Method and apparatuses for monitoring hemodynamic activities using an intracardiac impedance-derived parameter

• US 20030114889A1
• Filed: 02/06/2003
• Published: 06/19/2003
• Est. Priority Date: 07/14/2000
• Status: Active Grant

• Current Assignee: Cardiac Pacemakers Incorporated (Boston Scientific Corporation)
• Original Assignee: Cardiac Pacemakers Incorporated (Boston Scientific Corporation)
• Inventors: Sanchez, Francisca Cuesta, Huvelle, Etienne
• Granted Patent: US 7,062,326 B2
• Time in Patent Office: Days
• US Class Current: 607/17
• CPC Class Codes: A61N 1/36521 the parameter being derived from measurement of an electrical impedance

Abstract

An intracardiac impedance-derived parameter, Half Cycle Activity (HCA) is used in sensing and controlling cardiac activities in implantable cardiac devices such as bradycardia pacemakers and cardioverter defibrillators. This impedance-derived parameter correlates closely with physical workload and at the same time provides hemodynamic feedback information. Thus, it allows a pacemaker system to implement accurately an increase in hemodynamically driven pacing rate, as well as to limit an inappropriate decrease of driven pacing rate advised by another sensor such as an accelerometer. In addition, it determines the maximum pacing rate for the pacemaker so as to prevent hemodynamic compromise. Therefore, the HCA parameter may be used to determine a Hemodynamic Upper Rate Limit and a Hemodynamic Lower Rate Limit, and thus define a Hemodynamic Pacing Range that is compatible with the range of physiological rate. This allows a closed-loop control of the pacing rate. In an implantable cardioverter defibrillator system, the hemodynamic tolerance of arrhythmias can also be assessed by using the HCA parameter to adjust therapy provided to a heart, such as antitachycardia pacing and/or cardioverting shocks.

Claims

1. A cardiac pacemaker system comprising:

(a) an implantable lead adaptable for sensing intracardiac electrical signals and delivering high and low energy pacing therapy, wherein the lead includes two or more electrodes at various distances from each other;

(b) a sensing module for detecting the intracardiac electrical signals;

(c) an impedance circuit for recording intracardia impedance signals;

(d) a microprocessor for computing an intracardiac impedance-derived parameter based on the impedance signals wherein the intracardiac impedance-derived parameter includes a ratio of a first value related to an area encompassed by a portion of an impedance waveform and a second value related to an area encompassed by a whole impedance waveform corresponding to a single cardiac cycle;

(e) a pacing controller for adjusting a pacing therapy delivered by the system according to the impedance-derived parameter;

(f) a pacing module for delivering pacing signals to the implantable lead according to the pacing therapy;

(g) a sensor for generating electrical signals associated with activity related to cardiac demand; and

(h) a second sensing module for receiving the activity related electrical signals from the sensor, wherein the pacing controller uses the intracardiac impedance-derived parameter to modify pacing therapies suggested by the sensor activity-related signals.

2. The system of claim 1, wherein the sensor for generating electrical signals associated with activity related to cardiac demand is an accelerometer.

3. The system of claim 1, wherein the intracardiac impedance-derived parameter is a Half Cycle Activity (HCA) parameter and wherein the first value related to an area encompassed by a portion of the impedance waveform is an area related to a first half of the impedance waveform.

4. The system of claim 1, wherein the intracardiac impedance-derived parameter is an inverse of the HCA parameter.

5. The system of claim 1, wherein the intracardiac impedance-derived parameter is a Partial Cycle Activity (PCA) parameter and wherein the first value related to an area encompassed by a portion of an impedance waveform is related to a portion of an impedance waveform with a start point at a certain time of a cardiac cycle and an end point at a certain later time of the cardiac cycle.

6. The system of claim 1, wherein the intracardiac impedance-derived parameter is an inverse of the PCA parameter.

7. The system of claim 1, wherein the pacing controller using the intracardiac impedance-derived parameter to modify pacing therapies suggested by the sensor includes limiting an increase in pacing rate advised by the sensor.

8. The system of claim 1, wherein the pacing controller adjusting a pacing therapy delivered by the system according to the value of the impedance-derived parameter includes determining the maximum tolerated heart rate in the event of a supraventricular tachycardia.

9. The system of claim 1, wherein the pacing controller using the intracardiac impedance-derived parameter to modify pacing therapies suggested by the sensor includes limiting a decrease in pacing rate advised by the sensor.

10. The system of claim 1, wherein the first value related to an area encompassed by a portion of an impedance waveform and the second value related to an area encompassed by a whole impedance waveform corresponding to a single cardiac cycle are determined relative to a baseline impedance value associated with respiration.

11. The system of claim 1, wherein the impedance circuit blanks the impedance signals in response to a paced event, and wherein the microprocessor pads the values of the impedance signals during blanking with a last valid impedance signal.

12. The system of claim 11, wherein the blanking occurs in response to an atrial pace marker.

13. The system of claim 11, wherein the blanking occurs in response to a ventricular pace marker.

14. The system in claim 11, wherein a duration of the blanking and padding is less than thirty milliseconds.

15. The system in claim 11, wherein a duration of the blanking and padding falls within a range of twenty to thirty milliseconds.

16. A method of monitoring hemodynamic efficacy of a patient'"'"'s heart rate comprising:

computing an intracardiac impedance-derived parameter, wherein the intracardiac impedance-derived parameter includes a ratio of a first value related to an area encompassed by a portion of an impedance waveform and a second value related to an area encompassed by a whole impedance waveform corresponding to a single cardiac cycle, wherein the area encompassed by a portion of an impedance waveform and the area encompassed by the whole impedance waveform are determined relative to a baseline impedance value associated with respiration;

detecting a state of hemodynamic compromise based on the intracardiac impedance derived parameter when the rate is high; and

detecting that a hemodymanic demand is not being met when the rate is low.

17. The method of claim 16, wherein the intracardiac impedance-derived parameter is Half Cycle Activity (HCA) parameter and wherein the first value related to an area encompassed by a portion of the impedance waveform is an area related to a first half of the impedance waveform.

18. The method of claim 16, wherein the intracardiac impedance-derived parameter is an inverse of the HCA parameter.

19. The method claim 16, wherein the intracardiac impedance-derived parameter is a Partial Cycle Activity (PCA) parameter and wherein the first value related to an area encompassed by a portion of an impedance waveform is related to a portion of an impedance waveform with a start point at a certain time of a cardiac cycle and an end point at a certain later time of the cardiac cycle.

20. The method claim 16, wherein the intracardiac impedance-derived parameter is an inverse of the PCA parameter.