Thermal drift correction while continuously monitoring cardiac output

• US 5,261,411 A
• Filed: 12/27/1991
• Issued: 11/16/1993
• Est. Priority Date: 12/27/1991
• Status: Expired due to Term

• Current Assignee: Hospira Incorporated (Pfizer Inc.)
• Original Assignee: Abbott Laboratories Incorporated
• Inventors: Hughes, Timothy J.
• Primary Examiner(s): Green, Randall L.
• Assistant Examiner(s): Burke, Elizabeth
• Application Number:
  US07/815,345
• Time in Patent Office: 690 Days
• Field of Search: 128/668, 128/691, 128/692, 128/713, 128/736, 128/642, 128/898
• US Class Current: 600/481
• CPC Class Codes: A61B 5/0275 using tracers, e.g. dye dilution
• CPC Class Codes: A61B 5/028 by thermo-dilution
• CPC Class Codes: A61B 5/7203 for noise prevention, reduction or removal
• CPC Class Codes: A61B 5/7257 using Fourier transforms

Abstract

A method for compensating the determination of cardiac output for a baseline blood temperature drift, or other long-term noise. The method is applicable to the continuous monitoring of cardiac output, which is carried out by modifying the temperature of blood within a heart (12) using a periodically varying electrical current that is applied to a heater (22) disposed on the outer surface of a catheter (14) inserted within the heart. A temperature sensor (24) disposed near a distal end (18) of the catheter monitors the temperature of blood leaving the heart, producing a blood temperature signal that periodically varies in a manner corresponding to the input signal. Alternatively, the temperature of blood within the heart can be modified by heat exchange with a fluid circulated within a heat exchanger (16) on the catheter, so that heat is transferred between the fluid and blood. Changes in the baseline blood temperature caused by a gradual warming of the patient from a chilled condition or due to other long term noise are compensated by either carefully selecting a measurement interval during which the blood temperature signal is filtered (by performing a discrete Fourier transform) so that the blood temperature signal (without the effect or drift) comprises only a real component, or by shifting the starting point of the input power signal to achieve the same result. The baseline temperature drift of the blood or other noise is thus in quadrature with the blood temperature signal (without drift) and has little effect on the determination of cardiac output. Further compensation in the measurement interval and/or starting time of the input signal can be made to compensate for other time delays, such as delays due to mixing volume, transport delay, and delays associated with the time constants of the apparatus used to modify the temperature of the blood and determine its temperature.

Claims

1. A method for measuring cardiac output of a heart that is compensated for a drift in a baseline temperature of blood, comprising the steps of:

(a) producing a periodically varying input signal that is used for changing a temperature of blood within the heart, so that a temperature of the blood leaving the heart varies periodically with respect to the baseline temperature of the blood;

(b) sensing the temperature of the blood leaving the heart, producing a blood temperature signal corresponding thereto that varies periodically;

(c) filtering the blood temperature signal to determine a filtered output signal comprising an in-phase component and a quadrature component;

(d) selecting a measurement interval for the blood temperature signal relative to the input signal, so as to insure that the filtered output signal predominantly comprises the in-phase component; and

(e) determining the cardiac output of the heart as a function of the input signal and of the filtered output signal, the effect of any baseline temperature drift being minimized in this determination because the baseline temperature drift primarily comprises the quadrature component, which is substantially out of phase with the in-phase component of the filtered output signal.

2. The method of claim 1, wherein the step of selecting the measurement interval comprises the step of shifting a time at which the input signal is applied relative to a measurement interval of the blood temperature signal that was initially arbitrarily selected.

3. The method of claim 1, wherein the step of selecting the measurement interval comprises the step of shifting the measurement interval during which the blood temperature signal is filtered so that it is at a predefined phase angle with respect to the input signal.

4. The method of claim 3, wherein the phase angle by which the measurement interval is shifted relative to the input signal is selected as a function of a phase lag associated with a thermal mass of apparatus inserted into the heart to periodically vary the temperature of the blood by application of the input signal, and as a function of a phase lag associated with a thermal mass of a temperature sensor used to sense the temperature of the blood leaving the heart.

5. The method of claim 3, wherein the phase angle by which the measurement interval is shifted relative to the input signal is selected as a function of a phase lag caused by a mixing volume of the heart.

6. The method of claim 5, wherein the step of filtering comprises the step of determining a phase angle of the blood temperature signal in a frequency domain, wherein the phase lag caused by the mixing volume is determined by averaging the phase angle of the blood temperature signal over a plurality of measurement intervals to determine an average phase angle, and wherein the amount by which the measurement interval is shifted in phase is chosen as necessary to make the average phase angle of the blood temperature signal substantially equal to zero.

7. The method of claim 5, wherein the phase lag of the mixing volume is determined by the steps of performing a spectral analysis of the filtered output signal over a plurality of measurement intervals to determine a phase angle for the filtered output signal in a frequency domain;

and, adjusting the measurement interval so said phase angle is substantially equal to zero.

8. A method for measuring cardiac output of a heart so as to compensate for a drift in a baseline temperature of blood and for other noise, comprising the steps of:

(a) producing a periodic input signal that changes a temperature of blood leaving the heart with respect to the baseline temperature of blood entering the heart, said input signal comprising a wave form defining a plurality of cycles, each cycle extending over a predefined period of time;

(b) sensing the temperature of blood leaving the heart, producing a blood temperature signal that varies periodically in a manner corresponding to the period of the input signal, said blood temperature signal comprising a wave form defining a plurality of cycles, each cycle extending over the predefined period of time;

(c) providing a selected phasal relationship between a start of the input signal and a start of a measurement interval during which the blood temperature signal is produced, so that the drift in the baseline temperature of blood and other noise add to the blood temperature signal in quadrature; and

(d) determining the cardiac output of the heart as a function of the input signal and of the blood temperature signal, any effect of the baseline temperature drift and other noise being minimized in this determination because any contribution of the baseline temperature drift and noise to the blood temperature signal is substantially out of phase with changes in the blood temperature signal caused by the input signal and is therefore substantially negligible.

9. The method of claim 8, wherein the step of providing a selected phasal relationship comprises the step of shifting a starting point during a cycle of the periodic input signal relative to an initial starting point so that the baseline temperature of blood and other noise add to the blood temperature signal in quadrature, a point initially selected for the start of the measurement interval in each cycle of the blood temperature signal remaining unchanged.

10. The method of claim 8, wherein the step of determining the cardiac output of the heart comprises the steps of digitizing the blood temperature signal to produce a corresponding digital blood temperature signal;

and filtering the digital blood temperature signal to determine an in-phase component and a quadrature component together comprising a filtered output signal, a point during each cycle of the blood temperature signal being selected for the start of the measurement interval, which is equal in duration to the predefined period of time for each cycle, so that the blood temperature signal contributes principally to the in-phase component and the baseline temperature drift and other noise contribute principally to the quadrature component.

11. The method of claim 10, wherein the step of filtering comprises the step of performing a discrete Fourier transform of the digital blood temperature signal to determine the in-phase and the quadrature components of the digital blood temperature signal.

12. The method of claim 10, further comprising the steps of spectrally analyzing a plurality of cycles of the filtered output signal to determine an average phase angle of the filtered output signal;

and selecting a point during each cycle of the blood temperature signal so as to insure that the average phase angle of the filtered output signal is substantially equal to zero.

13. The method of claim 10, further comprising the steps of spectrally analyzing a plurality of cycles of the filtered output signal to determine an average phase angle of the filtered output signal;

and selecting the start of the input signal so as to insure that the average phase angle of the filtered output signal is substantially equal to zero.

14. The method of claim 10, wherein the periodic input signal comprises a plurality of harmonic frequencies, further comprising the steps of:

(a) providing a selected phasal relationship between the start of the input signal and the start of the measurement interval for each of the harmonic frequencies each such measurement interval starting a different phasal time than the measurement intervals of any other harmonic frequencies;

(b) determining an in-phase component of the blood temperature signal for each of the measurement intervals;

(c) adding the in-phase components for each of the measurement intervals of the harmonic frequencies together to produce the filtered output signal; and

(d) using the filtered output signal to determine the cardiac output, said cardiac output being compensated for the baseline temperature drift and noise.

15. The method of claim 10, wherein the step of providing a selected phasal relationship comprises the step of determining a time delay to compensate for a time constant of a mixing volume and for a transport delay, both of which are characteristic of the heart.

16. The method of claim 15, wherein the filtered output signal includes a magnitude and a phase angle, and wherein compensation for the time constant of the mixing volume and the transport delay is determined by calculating an average phase angle of the filtered output signal over a plurality of cycles and shifting a point during each cycle of the blood temperature signal at which the measurement interval starts as necessary to make the average phase angle of the filtered output signal substantially equal to zero.

17. The method of claim 15, wherein the filtered output signal includes a magnitude and a phase angle, and wherein compensation for the time constant of the mixing volume and the transport delay is determined by calculating an average phase angle of the filtered output signal over a plurality of cycles and shifting a start of the input signal as necessary to make the average phase angle of the filtered output signal substantially equal to zero.

18. The method of claim 8, wherein the step of producing the periodic input signal comprises the steps of supplying a sinusoidally varying electrical current to a resistance heater disposed in the heart, which transfers heat to the blood to periodically change its temperature in a sinusoidal manner.

19. The method of claim 8, wherein the step of producing the periodic input signal comprises the steps of periodically supplying a temperature-conditioned fluid to a heat exchanger disposed in the heart, the heat exchanger modifying the temperature of the blood in the heart by transferring heat between the temperature-conditioned fluid and the blood.

20. The method of claim 8, wherein the step of providing a selected phasal relationship comprises the step of determining a time delay for either the start of the measurement interval or the start of the input signal, said time delay including a compensation for a time constant of a temperature sensor that produces the blood temperature signal.

21. The method of claim 8, further comprising the steps of:

(a) determining a cardiac output that is not compensated for the baseline temperature drift;

(b) estimating a mixing volume phase angle;

(c) determining a mixing volume as a function of the mixing volume phase angle and of the cardiac output that is not compensated for the baseline temperature drift;

(d) averaging the mixing volume over a plurality of measurement intervals to determine an average mixing volume;

(e) determining a mixing volume phase angle as a function of the average mixing volume and the cardiac output that is not compensated for the baseline temperature drift; and

(f) adjusting the phasal relationship between the start of the input signal and the start of the measurement intervals during subsequent determinations of the cardiac output as a function of the mixing volume phase angle and to compensate for the drift in the baseline temperature and other noise.