Ultrasonic doppler blood flowmeter

Abstract: Disclosed is an ultrasonic Doppler blood flow-meter in­ tended to measure the velocity of blood flow at an arbitrary position of the body of a subject by making use of Doppler shift of an ultrasonic echo signal. The echo signal including Doppler shift from the blood flow of the body is detected in phase on the basis of standard reference signal, and the dis­ tance to an intended position is extracted from the phase detected signal and is integrated, and the direct-current com­ ponent or ultralow frequency component of the Doppler shift signal obtained from the integrating means is fed back nega­ tively to the integrating means. As a result, the echo signal components of the body tissues are removed, and the fre­ quency of blood flow only can be analyzed, so that an accurate blood flow information may be obtained.

Description: This invention relates to an ultrasonic Doppler blood flowmeter used in the measurement of the velocity of blood flow at an arbitrary position within the body of a subject in the medical field. Recently, the ultrasonic Doppler blood flowmeter is used in medical field for use in the cardio vascular system. Its operation depends on the principle that the ultrasonic wave transmitted into the body undergoes a frequency shift due to the Doppler effect which occurs when the wave in reflected by a moving substance such as blood flow, and by indicating the Doppler shift frequency corresponding to the rate of blood flow, the distribution of the rate of blood flow in the body can be easily observed from the surface of the body. Such ultrasonic Doppler blood flowmeter is disclosed, for example, in IEEE, Trans. S.U., SU-17 (3), p.170, 1970. Referring now to FIG. 1, the conventional ultrasonic Doppler blood flowmeter is described below. In this diagram, numeral 101 is an ultrasonic transmission and reception means (probe) which transmits ultrasonic pulses into the body from an ultrasonic transmission/reception plane 101a, and receives an echo signal reflected due to difference in the acoustic impedance, and generally it is made of a piezoelectric material. Numeral 102 is a drive circuit which generates the drive voltage for generating ultrasonic pulses to be transmitted from the probe 101 at the timing of external trigger and frequency of external clock, and drives the probe 101; 103 is a transmission timing circuit which gives the timing for the drive circuit 102 to generate a drive voltage as a trigger; 104 is a phase detector to detect the phase of the echo signal received by the probe 101; 105 is a reference signal generating circuit to serve as the reference of frequency and phase of reference signal when detecting the phase of the transmission signal and echo signal of the drive circuit 102 by means of phase detector 104; 106 is a gate signal generating circuit which generates a gate signal at the timing corresponding to the propagation time of the ultrasonic wave up to the transmission/reception plane of the probe 101 and desired position; 107 is an analog switch which causes to pass the phase signal detected by the phase detector 104 through the interval of the gate signal generated by the gate signal generating circuit 106; 108 is an integrating circuit which integrates the phase signal passing through the analog switch 107, determines the sum of phase signals, and repeats transmission and reception to obtain a Doppler shift signal; 110 is a sample hold circuit which holds the result integrated for resetting until the result of next integration is obtained prior to integration by the integrating circuit 108; 111 is a high pass filter which removes signals of less than several hundred hertz from the Doppler shift signal obtained in the integrating circuit 108; 112 is a frequency analyze which analyzes the frequency of the Doppler shift signal passing through the high pass filter 111; and 113 is a display unit which indicates the result of frequency analyzer 112. While referring to the time chart shown in FIG. 2, its action is described below. In the transmission timing circuit 103, trigger signals T of constant or arbitrary intervals are generated (a), and are applied to the drive circuit 102. The drive circuit 102 drives the probe 102 by the trigger signals T in drive pulse TX (b), and ultrasonic pulses are transmitted from this probe 101 into the body. The ultrasonic pulses propagate within the body, and are reflected by the parts differing in the acoustic impedance, and return to the probe 101, being received as echo signals E (c). The echo signals E are obtained as delay time t d from t o of trigger signal T, corresponding to the reciprocal propagation time of the ultrasonic wave from the transmission/reception plane 101a of the proble 101 to the reflecting point of the transmitted ultrasonic pulse, and since the echo signals from a moving reflecting body always vary in the reciprocal propagation time, t d also changes. Supposing the variation of propagation time changing within the period of trigger signal T to be Δt d and echo signal intensity to be A, the echo signal E obtained by the n-th transmission/reception is expressed in the following equation. E = Acos {ω(t d + n · Δt d ) (1) This is orthogonally detected by the reference signal R (d) to be mentioned below by the phase detector 104. The reference signal is avaialble, though not shown, as V X and V Y which are uniform in amplitude but mutually different in phase by 90° from time t o of trigger signal T, which are expressed as follows. V X = cosωt d V Y = sinωt d (2) By the phase detector 104, the following signals are obtained by multiplying V X , V Y of eq. (2) by E of eq. (1). E · V X = (A/2) · {cos(ωnΔt d ) + sin(2ωt + ωnΔt d )} E · V Y = (A/2) · {sin(2ωt + ωnΔt d ) - sin(ωnΔt d )} (3) Two signals C (e) of eq. (3) obtained in the phase detector 104 are integrated in the integrating circuit 108 by turning on the analog switch 107 in the period of t₁ to t₂ of gate signal G (f) generated by the gate signal generating circuit 106. The signal C (e) expressed in eq. (3) is composed of two signal components (wnΔt d ) and (2ωt + wnΔt d ) , and the former does not contain parameter t of time and is a direct-current signal, while the latter is a high frequency signal with the frequency twice as high as the transmission frequency ω. Therefore, by passing through the integrating circuit 108, the latter component is eliminated, and the Doppler shift signal X, Y obtained as a result at the integration end time t₂ are as follows. X = (A/2)·K·t G ·cos(ωnΔt d ) (4) Y = -(A/2)·K·t G ·sin(ωnΔt d ) (4) where K is a constant determined by the circuit constant of integrating circuit 108, and t G is a time width of gate signal G. The gate signal G is intended to match with the time t₁ to t₂ when the echo signal from a desired position of the body is received, and the integration results X, Y received the n-th time contain all of echo signal information between t₁ and t₂ (g). The voltages of integration results X, Y are held by the next sample hold circuits 110 as indicated by the broken line (h) until the next n+l time integration result is obtained. The integrating circuit 108 is reset when holding of the sample hold circuits 110 is over. Thus obtained integration result is a direct-current voltage, as clear from eq. (4), when transmitted and received only once, but as the transmission and reception are repeated every period T of trigger signal, n increases, and X, Y continue to change while keeping a phase difference of 90°. This is an orthogonal Doppler signal, supposing, for example, X to be a real part signal and Y to be an imaginary part signal. Both X and Y are obtained as discrete information at every period T, and the following relation is established between the delay time amount Δt d varying in interval T from the n-th time transmission/reception and n+l time transmission/reception. Δt d = (2vT)/C (5) Therefore, from eqs. (4) and (5), the deviation frequency f d of Doppler shift signals X, Y is expressed as follows. f d = (2·v·f·cosϑ)/C (6) where C is the speed of sound propagation in the body, f is reference signal frequency (which is generally equal to the transmitted ultrasonic pulse frequency), and ϑ is the angle formed by the moving direction of the reflecting substance and ultrasonic wave running direction. In the body, when an echo signal from blood flow is captured, since the intensity of reflection by the blood flow is very small, the amplitude of Doppler shift signal is extremely weak, while the rate of blood flow is fast, so that the deviaiton frequency f d becomes high. In the body tissues such as viscera, the intensity of reflection A is high, and the movement is slow by the internal body movement or the like, and the deviation frequency f d is very low. By passing it through the high pass filter 111, only the Doppler shift signal from the blood flow having a small amplitude and high frequency can be obtained. To remove the Doppler shift signal from the body tissues is very important for expanding the dynamic range of frequency analyzer 112, and it is generally set at 100 to 1 kHz. In the frequency analyzer 112, the Doppler shift signals X, Y are analyzed in frequency, and the direction of the blood flow is determined from the phase relation of two signals, and is displayed in the display unit 112 as blood flow pattern. However, as compared with trigger signal T shown in FIG. 3 (a), the echo signal E is roughly divided into the very intense portion b from the body tissues appearing to be nearly standstill as shown in FIG. 3 (b), and the feeble portion a from the blood flow which is always moving. To measure the rate of blood flow, it is necessary to amplify the feeble echo signal portion a from the blood flow with a large gain, and with the feeble echo signal from the blood flow alone, the real part signal Xa and imaginary part signal Ya having only alternating-current components are obtained in the integrating circuit 108 in the amplitude of up to amplitude limit V of the integrating circuit (c). When the setting of measuring point is at the intense echo signal portion b from the body tissue, the phase difference of reference signal R and echo signal E is always constant or changes very slowly, and at the output of the integrating circuit 108, the direct-current component or the alternating-current component of real part signal Xb and imaginary part signal Yb with a very slow change appears (d). In the actual clinical application, since the ultrasonic beam transmitted from the probe 101 has a spread, if a blood vessel smaller in diameter than the beam diameter is captured, echo signals from the blood flow and body tissue may often exist at the same time, and conventionally, the effect of the body tissue was eliminated by using a wall filter 111. However, when a relatively shallow measuring point is observed, for instance, the real part signal Xa and imaginary part signal Ya are superposed on the real part signal Xb and imaginary part signal Yb, resulting in Xc and Yc (e). But because of the amplitude limit V of the integrating circuit 108, the portion indicated by shaded area clips, and the waveform is distorted. When the direct-current component is small and saturation is not caused, it is possible to remove the direct-current component by the conventional high pass filter 111, but when measuring the blood flow in relatively superficial carotid artery or deep-seated fine blood vessels, the echo signal from the body tissue around the blood vessel is particularly intense due to spread of the ultrasonic beam, and the direct-current component increases particularly. As a result, the integrating circuit 108 is saturated by this direct-current component alone, and Doppler shift signal does not appear. Therefore, if the direct-current component is removed by the high pass filter 111, Doppler shift signal cannot be obtained, and the result of frequency analysis involves unnecessary frequency components, or the result of analysis is suspended. Or, if either Doppler shift signal X or Y is saturated, information about the direction of blood flow cannot be obtained, which was a serious problem clinically. The change of time t G while gate signal G is ON influences the shut-off frequency fc, and the low frequency component decreases as the gate width is wider, so that the obtained blood flow information varies depending on the gate width at the same location. Generally, the frequency of the high pass filter 111 is set by the physician before use depending on the diagnostic condition, and the set frequency is shown on the operation panel or display unit of the apparatus, but the shut-off frequency fc of the integrating circuit affects the shut-off frequency of the high pass filter, and the displayed set frequency is no longer correct. Thus, depending on the gate width, the obtained information differs, and the displayed set frequency is not correct, and the accuracy as diagnostic data is lowered, and the reproducibility is inferior, and the result of diagnosis may differ depending on the gate width, which posed serious problems. US 4255977 shows a device comprising pulsed Doppler velocimeter 7 and a phase-locked loop which consists primarily of voltage controlled oscillator, phase sensitive detector, wide bandwidth low-pass filter, and narrow bandwidth low-pass filter. In this device, a Doppler shift signal from a living body is detected by the pulsed doppler velocimeter, and the phase of the Doppler shift signal and the phase of the signal generated by the VCO are compared by the phase sensitive detector. Then, the phase difference voltage between these two signals is extracted by either the wide bandwidth low-pass filter or the narrow bandwidth low-pass filter, and this is utilized to control the frequency of the signal generated by VCO. Therefore, the frequency of the signal generated by the VCO is maintained at the frequency of the Doppler shift signal, and thus, a reasonably high S/N ratio can be achieved so that the measurement of the blood flow at a position deep in the living body becomes possible. Furthermore, the wide bandwidth low-pass filter and the narrow bandwidth low-pass filter in this document are low pass filters provided to ensure a stabilized operation of the PLL. By means of PSD, the phase difference signal between the Doppler shift signal derived by the pulse Doppler velocimeter and the signal from the VCO is extracted, and by this, the VCO is controlled to make its oscillating frequency equal to the Doppler shift frequency. The present invention provides an ultrasonic Doppler blood flowmeter comprising an ultrasonic transmission means adapted to transmit ultrasonic pulses into the body of a subject, an ultrasonic reception means adapted to receive echo signals reflected from within the body, drive circuitry arranged to cause ultrasonic pulses to be transmitted by said ultrasonic transmission means, transmission timing signal circuitry arranged to output signals to control the timing of the drive circuitry, a phase detector arranged to detect the phase of echo signal obtained by said ultrasonic reception means, reference signal generation circuitry arranged to output a reference signal to the phase detector to be a reference in the detection of the frequency and phase of the transmission signal transmitted by said transmission means and said echo signal, gate signal generating circuitry adapted to generate a gate signal at a time corresponding to the echo signal from a particular position, control means responsive to said gate signal and adapted to pass the phase signal from said phase detector during said gate signal, and integrating circuitry arranged to obtain a Doppler shift signal by integrating said phase signal passing through said control means; characterized by further comprising direct-current feedback circuitry adapted to negatively feed back the direct-current and ultra low-frequency components of the Doppler shift signal output from the integrating circuitry such that it is applied to the input of the integrating circuitry. This invention therefore aims to solve the above-discussed problems of the prior art, and a primary advantage of this invention is the provision of an ultrasonic Doppler blood flowmeter capable of analysing the frequency of the blood flow only and obtaining an accurate blood flow information, by removing the direct-current components generated by the echo signals of body tissues from the real part output and imaginary part output delivered from the integrating circuit. Another advantage of this invention is the provision of an ultrasonic Doppler blood flowmeter capable of diagnosing accurately by using the blood flow information and high pass filter characteristics being completely free from effects of the gate width. BRIEF DESCRIPTION OF THE DRAWINGS FIG. 1 is a block circuit diagram showing a conventional Doppler blood flowmeter; FIG. 2 is a time chart showing the operation of the same flowmeter; FIG. 3 is an integrated waveform obtained by using the same flowmeter; FIG. 4 is a block diagram representing one of the embodiments of an ultrasonic Doppler blood flowmeter according to this invention; FIG. 5 (a) is a practical circuit diagram in an embodiment of the essential parts of the same flowmeter, FIG. 5 (b) is a time chart showing the operation of the same circuit in FIG. 5 (a), FIG. 5 (c) is a practical circuit diagram in a different embodiment of the essential parts of the same flowmeter, FIG. 5 (d) is a time chart showing the operation of the same circuit in FIG. 5 (c), and FIG. 5 (e) is a diagram showing the frequency characteristics of the circuits in FIG. 5 (a) and (c); FIG. 6 is a diagram to compare the integrated waveforms between this invention and the prior art; FIG. 7 is a block circuit diagram showing an ultrasonic Doppler blood flowmeter in a different embodiment of this invention; FIG. 8 shows frequency characteristics of direct-current feedback circuit and integrating circuit of the same flowmeter, (a) being a frequency characteristic diagram of the direct-current feedback circuit and (b) being a frequency characteristic diagram of the integrating circuit with negative feedback applied; FIG. 9 (a) and (b) are practical circuit diagrams showing the integrating circuit, direct-current feedback circuit, and feedback gain control circuit in a further different embodiment of the ultrasonic Doppler blood flowmeter of this invention; and FIG. 10 (a) is a practical circuit diagram showing the integrating circuit, direct-current feedback circuit, and feedback gain control circuit in a still further embodiment of the ultrasonic Doppler blood flowmeter of this invention, and FIG. 10 (b) is an operation timing chart of (a). DETAILED DESCRIPTION OF THE INVENTION FIG. 4 is a block diagram of an ultrasonic Doppler blood flowmeter in one of the embodiments of this invention. The ultrasonic Doppler blood flowmeter of this invention possesses a direct-current feedback circuit 9 for negatively feeding back the direct-current and ultralow frequency components of the orthogonal signal delivered by the integrating circuit or sample hold circuit in the above conventional ultrasonic Doppler blood flowmeter into the input of the integrating circuit of way of an analog switch. That is, numeral 1 is an ultrasonic transmission and reception means (hereinafter called a probe) which transmits an ultrasonic pulse into the body from its ultrasonic transmission/reception plane 1a, and receives the echo signal reflected due to difference in the acoustic impedance, and it is generally made of piezoelectric material. The probe 1 may be either transmission/reception combination type or transmission and reception separate type. Numeral 2 is a drive circuit which drives the probe 1 by generating the drive voltage for generating ultrasonic pulses transmitted from the probe 1 at the frequency of external clock and timing of external trigger. Numeral 3 is a transmission timing signal which gives the timing for the drive circuit 2 to generate the drive voltage as trigger. Numeral 4 is a phase detector which detects the phase of echo signal received by the probe 1. Numeral 5 is a reference signal generating circuit which serves as the reference for frequency and phase of the reference signal when detecting the phase of the transmission signal and echo signal of the drive circuit 2 by means of the phase detector. Numeral 6 is a gate signal generating circuit which generates a gate signal at the time corresponding to the propagation time of the ultrasonic wave up to the transmission/reception plane 1a of the probe 1 and an intended position. Numeral 7 is an analog switch which causes to pass the phase signal and direct-current feedback voltage detected by the phase detector 4 through the period of gate signal generated by the gate signal generating circuit 6. Numeral 8 is an integrating circuit which integrates the phase signal passing through the analog switch 7, determines the sum of phase signals, repeates transmission and reception, and obtains Doppler shift signals. Numeral 10 is a sample hold circuit which holds the result integrated for resetting until the next integration result is obtained prior to integration by the integrating circuit 8. Numeral 9 is a direct-current feedback circuit which negatively feeds back the direct-current component and ultralow frequency component of Doppler shift signal delivered from the integrating circuit 8 or sample hold circuit 10 to the integrating circuit 8 by way of the analog switch 7. Numeral 11 is a high pass filter which removes signals of less than several hundred hertz from the Doppler shift signal obtained in the integrating circuit 8. Numeral 12 is a frequency analyzer which analyzes the frequency of the Doppler shift signal passing through the high pass filter 11. And numeral 13 is a display unit to shows the result of the frequency analyzer 12. The operation of this embodiment is described below. In this embodiment, too, the echo signal is orthogonally detected according to the route explained in the conventional example in FIGS. 1 and 2, and is dispalyed after frequency analysis. Here, the integrating circuit 8 is negatively fed back by the direct-current components of real part signal X and imaginary part signal Y after integration, and it works as high pass filter in ultralow frequency region. FIG. 5 (a), (c) depict examples of practical circuits of the analog switch 7, integrating circuit 8, sample hold circuit 10, and direct-current feed-back circuit 9 as shown in the embodiment in FIG. 4, and FIG. 5 (b), (d) denote signal waveforms at each terminal of FIG. 5 (a), (c). The circuit in (a) or (c) requires one system for real part signal X and imaginary part signal Y respectively, but only one is shown in the diagram. The circuits in (a) and (c) produce exactly the same effect. As a first embodiment, the operation of the circuit in (a) is explained below while referring to FIG. 5 (b). The integrating circuit 8 in FIG. 4 is composed of, as shown in FIG. 5 (a), an inverting amplifier OP₁ having a degree of amplification of -A₁, a resistance R₁, and capacitor C₀, and it has two input terminals, that is, E i to which the output of phase detector 4 (see FIG. 4) is applied, and to which a direct-current feedback voltage of direct-current feedback circuit 9 is applied, and the signals of both terminals are added immediately before the analog switch 7, and are integrated when the analog switch 7 is ON. The analog switch 7 is tunred on in the period of t₁ to t₂ of gate signal G, and the signals are integrated for the time t g , and a wave-form as shown in the drawing is obtained at the input terminal (output of integrating circuit) of direct-current feedback circuit 9. The sample hold circuit 10 has a gain of -A, and samples from t₂ when the integration is over to time t ω , and holds the sample after t₃. After holding, the integrating circuit, prior to next transmission and reception, turns on the analog switch 7' to discharge C₀ for the period of t₃ to t₄ by means of RESET signal, and is reset. At the output terminal E₀ of the sample hold circuit 10, a Doppler signal discreted in period T appears as shown in the diagram, and is applied to the next high pass filter 11 (see Fig. 4). On the other hand, the direct-current feedback circuit 9 makes up a low pass filter by means of inverting amplifier OP₃, capacitor C f and resistance R f , and direct-current and ultralow frequency components are extracted from the output signal of the integrating circuit applied to and are negatively fed back through resistance R₂. The inverting amplifier OP₂ has a gain of -A f , and is intended to invert the phase. Therefore, the lower the frequency of the output of the integrating circuit, the more increases the feedback amount, and the integration result becomes smaller. Such input, output characteristics of the circuit may be obtained as follows. Equation (7) refers to the relation among the mean voltage l i of output of phase detector within gate time t g applied to input terminal E i , direct-current feedback voltage applied to input terminal and integrating circuit output and eq. (8) refers to the integrating circuit output and direct-current feedback voltage applied to the direct-current feedback circuit 9. In eq. (8), ω is the frequency of Doppler shift signal delivered to the integrating circuit, and (t g /K + t ω )/T is the duty ratio of the Doppler shift signal existing discretely in every period T, and in the integration time of t₁ to t₂, its value is less than 1 to correct the duty ratio in this duration because it is in the transient state until From eqs. (7), (8), the gain A v of circuit in FIG. 5 (a) becomes as follows. Incidentally, the -3 dB low range shut-off frequency f c in eq. (9) is expressed as follows. The value of f c should be selected at a frequency to allow to pass the Doppler shift signal by blood flow sufficiently and inhibit Doppler shift signal due to internal movement of the body, and in an ordinary ultrasonic pulse Doppler blood flowmeter with ultrasonic pulse frequency of about 2 to 7 MHz, it should be properly selected at 50 to 500 Hz. As a second embodiment, the operation of the circuit in FIG. 5 (c) is explained below while referring to (d). The principal construction and operation are same as in the first embodiment explained in (a), except that the output of the sample hold circuit 10 is applied to the integrating circuit, as compared with the first embodiment in (a) wherein the output of the integrating circuit is applied to the input of the integrating circuit through the analog switch 7 by the direct-current feedback circuit 9. Incidentally, the inverting amplifier OP₂ used in the first embodiment is not needed because the sample hold circuit 10 fulfills this function in this embodiment, The input and output characteristics of this circuit are obtained as follows. Equations (11) and (12) correspond respectively to eqs. (7) and (8), from which the gain A v of the circuit in FIG. 5 (c) is expressed as follows. Meanwhile, the -3 dB low range shut-off frequency f c in eq. (13) is expressed in the following equation. The value of f c is determined same as in FIG. 5 (a), and FIG. 5 (e) describes the frequency characteristics of the circuits in FIG. 5 (a) and (c). As shown in the diagram, only the effects of the body tissues can be eliminated, and a frequency f c free from adverse effects on the detection of Doppler shift from the blood flow can be selected, so that only the alternating-current components which are Doppler shift signals can be delivered to the subsequent circuits without integrating the direct-current components. Thus, the Doppler shift signals appearing at the orthogonal signals X, Y being rid of direct-current components are completely free from influences if signals from the body tissues are received simultaneously in the echo signals. FIG. 6 shows the output waveforms of the integrating circuit 8 of this embodiment and the prior art. The solid line refers to this invention, and the broken line denotes the prior art, and the shaded area is the portion of the waveform being cut off by saturation. As shown in the diagram, by executing this invention, the amplitude limit is expanded, and there occurs no effect of direct-current voltage, so that a very fine blood vessel can be measured, without saturating the integrating circuit 8, and that the amplitude of the Doppler shift signal can make use of the amplitude limit V to the maximum extent. As explained above, by the ultrasonic Doppler blood flowmeter of this invention, since the direct-current component and ultralow frequency component of Doppler shift signal obtained from the integrating circuit are negatively fed back by the direct-current feedback circuit, if an echo signal without time change from the body tissue is captured at the same time with an echo signal from blood flow, in this simple circuit composition, the frequency of blood flow only can be analyzed, and no other display that the blood flow appears on the blood flow pattern on the display unit, so that an accurate information about the direction of blood flow can be obtained. FIG. 7 is a block circuit diagram of an ultrasonic Doppler blood flowmeter in another embodiment of this invention. This embodiment involves a feedback gain control circuit which controls the feedback gain of direct-current feedback circuit 9 in the composition in FIG. 4, depending on the gate width information set in the gate signal generating circuit 7. The other structure and operation are same as in FIG. 4. The high pass filter of integrating circuit 8 has the characteristic as shown in FIG. 8 (b), but by expanding the gate time t G , the duration of the application of feedback signal to the integrating circuit 8 in extended, and the same effect as when the gain of the direct-current feedback circuit 9 is increased is produced, which causes to shift the characteristic 1 in FIG. 8 (a) toward the direction P to become characteristic 2, which results in the characteristic 2 of the integrating circuit of (b). To keep the frequency characteristic of integrating circuit 8 at curve 1, as the gate width expands, the gain of the direct-current feedback circuit 9 is lowered to correct in the direction of P'. Or, by lowering the shut-off frequency of the direct-current feedback circuit 9 and correcting the characteristic in the direction of Q', the increase of the gain of direct-current feedback circuit 9 due to expansion of gate width is canceled, so that the shut-off frequency f c may be kept constant. When the gate width is shortened, similarly, it is enough to correct the characteristic of direct-current feed-back circuit 9 in the direction of P or Q. The feedback gain control circuit 14 is responsible for such correction, and it controls the degree of amplification A f of the entire direct-current feedback circuit 9, corresponding to the set gate width, that is, time t G while analog switch 7 is ON, by determining according to the following equation. Afocl/t G (15) FIG. 9 (a), (b) relate to an embodiment of circuit structure for correcting the above-mentioned shut-off frequency, in which (a) is designed to correct the gain of direct-current feedback circuit 9 by means of gain variable amplifier 9a according to eq. (15), while (b) is to change the shut-off frequency of the direct-current feedback circuit 9, and the resistance Rf is changed in this case. In FIG. 8 (a), when the gate width is extended, the characteristic 1 moves toward the direction of P, and it is corrected by moving to the direction of Q', by lowering the shut-off frequency. Besides, it is also possible to correct by varying the capacitor Cf or resistance R₂. FIG. 10 (a) refers to a further different embodiment, in which 14a is an analog switch to turn on and off the Doppler shift signal fed into the direct-current feedback circuit 9, and the feedback gain control circuit 14 control the time width t f in which the analog switch 14a is ON by the gate width t G . FIG. 10 (b) shows the control timing of analog switch 14a. Its operation is described below. Same as in the preceding embodiments, the Doppler shift signal appearing at output E₀ is extracted of its ultralow frequency components in the direct-current feedback signal 9, and is fed back in reverse phase, but at the input of direct-current feedback circuit, the analog switch 14a is connected, and by controlling the duty ratio t f /T of the gain control signal G f generated depending on the gate width t G by the feedback gain control circuit 14, the entire gain of the direct-current feedback circuit 9 is varied and corrected. Thus, by the ultrasonic Doppler blood flowmeter of these embodiments herein, by applying a gain depending on the gate width to the direct-current feedback circuit by the feedback gain control circuit, the shut-off frequency of the integrating circuit may be kept constant regardless of the gate width, and measurement of the rate of blood flow being free from the effects of the Doppler shift signal from the body tissues can be effected in the same conditions regardless of the gate width, and its clinical effect is extremely notable.

Claims: An ultrasonic Doppler blood flowmeter comprising an ultrasonic transmission means (1) adapted to transmit ultrasonic pulses into the body of a subject, an ultrasonic reception means (1) adapted to receive echo signals reflected from within the body, drive circuitry (2) arranged to cause ultrasonic pulses to be transmitted by said ultrasonic transmission means (1), transmission timing signal circuitry (3) arranged to output signals to control the timing of the drive circuitry (2), a phase detector (4) arranged to detect the phase of echo signal obtained by said ultrasonic reception means (1), reference signal generation circuitry (5) arranged to output a reference signal to the phase detector to be a reference in the detection of the frequency and phase of the transmission signal transmitted by said transmission means (1) and said echo signal, gate signal generating circuitry (6) adapted to generate a gate signal at a time corresponding to the echo signal from a particular position, control means (7) responsive to said gate signal and adapted to pass the phase signal from said phase detector (4) during said gate signal, and integrating circuitry (8) arranged to obtain a Doppler shift signal by integrating said phase signal passing through said control means (7); characterized by further comprising direct-current feedback circuitry (9) adapted to negatively feed back the direct-current and ultra low-frequency components of the Doppler shift signal output from the integrating circuitry (8) such that it is applied to the input of the integrating circuitry (8). The ultrasonic Doppler blood flowmeter of Claim 1, wherein the feedback circuitry (9) is arranged such that the feedback signal is fed back to the input terminal of the control means (7). The ultrasonic Doppler blood flowmeter of Claim 1, wherein the ultrasonic transmission means (1) and the ultrasonic reception means (1) are formed by one ultrasonic probe (1). The ultrasonic Doppler blood flowmeter of Claim 1, further comprising a sample hold circuit arranged to hold temporarily the integrated result obtained in the integrating circuitry (8). The ultrasonic Doppler blood flowmeter of Claim 4, wherein the feedback circuitry (9) is arranged to derive said feedback signal from either the output of the integrating circuitry or the output of the sample hold circuit. The ultrasonic Doppler blood flowmeter of Claim 1, further comprising feedback gain control circuitry arranged to control the gain of the feedback circuitry either in proportion to the period of said ultrasonic pulses, or in reverse proportion to the period of the gate signal generated by said gate signal circuitry. The ultrasonic Doppler blood flowmeter of Claim 1, wherein the direct-current feedback circuitry comprises a low pass filter including further integrating circuitry. The ultrasonic Doppler blood flowmeter of Claim 1, wherein the direct-current feedback circuitry comprises a low pass filter including further integrating circuitry and a gain variable amplifier for controlling the gain. The ultrasonic Doppler blood flowmeter of Claim 1, wherein the direct-current feedback circuitry comprises a low pass filter including further integrating circuitry and a time constant control circuit arranged to control the time constant of said further integrating circuitry. The ultrasonic Doppler blood flowmeter of Claim 1, wherein the direct-current feedback circuitry comprises a low pass filter including further integrating circuitry and a chopper circuit adapted to turn on and off the input of said further integrating circuitry. The ultrasonic Doppler blood flowmeter of Claim 1, wherein the control means is an analog switch.

Inventors: KAWABUCHI MASAM, NAKAMURA YASUHIRO, KAWABUCHI, MASAM, NAKAMURA, YASUHIRO
Applicants: MATSUSHITA ELECTRIC IND CO LTD, MATSUSHITA ELECTRIC INDUSTRIAL CO., LTD.
Application year: 1986
Main classification: A61B8
IPC codes: A61B8