Ultrasound high velocity flow correlation measurement using coded pulses

Abstract: An ultrasound high velocity flow measurement apparatus uses cross-correlation between consecutive echoes of coded pulses to determine velocity profiles of flowing blood. Because coded pulses are used, the interval between two pulses can be made arbitrarily small, effectively removing the peak velocity limitation. Matched filters are used to differentiate between the echoes.

Description: Field of the Invention The present invention relates to an ultrasound flow measurement apparatus and, more particularly, to an ultrasound high velocity flow measurement apparatus using time domain correlation. Background Information A primary use of ultrasound high velocity flow measurement apparatus is for blood velocity flow measurement and profiling. One conventional apparatus is known as an ultrasonic Doppler velocimeter. The Doppler velocimeter transducer emits a continuous or pulsed beam of ultrasound generally in the range of 1 to 10 MHz in peripheral and deep-lying vessels. The frequency of the returned signal, backscattered from moving red blood cells, is different from the frequency of the signal transmitted. The difference in frequency is known as the Doppler shift frequency, Δf, given by: Δf = 2fv cos(y) c where f is the transmitted frequency, v is the velocity of blood, y is the angle between the ultrasound beam and flow direction, and c is the velocity of sound in tissue. The velocity of the blood cells vary across the width of the vessel, and therefore, the Doppler signal is a spectrum rather than a single frequency. The Doppler-shift spectrum, therefore, depends of the velocity distribution of the blood across the vessel cross-section and the angle between the ultrasound beam and flow direction. The method of measurement utilizing the Doppler methodology, therefore, is sensitive to components that are parallel to ultrasound beams but are relatively insensitive to flow components that are parallel to the transducer. Another conventional apparatus used in performing the blood flow measurement and profiling is known as a cross-correlation velocimeter, which is described in IEEE Transactions on Ultrasonics, Ferroelectrics, and Frequency Control, Vol.37, No.3, May 1990, pages 164-175, in an article by S.G.Foster et al.: "Flow Velocity Profile via Time-Domain Correlation: Error Analysis and Computer Simulation". Ordinarily, in the conventional cross-correlation velocimeter, a single pulse is transmitted to a blood vessel from a transducer and the pulse's echoes are received before a second pulse is transmitted. Normalized cross-correlation is then used to determine a time shift (t₂-t₁) of a segment of the first echo with respect to a similar segment of a second echo of the second transmitted pulse. The magnitude of the velocity v of the blood at the distance corresponding to the penetration depth of a relevant segment of the first pulse is given by the following expression: v = c(t 2 -t 1 ) 2T PR cos(x) where c is the velocity of sound in the medium, T PR is a pulse repetition (PR) interval and x is the angle that the ultrasound beam makes with the blood vessel. This is shown in Fig. 1. The time difference (t₂-t₁) is determined by cross-correlating segments of two consecutive signals which carry the flow information. The pulse repetition interval is set by the depth of the body to the flow. Therefore, the larger the depth, the larger the pulse repetition interval. On the other hand, equation (1) illustrates that for a given (t₂-t₁), the larger T PR the smaller the velocity v that can be measured. Furthermore, when the velocity v is high, the larger T PR increases the chances for the signals from two successive signals to be de-correlated. This de-correlation results because either during the time T PR scatterers flow out of the ultrasound beam, or in the case of turbulent flow, due to the random nature of the flow, the scatterers change their relative position and therefore, the signal from two successive signals become de-correlated. Thus, the use of a conventional cross-correlation scheme for measuring high velocities at large depths presents two conflicting requirements. One requirement is a large pulse repetition interval so that the echoes can be separated between two successive signals. The second requirement is a small pulse repetition interval so that the signals remain correlated. The issue of de-correlation of signals is rather complex. De-correlation depends on the time repetition interval and the flow velocity. Beam geometry and diameter further play important roles in determining the de-correlation time. For a Gaussian beam with full width of w, the maximum measurable velocity at a pulse repetition time of T PR is: w/(3.5 T PR sin(x)) Fig. 2 illustrates this numerically. As shown in Fig. 2, a pulse repetition time of 200 microseconds is used. This implies that the maximum depth of the vessel has to be less than 150 mm inside the body. With this repetition time, a beam diameter of 1 mm yields a maximum measurable flow velocity of 2 m/s for a vessel that intersects the ultrasound beam at 45°. In cardiology or peripheral vascular applications of ultrasound, however, situations exist where measurements must be made with flow jets having velocities in excess of 10 m/s. Neither Doppler nor conventional cross-correlation schemes are capable of measuring such velocities. The conventional cross-correlation velocimeter discussed above utilizes single, or uncoded, pulses. Coded pulses, or frequency modulated pulses with frequencies that increase or decrease with time, however can be used in ultrasound apparatus. Coded pulses historically have been used in radar systems to increase power and decrease noise. In the general radar system, a ramp-up coded pulse, which is a frequency modulated pulse that has a frequency increase with time, or a ramp-down coded pulse, which is a frequency modulated pulse that has a frequency decrease with time, is transmitted to a target, and a resultant reflected signal is subsequently decoded utilizing a ramp-down or a ramp-up, respectively, decoding matched filter. Utilizing coded pulses increases the signal-to-noise ratio because a matched filter can suppress all signals except the appropriately coded pulse. SUMMARY OF THE INVENTION Accordingly, it is an object of the invention to provide an ultrasound high velocity flow correlation measurement apparatus that can accurately measure the blood flow measurement at high velocities and at large depth simultaneously. It is another object of the present invention to provide an ultrasound high velocity flow measurement apparatus that will improve the signal-to-noise ratio over that obtainable by use of uncoded pulses. Additional objects and advantages of the present invention will be set forth in part in the description that follows and in part will be obvious from the description or may be learned by practice of the invention. The objects and advantages of the invention are realized and obtained by the methods and apparatus defined in the appended claims. To achieve the objects and in accordance with the purpose of the invention as embodied and as broadly described herein, an ultrasound high velocity flow measurement apparatus using time domain correlation is defined in claim 1, and essentially comprises a modulator for producing at least two coded pulses, the at least two codes pulses being separated by a predetermined delay; a transducer for transmitting the at least two coded pulses to a measuring object; a receiver for receiving a returned echo signal from the measuring object; a decoder for decoding the returned echo signal and producing at least two decoded signals being separated by the predetermined delay; and a correlator for cross-correlating the two decoded signals and outputting a velocity profile of the measuring object. BRIEF DESCRIPTION OF THE DRAWINGS The accompanying drawings, which are incorporated in and constitute a part of the specification, illustrate a presently preferred embodiment of the invention and, together with the general description given above and the detailed description of the preferred embodiment given below, serve to explain the principles of the invention. Fig. 1 illustrates the geometry of the transducer and the blood vessel for which the velocity profile is determined; Fig. 2 illustrates the prior art method of determining velocity by cross-correlation; Fig. 3 is a graph illustrating the decoding of oppositely coded, linear-FM pulses that have been transmitted 0.9 microseconds apart; Fig. 4 is a graph illustrating the decoding of oppositely coded, linear-FM pulses that have been transmitted 0.9 microseconds apart, the transfer function for the velocimeter is approximated by a Hamming function; Fig. 5 is a graph illustrating the decoding of oppositely coded hyperbolic-FM pulses that have been transmitted 0.9 microseconds apart, the transfer function for the velocimeter is approximated by a Hamming function; and Fig. 6 is a functional block diagram illustrating a preferred embodiment of an ultrasound high velocity flow measurement apparatus using time domain correlation. DESCRIPTION OF THE PREFERRED EMBODIMENT Reference will now be made in detail to the presently preferred embodiment of the invention as illustrated in the accompanying drawings. Throughout the drawings, like reference characters are used to indicate like elements. The present invention uses cross-correlation between consecutive echoes of coded pulses to determine the velocity profile of flowing blood. As will be described in greater detail later, a preferred embodiment of the present invention transmits to the blood, in sequence, a coded pulse increasing in frequency and a coded pulse decreasing in frequency. The resultant reflected signals returning from the blood are subsequently separated by decreasing frequency decoding and increasing frequency decoding, respectively. The result from the decoding is decoded pulses that can be cross-correlated to determine the velocity profile. A method of velocity determination by cross-correlation according to a proposed embodiment of the present invention is based on the fact that inhomogenities in flowing blood give rise to distinctive echo patterns. As an inhomogenity moves through the ultrasound beam at an angle x with velocity magnitude v, the round trip time for pulses transmitted an interval T PR apart changes by the amount (t 2 -t 1 ) = (2T PR v cos(x))/c . This time change can be evaluated by cross-correlating segments of the echo from pulse 1 with the echo of pulse 2. If a band-limited, RF signal is digitized at a rate greater than the Nyquist rate, cross-correlation can be performed directly. If E₁(nΔt) is a sampled data for the first echo and E₂(nΔt) is a sampled data for the second echo, these echoes are written as follows where A(nΔt) is a time-dependent amplitude of the echo, f₀ is a carrier frequency, (nΔt) is a phase and (t₂-t₁) is a time shift: E 1 (nΔt) = A(nΔt) cos(2πf 0 nΔt + (nΔt)) E 2 (nΔt) = A(nΔt+t 2 -t 1 ) cos(2πf 0 nΔt+t 2 -t 1 ) + (nΔt+t 2 -t 1 )) The time shift (t₂-t₁) is equal to the value of ε for which Pearson's correlation coefficient P(ε) is equal to unity. P(ε)= N n N E 1 (nΔt) E 2 (nΔt-ε) - n N E 1 (nΔt) n N E 2 (nΔt-ε) N n N E 1 2 (nΔt) - n N E 1 (nΔt) 2 N n N E 2 2 (nΔt-ε) - n N E 2 (NΔt-ε) 2 Here, N is the number of samples in the segment of the pulse echo that is scattered by the inhomogenity. It is also possible to perform cross-correlation on quadrature detector output data which has been modulated with a carrier signal of frequency f₀. Let Q₁(nΔt) be sampled quadrature data for the first echo and Q₂(nΔt) be sampled quadrature data for the second echo. These echoes are written as follows, where j =√ -1 . Q 1 (nΔt) = 0.5 A(nΔt)e j(π/2 + (nΔt)) Q 2 (nΔt) = 0.5 A(nΔt+t 2 -t 1 )e j(π/2 + 2πf 0 (t2-t1) + (nΔt+t2-t1)) The time shift (t₂-t₁) is equal to the value of ε for which P Q (ε) is equal to unity. (* denotes the complex conjugate, | | denotes the absolute value, and the RE means "real part".) P Q (ε)= RE e j2πf 0 ε N n N Q 1 (nΔt) Q 2 * (nΔt-ε) - n N Q 1 (nΔt) n N Q 2 * (nΔt-ε) N n N |Q 1 (nΔt)| 2 - n N Q 1 (nΔt) 2 N n N |Q 2 (nΔt-ε)| 2 - n N Q 2 (nΔt-ε) 2 This value of time shift (t₂-t₁) is used in Equation (1) to obtain the magnitude of blood velocity at the depth corresponding to the inhomogenity. Continuous segments of the first pulse are used in the cross-correlation to obtain a profile of the velocity of the blood as a function of depth. If the blood flow is fairly constant, subsequent profiles can be averaged to reduce statistical fluctuations on the profile. A method of coding the pulses according to a preferred embodiment of the present invention utilizes matched filters. Matched filters have two basic characteristics. First, if a signal spectrum is described by S(ω), a frequency response function of a filter that results in a maximum signal-to-noise ratio at the filter output is the complex conjugate of the spectrum, S*(ω). Second, if a signal waveform is defined by s(t), where t is time, an impulse response of the filter meeting the first characteristic is s(-t), and the filter output waveform is found by performing the operation: p(t) = -∞ ∞ s(τ)s(t-τ)dτ . For purposes of illustration, coded pulses will now be discussed. A linear-FM matched-filter pulse is given by the following expression, where ω 0 = 2πf 0 is an angular, carrier frequency, t is time, Δf is a signal bandwidth, T is a pulse duration, and µ = 2πΔf/T . S LFM + (t) = rect t T cos ω 0 t+ µt 2 2 rect(x) = 1 |x| ≦ ½ 0 |x| > ½ The "+" sign indicates that the frequency of the linear-FM matched filter pulse increases linearly with time. For this pulse, a frequency spectrum is given approximately by the following expression: S LFM + (ω) ≃ 2π µ rect (ω - ω 0 ) Δω e - j(ω - ω 0 ) 2 2µ The frequency spectrum of the matched filter required for the decoding of Equation (9) is therefore of the form: H LFM + (ω) = e j (ω - ω 0 ) 2 2µ and the decoded signal is found by an inverse Fourier transform of the product P LFM + (t) ≃ √ T Δf rect t 2T cos(ω 0 t)sinc(Δft) At its maximum, the decoded signal P LFM (t) is larger than the original signal S LFM (t) by a factor √ TΔf , which is called the processing gain. This gain is usually expressed on the dB scale so that the gain is given as 10 log₁₀(TΔf)dB. This is the factor by which the signal-to-noise ratio of the signal is improved. The linear-FM matching filter pulse of Equation (9) shows a frequency increase as a function of time. This will be designated as a positive coded pulse. A linear-FM pulse matched filter pulse can be written for which the frequency decreases linearly as a function of time. This will be designated as a negative coded pulse. S LFM - (t) = rect t T cos(ω 0 t - µt 2 2 ). This negative coded pulse has a frequency spectrum given approximately by: S LFM - (ω) ≃ 2π µ rect (ω - ω 0 ) Δω e j(ω - ω 0 ) 2 2µ and the matched filter required for the decoding of equation (14) has the frequency spectrum: H LFM - (ω) = e -j(ω - ω 0 ) 2 2µ The decoded signal is found by a inverse Fourier transducer of the product The decoded waveforms have similar pulse shapes and processing gains. However, if the positive coded pulse is decoded by the negative matched filter, the result is a sinusoidal waveform with near-unity scaling. The converse is also true. Thus, each unmatched waveform is reduced by a factor 1/√ ΔfT relative to the matched waveform as a result of matched filtration. If both waveforms are incident simultaneously on one of the matched filters, only the corresponding pulse will be transmitted with significant magnitude. This affects a separation of the linear-FM signals. Equations (9)-(16) hold for signals transmitted without distortion. In an actual system, the decoded signal pulse is an inverse Fourier transform of the product S(ω)H(ω)T(ω) where T(ω) is the transfer function of the system. If T(ω) is significantly different from unity, the decoding will not be optimal. However, coded pulses transmitted by a system having a realistic transfer function can be cross-correlated successfully. Figs. 3 and 4 illustrate the effect the transfer function can have on linear-FM coded pulses. By way of illustration, the system transfer function is assumed to be approximated by a Hamming function. These figures simulate linear-FM chirp, ultrasound pulses reflected from three stationary point objects. In both Figs. 3 and 4, the dashed line represents the decoded, negative linear-FM pulse and the solid line represents the decoded, positive linear-FM pulse. The pulses have a duration T = 27 µseconds, but are transmitted only 0.9 µseconds apart, so that they are superimposed during transmission. The center frequency is f₀ = 4 MHz, and the bandwidth is Δf = 4 MHz. These illustrations have a discrete sampling interval of 0.03 µseconds. Fig. 3 shows the ideal decoded signals. The gain of the matched pulse over the background is about 20 dB. If the pulses were identical, the cross-correlation coefficient match between the two pulses would be perfect and a cross-correlation coefficient would be 1.0. In practice, however, a cross-correlation coefficient above about 0.7 is adequate for determining flow velocity profiles. The cross-correlation coefficient between the two pulses in Fig. 3 is about 0.96. Fig. 4 shows the signals when a Hamming filter is used to simulate the system transfer function. The gain has been reduced to about 17 dB by the mismatch introduced by the Hamming filter. However, the cross-correlation coefficient is still about 0.95. In the above discussion the principal operation of the coding inputs for the purpose of cross-correlation flow measurement was given. It is known, however, that when measuring a moving target the code on a reflected echo can be destroyed. Furthermore, when the velocity of the target is very high, the decoding of the echo may not be possible. The change in the code is primarily due to the Doppler effect. For an object approaching a transducer with a velocity v in a medium where the speed of sound is c, all the frequency components in the spectrum of the echo are multiplied by a factor of (1 + u) where u = 2v/c . Similarly, if the object is moving away from the transducer, all the frequency components are downshifted in frequency. For a blood flow velocity as high as 10 m/s and a c of 1550 m/s, u turns out to be 0.013 which although small, can cause problems in decoding. Because of these problems, a preferred embodiment of the present invention utilizes modified chirp signals, such as a hyperbolic-FM signals These signals have the form: S HFM ± (t) = rect t T cos ω 0 2 µ ln 1 ± µt ω 0 The frequency spectra of these waveforms are given by: S HFM ± (ω) = ω 0 ω 2π µ rect ω 0 Δω (ω 0 /ω-1) e - j ω(ω - ω 0 ) ±µ e - jω 0 2 ±µ ln(ω 0 /ω) The decoding filters have the form: H HFM ± (ω) = e - j(ω - ω 0 )ω ±µ e jω 0 2 ±µ ln(ω 0 /ω) If a hyperbolic-FM waveform is transmitted and reflected from a moving target, and, if the received signal is decoded in the matched filter, a resulting output signal will contain only the time-shifted term and the phase-shifted term. S R HFM ± (ω) = C rect ω 0 Δω ω 0 (1 + ν)ω -1 e - j ν ω ω 0 ±µ e jω 2 0 ±µ ln(1+ν) Fig. 5 illustrates the use of the hyperbolic-FM coded pulses. The conditions of Fig 4. apply except that the hyperbolic-FM pulses and their matched filters are used instead of the linear-FM pulses. The Hamming filter is used to simulate the system transfer function. The gain of the decoded hyperbolic-FM pulses is reduced only a little compared to the decoded linear-FM pulses, and the cross-correlation coefficient is about 0.97. A functional block diagram of a preferred embodiment of an ultrasound high velocity flow measurement apparatus using time domain correlation is shown in Fig. 6. According to the present invention, an oscillator 10 is connected to timing electronics 20, a positive modulator 30, a negative modulator 40, and mixers 130, 140, 150 and 160. Timing electronics 20 is connected to a positive modulator 30, a negative modulator 40, a timing gate 70, a timing gate 90, a positive decoder 110 and a negative decoder 120. The negative modulator 40 and the positive modulator 30, connected through a delay component 50, are connected to an adder 60 which, in turn, is connected to timing gate 70. The signal from timing gate 70 is applied to a transducer 80. A signal received from timing gate 90 is sent to the preamplifier 100, which in turn is connected to positive decoder 110 and negative decoder 120. Positive decoder 110 is connected to mixers 130 and 140. Negative decoder 120 is connected to mixers 150 and 160. Mixer 130 is connected to a low pass filter 180, mixer 140 is connected to a low pass filter 190 and to a shifter 170. Mixer 150 is connected to a low pass filter 200, and mixer 160 is connected to a low pass filter 210 and to shifter 170. Low pass filters 180, 190, 200 and 210 are connected to A/D converters 220, 230, 240 and 250, respectively. A/D converters 220, 230, 240 and 250 are connected to moving target indicators 260, 270, 280 and 290, respectively. Moving target indicators 260, 270, 280 and 290 are connected to the input of the complex cross-correlator 300. A presently preferred embodiment provides that the output of complex cross-correlator 300 is connected to an averager 310; however, the system can be used without the averager. The output of the averager 310 is connected to a display 320. Although no imaging system is shown, the velocimeter of the present invention also can be combined with imaging electronics to produce a duplex system. The combining of the velocimeter of the present invention with imaging electronics is considered to be apparent to those skilled in the art. Operation of the invention will now be explained with reference to the preferred embodiment illustrated in Fig. 6. A carrier signal is generated by the oscillator 10. The carrier signal produces a reference signal used by timing electronics 20, positive modulator 30, negative modulator 40, and mixers 130, 140, 150 and 160. Positive modulator 30 produces a positive hyperbolic-FM pulse which corresponds to the (+) form of Equation (17). This pulse is delayed by a time interval τ determined by delay component 50. Negative modulator 40 produces a negative hyperbolic-FM pulse which corresponds to the (-) form of Equation (17). The delayed, positive hyperbolic-FM pulse is added to the negative hyperbolic-FM pulse by adder 60. At appropriate intervals determined by timing electronics 20, both the delayed, positive and the negative hyperbolic-FM coded pulses are passed by timing gate 70 and are applied to transducer 80 and ultimately to the object being measured. After a time interval corresponding to a round trip echo from the object being measured, timing electronics 20 opens timing gate 90, allowing composite echoes comprising echo pulses of both the delayed, positive and the negative coded pulses, to pass into pre-amplifier 100 and then into positive decoder 110 and negative decoder 120. Positive decoder 110 effects convolution with a waveform having the frequency spectrum of the (+) form of Equation (19). Negative decoder 120 effects convolution with a waveform having the frequency spectrum of the (-) form of Equation (19). The output of positive decoder 110 is a compressed pulse of the form of the solid line in Fig. 5. The output of negative decoder 120 is a compressed pulse of the form of the dashed line in Fig. 5. These decoded pulses will be separated in time by the interval τ plus any time shift (t₂-t₁) caused by the motion of the targets. Both decoded pulses undergo quadrature detection. The output from positive decoder 110 is input to both mixer 130 and mixer 140. The output from negative decoder 120 is input to both mixer 150 and mixer 160. Mixer 130 multiplies the output from positive decoder 110 by the carrier signal produced by oscillator 10 to produce the real part of Equation (5). This signal is filtered by low-pass filter 180, sampled by A/D converter 220, passed through moving-target indicator 260 and input to complex cross-correlator 300. Mixer 140 multiplies the signal from positive decoder 110 by the phase shifted carrier signal output from shifter 170 to produce the imaginary part of Equation (5). This signal is filtered by low-pass filter 190, sampled by A/D converter 230, passed through moving-target indicator 270 and input to complex cross correlator 300. Mixer 150 multiples the output from negative decoder 120 by the carrier signal produced by oscillator 10 to produce the real part of Equation (6). This signal is filtered by low-pass filter 200, sampled by A/D converter 240, passed through moving-target indicator 280 and input to complex cross correlator 300. Mixer 160 multiplies the output from negative decoder 120 by the phase shifted carrier signal output from shifter 170 to produce the imaginary part of Equation (6). This signal is filtered by low-pass filter 200, sampled by A/D converter 260, passed through moving-target indicator 290, and input to complex cross-correlator 300. The complex cross-correlator 300 outputs the velocity profile given by Equation (1) as a function of depth. This profile passes into averager 310 for averaging, if desired, and then to display 320. The present invention may, therefore, be summarized as providing an ultrasound high velocity flow measurement apparatus using cross-correlation between consecutive echoes of coded pulses to determine velocity profiles of flowing blood. The interval between at least two coded pulses can be made arbitrarily small, and thus can remove the peak velocity limitation. Furthermore, the present invention improves the signal-to-noise ratio over that obtainable by use of uncoded pulses. It will apparent to those skilled in the art that modifications and variations can be made in the ultrasound high velocity flow correlation measurement apparatus of the present invention. The invention in its broader aspects is, therefore, not limited to the specific details, representative methods and apparatus, and illustrated examples shown and described herein. Thus, it is intended that all matter contained in the foregoing description and shown in the accompanying drawings shall be interpreted as illustrative and not in a limiting sense.

Claims: An ultrasound high velocity flow measurement apparatus using time domain correlation, comprising: modulator means (30-60) for producing at least two different coded pulses, the at least two different coded pulses being separated by a predetermined delay; transducer means (80) for transmitting the at least two different coded pulses to a measuring object; receiving means (90, 100) for receiving a returned echo signal from the measuring object; decoding means (110-290) for decoding the returned echo signal and producing at least two decoded signals being separated by the predetermined delay; and correlation means (300, 310, 320) for cross-correlating the two decoded signals and outputting a velocity profile of the measuring object. The apparatus as recited in claim 1, wherein the modulator means (30-60) includes a positive modulator means (30) for producing a positive-slope Doppler-insensitive coded pulse and a negative modulator means (40) for producing a negative-slope Doppler-insensitive coded pulse. The apparatus as recited in claim 2, wherein the modulator means (30-60) includes a delay means (50) for delaying the positive-slope Doppler-insensitive coded pulse by the predetermined delay, The apparatus as recited in claim 2, wherein the modulator means (30-60) includes an adding means (60) for adding the time delayed positive-slope and the negative-slope Doppler-insensitive coded pulses together. The apparatus as recited in claim 1, wherein the at least two different coded pulses are hyperbolic-FM coded pulses. The apparatus as recited in claim 1, wherein the receiving means (90, 100) includes a timing gate (90). The apparatus as recited in claim 6, wherein the receiving means (90, 100) includes a pre-amplifier (100). The apparatus as recited in claim 1, wherein the decoding means (110-290) includes a positive decoder (110) and a negative decoder (120). The apparatus as recited in claim 8, wherein the decoding means (110-290) includes two mixers (130, 140) connected to the positive modulator (110) and two further mixers (150, 160) connected to the negative decoder (120), low pass filters (180-210) connected to each of the mixers, A/D converters (220-250) connected to each low pass filter, and moving target indicators (260-290) connected to each A/D converter. The apparatus as recited in claim 1, wherein the correlation means (300, 310, 320) includes an averager (310) and a display (320). A method of measuring high velocity flow utilizing an ultrasound high velocity flow measurement apparatus using time domain correlation, comprising the steps of: producing at least two different coded pulses, the at least two different coded pulses being separated by a predetermined delay; transmitting the at least two different coded pulses to a measuring object; receiving a returned echo signal from the measuring object; decoding the returned echo signal and producing at least two decoded signals being separated by the predetermined delay; and cross-correlating the two decoded signals and outputting a velocity profile of the measuring object. The method of claim 11, wherein the step of producing at least two different coded pulses includes producing a positive hyperbolic-FM pulse and a negative hyperbolic-FM pulse. The method of claim 11, wherein the step of decoding the returned echo signal includes quadrature detection.

Inventors: NIKOONAHAD MEHRDAD, SILVERS ERLVADA ANNE, NIKOONAHAD, MEHRDAD, SILVERS, ERLVADA ANNE
Applicants: TOSHIBA KK, KABUSHIKI KAISHA TOSHIBA
Application year: 1992
Main classification: A61B8
IPC codes: G01S15, G01F1, A61B8, G01P5