. If it is
determined that the patient's heart rate consistently remains at
approximately the same rate below the target profile rate for the
predetermined number N of previously generated histograms, YES in
Step 530, a determination is made as to whether a projected
histogram including a session of the current selected exercise time
profile would result in one or more of bins of the target rate
profile to be exceeded, Step 533. If it is projected that one or
more bins would be exceeded, the selected exercise time profile is
updated by changing one or more of the exercise stimulation rate
610 (which effectively changes the specific bin or bins that are
compared with the target rate profile), times T1-T3, and shapes S1
and S2, Step 535. According to an embodiment of the present
invention, the process returns to Step 502 immediately upon
updating of the exercise time profile in Step 535, and
microprocessor 189 generates an updated histogram after waiting the
predetermined time period, repeats the comparison of the updated
histogram with the target rate profile, Steps 502-512 and performs
the subsequent heart rate variation session, Steps 530-548 using
the updated exercise time profile. In another embodiment of the
present invention, once the exercise time profile is updated in
Step 512, a determination is again made as to whether a projected
histogram including a session of the current selected exercise time
profile would result in one or more of bins of the target rate
profile to be exceeded, Step 533. In this embodiment, the number of
times that the exercise time profile is updated could be limited to
a predetermined number of updates, so that once the predetermined
number of updates have been performed without resulting in the
corresponding bin or bins of the target rate profile not being
exceeded, i.e., without determining NO in Step 533, the process
returns to Step 502 and microprocessor 189 generates an updated
histogram after waiting the predetermined time period, repeats the
comparison of the updated histogram with the target rate profile,
Steps 502-512 and performs the subsequent heart rate variation
session, Steps 530-548 using either the original exercise time
profile or an alternate exercise time profile.
[0082] However, according to an alternate embodiment of the
invention, if it is projected that one or more bins would be
exceeded, YES in Step 533, the process returns to Step 502 without
making updates to the exercise time profile, and microprocessor 189
generates an updated histogram after waiting the predetermined time
period, repeats the comparison of the updated histogram with the
target rate profile, Steps 502-512 and performs the subsequent
heart rate variation session, Steps 530-548 using the same exercise
time profile. In other words, the updating Step 535 is omitted in
the alternate embodiment.
[0083] If the projected histogram indicates that one or more bins
would not be exceeded, NO in Step 533, microprocessor 189 activates
the patient specific ADL exercise time profile, Step 534, so that
the implanted device begins pacing at the corresponding exercise
simulation rate 610 (FIG. 11A), utilizing the predetermined periods
of time T1-T3 and shapes S1 and S2.
[0084] Once the selected exercise time profile is activated,
microprocessor 189 continues to monitor the patient to determine
whether a termination event that would necessitate terminating the
rate variability function, such as increased sinus rhythm, or an
atrial or ventricular tachycardia event, for example, is detected
during the session, Step 536. If a termination event is detected
during the session, the session is terminated, Step 538. As
described above in reference to FIG. 9, conditions for termination
in Step 536 prior to completion of the session include detection of
a programming session, magnet, cardiac arrhythmia, or the
spontaneous rate or the rate response rate increasing to be greater
than the exercise stimulation rate 610.
[0085] Once the rate variation session is completed, YES in Step
540, microprocessor 189 generates an updated histogram, Step 542,
and determines whether the target rate profile has been reached,
Step 544, by comparing the bin 600 corresponding to the exercise
simulation rate 610 of the selected exercise time profile, i.e. 85
beats per minute, to the same bin 602 of the target rate profile
(FIG. 10B). As described above in reference to FIG. 9, the session
is determined to be completed in Step 540, for example, once the
total of time periods T1, T2 and T3 has expired.
[0086] If the target rate profile is not reached as a result of the
activated exercise time profile, NO in Step 544, the exercise time
profile is repeated, Step 534, and the determination as to whether
the target rate has been reached, Step 544, is repeated based on an
updated histogram generated after the repeated session is completed
without occurrence of a termination event, Steps 536-542. On the
other hand, if the target rate profile is reached as a result of
the activated exercise time profile, Yes in Step 544,
microprocessor 189 determines whether the target rate profile has
been reached a predetermined number N of times, Step 546.
[0087] The predetermined number of times N that the target rate
profile must be met, which is programmable and could be set at any
desired value, enables the pacing rate to be increased to the
selected exercise simulation rate 610 the predetermined number N of
times prior to adjusting the exercise time profile, Step 548,
thereby enabling the heart rate variation feature of the present
invention to gradually vary and increase the selected exercise time
profile as the patient experiences more and more sessions, similar
to normal recommended exercise regimens. In particular, once the
target rate profile has been reached a predetermined number N of
times, the selected exercise time profile is updated, Step 548, by
changing any one or more of the variables in the exercise time
profile, such as the exercise simulation rate 610, time periods
T1-T3 and shapes S1 and S2.
[0088] Once the exercise time profile has been updated, the pacing
rate is returned from the exercise simulation rate 610 back to a
termination setting, which corresponds to deceleration portion 608
reaching either the spontaneous rate if greater than the lower
pacing rate LR, the rate response rate if greater than the lower
pacing rate LR, or the lower pacing rate LR, for example, the
process returns to Step 502, and microprocessor 189 generates an
updated histogram after waiting the predetermined time period,
repeats the comparison of the updated histogram with the target
rate profile, Steps 502-512 and performs the subsequent heart rate
variation session, Steps 530-548 using the updated exercise time
profile.
[0089] Information corresponding to when sessions have been
terminated, Step 538, completed Step 540, when the target rate
profile has not been met N times, Step 546, or when the exercise
time profiles have been updated or exhausted Steps 535 and 548, is
stored for later retrieval as diagnostic information. In this way,
a physician may retrieve diagnostic information related to what
exercise sessions were initiated by the device, when each of the
initiated sessions started, when the sessions were terminated, and
whether the sessions were terminated due to normal conditions,
i.e., deceleration portion 608 reaching either the spontaneous
rate, the rate response rate, or the original lower pacing rate LR,
or were due to the detection of a termination event, such as
detection of a programming session, magnet, cardiac arrhythmia, or
the spontaneous rate or the rate response rate increasing to be
greater than the exercise stimulation rate 610.
[0090] According to an embodiment of the present invention, rather
than performing a single iteration of the selected exercise time
profile during a given session, the selected exercise time profile,
such as shown in FIGS. 11A or 11B, for example, could be repeated
any number of times, or could include multiple sessions at
different exercise simulation rates 610. For example, a single
session could include activating the exercise time profile of FIG.
11A three successive times, or could include multiple varied
sessions, with one session having one exercise simulation rate,
such as 85 beats per minute (FIG. 11A), and a second session having
a different exercise simulation rate, such as 100 beats per minute
(FIG. 11B), and so forth. In addition to the exercise simulation
rate 610, variations in one or more of time periods T1-T3 and
shapes S1 and S2 could also be included in the updating procedure.
FIGS. 11C-11F present alternate exercise time profiles, with FIG.
11C illustrating stepped heart rate variations to a peak level and
then steps back down to the lower rate, for example. FIG. 11D
illustrates the same step increase in the paced rate, however,
between each step is a period at the lower rate. FIG. 11E
illustrates a step rate to a peak rate, which is then maintained
for a prolonged period before returning back to the lower rate.
FIG. 11F illustrates step increases to the exercise simulation
rate, which is then returned to the lower rate. The illustrated
variations in the pacing rate, along with those illustrated in
FIGS. 11A and 11B, are not meant to be limiting, and illustrate
only a few of the numerous possible methods that could be used to
vary the heart rate. An appropriate exercise time profile is
selected to vary the heart rate to a targeted rate outside the
patient's basal variation for a prescribed period according to the
selected exercise time profile.
[0091] Some of the techniques described above may be embodied as a
computer-readable medium comprising instructions for a programmable
processor such as microprocessor 189 or pacer timing/control
circuitry 183 shown in FIG. 4. The programmable processor may
include one or more individual processors, which may act
independently or in concert. A "computer-readable medium" includes
but is not limited to any type of computer memory such as floppy
disks, conventional hard disks, CR-ROMS, Flash ROMS, nonvolatile
ROMS, RAM and a magnetic or optical storage medium. The medium may
include instructions for causing a processor to perform any of the
features described above for initiating a session of the escape
rate variation according to the present invention.
[0092] It is understood that while the above description includes
utilizing histogram bins to determine heart rate variability using
a time domain, application of the present invention is not intended
to be limited to the use of histograms and to the use of a time
domain. Rather, the present invention is intended to include other
methods for determining heart rate variability, such as standard
deviation for example, and domains other than the time domain, such
as a frequency domain for example.
[0093] While a particular embodiment of the present invention has
been shown and described, modifications may be made. It is
therefore intended in the appended claims to cover all such changes
and modifications, which fall within the true spirit and scope of
the invention.
* * * * *