Method and system for non-invasive ultrasound Doppler cardiac output measurement

• US 4,509,526 A
• Filed: 02/08/1983
• Issued: 04/09/1985
• Est. Priority Date: 02/08/1983
• Status: Expired due to Fees

• Current Assignee: Lawrence Medical Systems Incorporated
• Original Assignee: Lawrence Medical Systems Incorporated
• Inventors: Barnes, Stephen R., McLaren, Barry D., Huntsman, Lee L., Tarbox, Gary L.
• Primary Examiner(s): Howell, Kyle L.
• Assistant Examiner(s): Jaworski, Francis J.
• Application Number:
  US06/464,965
• Time in Patent Office: 791 Days
• Field of Search: 128/663, 128/661, 128/713
• US Class Current: 600/456
• CPC Class Codes: A61B 8/065 to determine blood output from the heart in general A61B5/029
• CPC Class Codes: A61B 8/4405 Device being mounted on a trolley
• CPC Class Codes: A61B 8/463 characterised by displaying multiple images or images and diagnostic data on one display composite display in devices for short-range imaging with acoustic waves G01S7/52074
• CPC Class Codes: A61B 8/465 adapted to display user selection data, e.g. icons or menus
• CPC Class Codes: G01S 15/8979 Combined Doppler and pulse-echo imaging systems

Abstract

A method and system for the noninvasive measurement of cardiac output of a mammalian patient on a real time, beat-by-beat basis as a combined function of the cross-sectional area of the ascending aorta and the systolic velocity of blood flow therethrough is comprised of the steps of and apparatus for pulsedly insonifying the ascending aorta of the patient with repetitive, intermittent ultrasonic energy propagating through the patient'"'"'s cardiac window; receiving pulses of ultrasonic energy reflected from the anatomical structure within the first insonification zone, including energy reflected from the aortic walls and characteristic of the dimensional separation thereof; developing an aortic diameter signal indicative of dimensional separation; computing the cross-sectional area of the ascending aorta therefrom; then continuously insonifying the ascending aorta with uninterrupted ultrasonic energy; receiving a Doppler-shifted ultrasonic energy signal reflected from pulsatile blood flow through the ascending aorta, and characteristic of systolic velocity of blood flow; subjecting the systolic velocity signal to a frequency spectrum analysis at a predetermined signal sampling rate to yield a velocity component profile signal; integrating the velocity component profile signal over time; computing systolic volume as a combined function of cross-sectional area and the systolic velocity integral for each of n cardiac cycles; and, computing cardiac output as the time-averaged sum of systolic volumes for the n periods.

Claims

1. A method for the noninvasive measurement of cardiac output of a mammalian patient on a real time, beat-by-beat basis as a combined function of the cross-sectional area of the ascending aorta and the systolic velocity of blood flow therethrough, comprising the steps of:

a. pulsedly insonifying the ascending aorta of said patient with repetitive, intermittent ultrasonic energy propagating along a line generally transverse with respect to the axis of said ascending aorta to define a first insonification zone;

b. receiving pulses of ultrasonic energy reflected from anatomical structure within said first insonification zone, including energy reflected from the anterior and posterior walls of said ascending aorta characteristic of the separation thereof along the transverse line of propagation;

c. discriminating said pulses of received ultrasonic energy to detect the transverse dimension of said ascending aorta between said anterior and posterior walls thereof;

d. developing an aortic diameter signal proportional to and indicative of said transverse dimension;

e. computing the cross-sectional area of said ascending aorta in the plane of said transverse line of propagation of pulsed energy;

f. continuously insonifying said ascending aorta with uninterrupted ultrasonic energy propagating along a line generally axial with respect to the axis of said ascending aorta to define a second insonification zone;

g. receiving Doppler-shifted ultrasonic energy reflected from pulsatile blood flow through said ascending aorta, frequency-shifted from said uninterrupted ultrasonic energy by values characteristic of systolic velocity of said blood flow;

h. developing a systolic velocity energy signal proportional to and indicative of said systolic velocity;

i. subjecting said systolic velocity energy signal to frequency spectrum analysis at a predetermined signal sampling rate to yield a velocity component profile signal;

j. integrating said velocity component profile signal over time for each period of said pulsatile flow to calculate a systolic velocity integral;

k. computing systolic volume as a combined function of said cross-sectional area and said systolic velocity integral;

l. computing cardiac output as the sum of said systolic volumes for n periods and dividing the sum by the time duration thereof.

2. The method of claim 1, wherein said step of subjecting said systolic velocity energy signal to frequency spectrum analysis includes the steps of:

a. establishing a plurality of signal sampling rates;

b. establishing a plurality of statistically anticipated systolic velocity ranges for pulsatile blood flow;

c. selecting high and low threshold values for said ranges;

d. monitoring systolic velocity to determine its value within a given one of said ranges relative to said threshold values; and

,

e. adjusting said signal sampling rate to a predetermined one of said plurality corresponding to the value of said systolic velocity within the high and low threshold values for said predetermined range.

3. The method of claim 2, further comprising the step of providing an operator-interactive visual display for presenting a visual sequence of procedural operator options, including the step of measuring said aortic diameter by:

a. locating a pulse-echo ultrasonic transducer probe to establish said first insonification zone through said patient'"'"'s cardiac window;

b. presenting a scaled visual display of said received ultrasonic energy indicative of the anatomical structure within said insonification zone including said anterior and posterior walls of said ascending aorta;

c. measuring the scaled dimension between said walls to develop said transverse aortic signal; and

d. delivering said transverse aortic signal to processor means for computing said cross-sectional area in accordance with an adaptive algorithm stored therein.

4. The method of claim 3, further comprising the step of manipulating said probe to minimize the scaled distance between said walls and returns from structure other than said walls appearing on said visual display.

5. The method of claim 4, wherein said measuring step includes:

a. visually discriminating the returns corresponding respectively to said anterior and posterior walls for the correct cross section of said aorta;

b. positioning a first moveable visual marker over said return for said anterior wall;

c. positioning a second moveable visual marker over said return for said posterior wall; and

,

d. measuring the scaled distance between said first and second markers.

6. The method of claim 5, wherein said display is a cathode ray tube display and said presenting step includes:

a. amplifying received pulse-echo signals indicative of returned ultrasonic energy from said first insonification zone;

b. selectively attenuating said pulse-echo signals inversely proportional to the propagation distance between said probe and the structure within said first insonification zone responsible for a given return to spatially normalize said pulse-echo signals;

c. digitizing the normalized pulse-echo signals to develop digital raster scan signals; and

,

d. controlling raster scan of said cathode ray tube with said digital raster scan signals to present said visual display.

7. The method of claim 6, wherein said display includes a touch-sensitive overlay for operator interaction, whereby said sequence of procedural operator options are elected upon a manual touch of active field areas of said overlay.

8. The method of claim 3, further comprising the steps of providing a continuous wave transducer probe having a transmitter crystal for developing said uninterrupted ultrasonic energy at a transmitter frequency and a receiver crystal for detecting received, Doppler-shifted energy from said second insonification zone having a frequency shift proportional to said systolic velocity, and converting said received energy to a Doppler signal, wherein said step of developing said systolic velocity energy signal comprises the steps of:

a. amplifying said Doppler signal;

b. mixing said Doppler signal with at least one reference signal having a reference frequency selected to develop an audio frequency Doppler signal; and

,

c. digitizing said audio frequency Doppler signal and applying same to said frequency spectrum analysis.

9. The method of claim 8, wherein said mixing step includes the steps of:

a. selectively attenuating said Doppler signal to develop an amplitude normalized RF Doppler signal;

b. mixing said normalized RF Doppler signal with a first reference frequency signal having a frequency different from said transmitter frequency by a frequency f to develop an intermediate frequency Doppler signal;

c. selectively attenuating said intermediate frequency Doppler signal to develop an amplitude normalized intermediate frequency Doppler signal; and

,

d. mixing said normalized intermediate frequency Doppler signal with a second reference frequency signal having a frequency f to develop an audio frequency Doppler signal having a frequency directly proportional to systolic velocity, constituting said systolic velocity energy signal.

10. The method of claim 9, wherein said step of subjecting said systolic velocity energy signal to frequency spectrum analysis includes:

a. sampling said systolic velocity energy signal at a first of said signal sampling rates to develop a sampled systolic velocity energy signal;

b. digitizing said sampled systolic velocity energy signal;

c. subjecting the digitized systolic velocity energy signals to fast Fourier transformation; and

,

d. selecting the peak component frequency in each sampling period to develop said velocity component profile signal.

11. The method of claim 10, wherein said step of establishing a plurality of signal sampling rates includes establishing a first range for systolic velocities up to about 82 cm/s, a second range for systolic velocities up to about 165 cm/s and a third range for systolic velocities up to about 330 cm/sec.;

and further wherein said step of adjusting said signal sampling rate comprises;

a. initially sampling at a first rate corresponding to said first range;

b. monitoring said velocity component profile signal for a predetermined number of cardiac cycles to determine systolic velocity;

c. comparing systolic velocity to a high threshold value for said first range;

d. adjusting said sampling rate to a second rate corresponding to said second range upon the occurrence of systolic velocities in excess of the high threshold value for said first range;

e. comparing systolic velocity ot a high and low threshold values for said second range;

f. adjusting said sampling rate to said first rate upon the occurrence of systolic velocities lower than the low threshold value for said second range or to said third rate upon the occurrence of systolic velocities in excess of said high threshold value for said second range;

g. comparing systolic velocity to a low threshold value for said third range; and

,

h. adjusting said sampling rate to said second rate upon the occurrence of systolic velocities lower than said low threshold value for said third range.

12. The method of claim 11, wherein said velocity component profile signal is applied to processor means for computing the time integral of each of said signals over the corresponding cardiac period to yield said systolic velocity integral and for computing cardiac stroke volume as the product of said systolic velocity integral and said aortic cross-sectional area.

13. The method of claim 12, further comprising the step of visually displaying said systolic velocity integral on a cathode ray tube display.

14. The method of claim 13, further comprising the steps of manipulating said continuous wave transducer probe to maximize the value of the displayed systolic velocity integral.

15. The method of claim 14, wherein said cardiac output is calculated as the average of the sum of discrete stroke volume values based on the sum of cardiac cycle periods.

16. The method of claim 15, further comprising the steps of calculating cardiac index as the ratio of cardiac output to body surface area of said patient and stroke index as the ratio of stroke volume to said body surface area.

17. A system for the noninvasive measurement of cardiac output of a mammalian patient on a real time, beat-by-beat basis as a combined function of the cross-sectional area of the ascending aorta and the systolic velocity of blood flow therethrough, comprising:

a. pulse-echo transducer means for developing repetitive, intermittent bursts of ultrasonic energy and applying same to said patient to define a first insonification zone enveloping the region of the ascending aorta of said patient and for detecting energy reflected from the anatomical structure within said first insonification zone, including the anterior and posterior walls of said ascending aorta;

b. pulse transmitter means for exciting said pulse-echo transducer to develop said bursts of energy;

c. pulse receiver means for developing an echo signal proportional to and indicative of detected energy;

d. operator-interactive visual display means for presenting control and display capabilities, including a graphic, scaled display of echo signals representative of the spatial conformation of said anatomical structure and signal strength representative of pulsatile blood flow therethrough;

e. measurement means in operative association with said visual display means for determining the spatial separation between anterior and posterior walls represented on said scaled display, to develop an aortic diameter signal,

f. area processor means receiving said aortic diameter signal for determining the cross-sectional area of said ascending aorta;

g. continuous wave transducer means for developing uninterrupted ultrasonic energy and applying same to define a second insonification zone within said region of said ascending aorta and for detecting Doppler-shifted energy reflected from pulsatile blood flow therethrough;

h. continuous wave transmitter means for exciting said continuous wave transducer to develop said uninterrupted ultrasonic energy at a continuous wave transmitter frequency;

i. continuous wave receiver means for developing a Doppler signal having a frequency shift from said continuous wave transmitter frequency proportional to and indicative of the systolic velocity of said pulsatile blood flow;

j. converter means for processing said Doppler signal to an audio frequency systolic velocity energy signal;

k. spectrum analyzer means receiving said systolic velocity energy signal for developing a frequency domain velocity component profile signal characteristic of the velocity profile of systolic flow over an observed cardiac cycle;

l. velocity processor means receiving said velocity component profile signal for computing the time integral thereof over the period of said caridac cycle, in accordance with an adaptive algorithm stored therein, to yield a systolic velocity integral signal and a stroke volume signal as a function of said cross-sectional area and said stroke volume; and

,

m. cardiac output processor means receiving said stroke volume signal and a heart rate signal for determining cardiac output as the time-averaged sum of a plurality of cyclic stroke volumes.

18. The system of claim 17, wherein said pulse receiver means comprises:

a. echo amplifier means for developing an amplitude-conditioned radio frequency echo signal;

b. controlled attenuator means for amplitude alteration of said amplitude-conditioned radio frequency echo signal inversely proportional to the propagation distance between said pulse-echo transducer means and the anatomical structure within said first insonification zone responsible for a given return to develop a spatially normalized echo signal;

c. detector means for rectifying and filtering said spatially normalized echo signal to yield an envelope signal proportional to and indicative of said detected energy; and

,

d. analog-to-digital converter means receiving said envelope signal for developing a digital echo signal output.

19. The system of claim 18, wherein said visual display is a cathode ray tube display;

said system further comprising raster scan driving and storage means receiving said digital echo signal for visual presentation of said detected energy on a scaled video display representing said anatomical structure.

20. The system of claim 19, wherein said measurement means is comprised of moveable markers appearing on said display for operator registration with the video display at returns representative of said anterior and posterior walls respectively.

21. The system of claim 20, further comprising touch-sensitive overlay means in operative association with said visual display, wherein said markers are moveable in response to a manual touch of an active field area on said display and said aortic diameter signal is developed as a signal proportional to the distance between said markers when registered with said returns.

22. The system of claim 21, wherein said continuous wave receiver means includes:

a. Doppler signal amplifier means for developing an amplitude-conditioned radio frequency Doppler signal; and

,

b. mixer means for frequency translation of said Doppler signal to yield a frequency normalized Doppler signal.

23. The system of claim 22, wherein said receiver means includes first and second mixer stages preceded respectively by first and second controlled attenuator means;

and further wherein said first mixer stage receives said radio frequency Doppler signal and a beat frequency reference signal having a frequency different from said transmitter frequency by a frequency f to yield an intermediate frequency Doppler signal and said second mixer stage receives said intermediate frequency Doppler signal and a beat frequency reference signal having a frequency f to yield an audio frequency Doppler signal having a frequency profile directly proportional to said systolic velocity.