Method and Apparatus for Identifying Cardiac Risk

• US 20130131530A1
• Filed: 11/05/2012
• Published: 05/23/2013
• Est. Priority Date: 11/03/2009
• Status: Active Grant

• Current Assignee: VivaQuant LLC
• Original Assignee: VivaQuant LLC
• Inventors: BROCKWAY, MARINA, BROCKWAY, BRIAN, HAMLIN, ROBERT
• Granted Patent: US 8,688,202 B2
• Time in Patent Office: Days
• US Class Current: 600/513
• CPC Class Codes: A61B 5/316 Modalities, i.e. specific diagnostic methods
• CPC Class Codes: A61B 5/349 Detecting specific parameters of the electrocardiograph cycle
• CPC Class Codes: A61B 5/352 Detecting R peaks, e.g. for synchronising diagnostic apparatus; Estimating R-R interval
• CPC Class Codes: A61B 5/7203 for noise prevention, reduction or removal
• CPC Class Codes: A61B 5/7235 Details of waveform analysis A61B5/349 takes precedence
• CPC Class Codes: A61B 5/7253 characterised by using transforms
• CPC Class Codes: A61B 7/00 Instruments for auscultation

Abstract

A cardiac-based metric is computed based upon characteristics of a subject'"'"'s cardiac function. In accordance with one or more embodiments, the end of a mechanical systole is identified for each of a plurality of cardiac cycles of a subject, based upon an acoustical vibration associated with closure of an aortic valve during the cardiac cycle. The end of an electrical systole of an electrocardiogram (ECG) signal for each cardiac cycle is also identified. A cardiac-based metric is computed, based upon a time difference between the end of the electrical systole and the end of the mechanical systole, for the respective cardiac cycles.

Claims

1. A method for computing a cardiac-based metric, the method comprising:

for each of a plurality of cardiac cycles of a subject,

identifying the end of a mechanical systole based upon an acoustical vibration associated with closure of an aortic valve during the cardiac cycle, and

identifying the end of an electrical systole of an electrocardiogram (ECG) signal for the cardiac cycle; and

computing the cardiac-based metric based upon a time difference between the end of the mechanical systole and the end of the electrical systole in each of the plurality of cardiac cycles.

2. The method of claim 1, wherein

identifying the end of the mechanical systole includes, in a circuit, processing electronic heart sound data for the cardiac cycle to identify the end of the mechanical systole based on characteristics of the heart sound data, and

identifying the end of the electrical systole includes, in a circuit, processing electronic ECG signal data for the cardiac cycle to identify the end of the electrical systole based on characteristics of the ECG signal data.

3. The method of claim 1, wherein computing the cardiac-based metric includes computing a metric indicative of proarrhythmic risk.

4. The method of claim 1, wherein identifying the end of the mechanical systole includes identifying the end of a mechanical systole using a heart sound signal obtained from the subject during the cardiac cycle.

5. The method of claim 1 wherein identifying the end of the electrical systole includes identifying a T-wave offset for the ECG signal.

6. The method of claim 1, wherein computing the cardiac-based metric includes computing one of a mean and median of the values of the time difference for each cardiac cycle.

7. The method of claim 1, wherein computing the cardiac-based metric includes computing at least one of variance, standard deviation, and standard error of the time difference for each cardiac cycle.

8. The method of claim 1, wherein computing the cardiac-based metric includes computing a short-term instability metric by computing one of the mean, standard deviation and root mean square of successive differences between beat-to-beat values in a window segment including the plurality of cardiac cycles.

9. The method of claim 8, further including computing a long-term instability metric by computing a variance in the beat-to-beat values, multiplying the computed variance by two and subtracting the computed short term instability metric.

10. The method of claim 1, wherein identifying the end of a mechanical systole includes

detecting the closure of the aortic valve using an acoustical signal containing energy associated with closure of the aortic valve and noise energy,

decomposing the acoustical signal from a first domain into subcomponents of the acoustical signal in a second domain,

identifying at least two of the subcomponents that respectively exhibit an energy level of which at least half is associated with closure of the aortic valve, and

mathematically combining the identified subcomponents to compute a time function that identifiably changes in value upon aortic valve closure.

11. The method of claim 1, wherein the ECG signal includes an ECG component originating from heart tissue of the subject and a noise component, and wherein identifying the end of the electrical systole includes:

decomposing the ECG signal from a first domain into subcomponents of the ECG signal in a second domain,

identifying the location of a QRS complex of the cardiac cycle based upon a spatial distribution of the subcomponents,

identifying a first time window in the cardiac cycle that includes the QRS complex,

identifying at least one additional time window in the cardiac cycle that does not include the QRS complex,

for each time window, identify subcomponents having more energy corresponding to the ECG component than noise energy, and

constructing a denoised ECG in the first domain by combining the identified subcomponents, and using the denoised ECG to identify the end of the electrical systole.

12. The method of claim 1, wherein identifying the end of electrical systole includes:

decomposing the ECG signal from a first domain into subcomponents of the ECG signal in a second domain,

identifying the location of a QRS complex of the cardiac cycle based upon a spatial distribution of the subcomponents,

establishing a T-wave offset search window relative to the location of the QRS complex,

identifying at least two subcomponents having an energy value that is predominantly energy of a T-wave of the cardiac cycle,

mathematically combing the at least two identified subcomponents to compute an emphasis signal having an identifiable inflection corresponding to a location of the T-wave offset,

identifying the T-wave offset location based upon a characteristic of the emphasis signal, and

using the T-wave offset location to identify the end of the electrical systole.

13. The method of claim 1, further including computing the time difference between the end of the mechanical systole and the end of the electrical systole for each cardiac cycle.

14. An apparatus for computing a cardiac-based metric of a subject using signal data for a plurality of cardiac cycles, the apparatus including:

a first module configured and arranged to identify the end of a mechanical systole based upon an acoustical vibration associated with closure of an aortic valve during the cardiac cycle;

a second module configured and arranged to identify the end of an electrical systole of an electrocardiogram (ECG) signal for the cardiac cycle; and

a third module configured and arranged to compute the cardiac-based metric based upon a time difference between the end of the mechanical systole and the end of the electrical systole in each of the cardiac cycles.

15. The apparatus of claim 14, further including

a sensor configured and arranged to convert mechanical vibrations generated by heart sounds of the subject into an electrical heart sound signal, the first module being configured and arranged to receive the heart sound signal and to identify the end of the mechanical systole based upon the acoustical vibration using an acoustical vibration indicated via the received heart sound signal, and

at least two electrodes configured and arranged to sense the ECG signal from the subject'"'"'s heart, the second module being configured and arranged to receive the ECG signal.

16. The apparatus of claim 14, wherein the second module is configured and arranged to identify the end of the electrical systole by identifying a T-wave offset for the ECG signal.

17. The apparatus of claim 14, wherein the third module is configured and arranged to compute the cardiac-based metric by computing at least one of a mean, and median, variance, standard deviation, and standard error of the values of the time difference for the cardiac cycles.

18. The apparatus of claim 14, wherein the third module is configured and arranged to compute the cardiac-based metric by computing a short-term instability metric by computing at least one of the mean, standard deviation and root mean square of successive differences between beat-to-beat values in a window segment including the plurality of cardiac cycles, the beat-to-beat values corresponding to heartbeats that define the successive start of the cardiac cycles.

19. The apparatus of claim 18, wherein the third module is configured and arranged to compute a long-term instability metric by computing a variance in the beat-to-beat values, multiplying the computed variance by two and subtracting the computed short term instability metric.

20. The apparatus of claim 14, wherein the first module is configured and arranged to identify the end of a mechanical systole by

detecting the closure of the aortic valve using an acoustical signal containing energy associated with closure of the aortic valve and noise energy,

decomposing the acoustical signal from a first domain into subcomponents of the acoustical signal in a second domain,

identifying at least two of the subcomponents exhibiting an energy level of which at least half is associated with closure of the aortic valve, and

mathematically combining the identified subcomponents to compute a time function that identifiably changes in value upon aortic valve closure.

21. The apparatus of claim 14, wherein the ECG signal includes an ECG component originating from heart tissue of the subject and a noise component, and wherein the second module is configured and arranged to identify the end of the electrical systole by:

decomposing the ECG signal from a first domain into subcomponents of the ECG signal in a second domain,

identifying the location of a QRS complex of the cardiac cycle based upon a spatial distribution of the subcomponents,

identifying a first time window in the cardiac cycle that includes the QRS complex,

identifying at least one additional time window in the cardiac cycle that does not include the QRS complex,

for each time window, identify subcomponents having more energy corresponding to the ECG component than noise energy,

constructing a denoised ECG in the first domain by combining the identified subcomponents, and

identifying a T-wave offset in the denoised ECG as the end of the electrical systole.

22. The apparatus of claim 14, wherein the second module is configured and arranged to identify the end of the electrical systole by:

decomposing the ECG signal from a first domain into subcomponents of the ECG signal in a second domain,

identifying the location of a QRS complex of the cardiac cycle based upon a spatial distribution of the subcomponents,

establishing a T-wave offset search window relative to the location of the QRS complex,

identifying at least two subcomponents having an energy value that is predominantly energy of a T-wave of the cardiac cycle,

mathematically combing the at least two identified subcomponents to compute an emphasis signal having an identifiable inflection corresponding to a location of the T-wave offset,

identifying the T-wave offset location based upon a characteristic of said emphasis signal, and

using the T-wave offset location to identify the end of the electrical systole

23. The apparatus of claim 14, wherein the sensor and the electrodes are coupled with an adhesive-backed patch configured and arranged to adhere to the subject.

24. A method for computing a metric indicative of arrhythmic risk, the method comprising:

computing beat-to-beat values of a subject'"'"'s cardiac function based on at least one of;

an electromechanical window corresponding to a time between the end of mechanical systole and the end of electrical systole of the subject'"'"'s heart, a QT interval corresponding to a time between the start of a Q wave and the end of a T wave of the subject'"'"'s ECG, and an R-R interval of the subject'"'"'s ECG;

computing a time series for each of successive lags of the beat-to-beat values by applying a low-pass filter and decimator to the beat-to-beat values;

computing a trend of the variability of the time series by using one of sample entropy, long-term instability, short-term instability, and variance; and

evaluating arrhythmic risk based upon the computed trend.

25. The method of claim 24, wherein the successive lags vary from 1 to 10.