JPH08154939A - Ultrasonic imaging display method and ultrasonic imaging apparatus - Google Patents

Abstract

PURPOSE: To enable display allowing identification of a palmic stream or a steady stream concerning a blood stream by performing a delay addition at an interval larger than the sampling interval of the same sound beam data of a reflection signal width of a moving object to obtain flow velocity data and an ultrasonic imaging display is made by a color flow mapping. CONSTITUTION: (i) and (q) signals are filtered with MTI filters 400 and 401 to extract a reflection signal of a moving object and supplied to delay sections 402 and 403 with a delay time of Δt. Here, the delay time Δt is set to be an interval at which a signal of the same sound beam is received by a transmitting/ receiving section. Then, a delayed signal is multiplied by a signal not delayed using multipliers 405-408. Moreover, addition or subtraction is performed with an adder 409 or a subtractor 410. A square addition processing is performed by a power calculation section 404 to determine a cumulative mean at each Δt with a delay adder 411 and an average velocity is determined by an average velocity calculating section 414 to obtain a scattering by a scattering calculation section 415. Thus, an image processing section 5 accomplishes a color display getting green or the like superimposed on red/blue varying luminance.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ultrasonic imaging display method and an ultrasonic imaging apparatus, and more particularly to an ultrasonic imaging display capable of displaying a pulsatile flow or a steady flow with respect to a blood flow in a distinguishable state. A method and an ultrasonic imaging apparatus.

[0002]

2. Description of the Related Art When an ultrasonic wave is applied to a subject, the ultrasonic wave is transmitted through a living tissue as a medium. However, there is a difference in acoustic impedance from tissues such as organs and surrounding tissues such as lesions. A part of the transmitted ultrasonic wave returns by being reflected and scattered by red blood cells in blood. When the reflector or scatterer is an object that moves or moves in the direction of the line of sight, the frequency of the reflected wave deviates from the transmission frequency due to the Doppler effect. The ultrasonic diagnostic apparatus is an apparatus for measuring the frequency shift amount, displaying and observing the velocity and moving direction of the moving object, and providing the diagnostic object.

When the reflector is moving toward the probe, the reception frequency is higher than the transmission frequency, and conversely, the reception frequency is low. The shift frequency is proportional to the moving speed of the reflector. Using this Doppler effect, for example, the direction and velocity of the blood flow in the heart or blood vessel can be known.

In this ultrasonic diagnostic apparatus, the moving direction of a moving object is displayed in colors such as red when approaching and blue when moving away, and the moving speed is displayed in brightness.
There is a device having an M (Color Flow Mapping) mode.

By the way, the reflection of the ultrasonic pulse includes both a fixed object and a moving object.
Especially when paying attention to a moving object, it is easier to understand by removing the reflection signal from the fixed object and displaying only the reflection signal of the moving object. For that purpose, MTI (Moving Target Indicator) that extracts only the reflection signal of the moving object. ) Is used.

However, the information about the fixed reflecting object also has important meaning in the medical ultrasonic diagnostic apparatus. It is not possible to specify what is in the display screen and what it does without the above information, and it is difficult to determine what it is by simply displaying a moving object.

Therefore, in order to display the display of a fixed object and the display of a moving object in common on the same screen and distinguish them from each other, the direction of the blood flow, the average velocity and the velocity dispersion value from the scattered echoes from the blood cells are displayed. Also, the power value and the like are calculated, and various quantities thereof are two-dimensionally displayed on the B mode screen in real time by color. This mode is called a CFM mode, and a device having these functions is a CFM ultrasonic diagnostic device.

FIG. 6 shows a block diagram of a conventional ultrasonic diagnostic apparatus having a CFM mode. In the configuration of FIG. 6, the ultrasonic probe 1 converts the transmitted electric signal into an ultrasonic wave and transmits the ultrasonic wave into the subject, and the ultrasonic signal reflected and returned from the inside of the subject is an electric signal. Convert to. The transmission / reception unit 2 amplifies the transmission signal and sends it to the ultrasonic probe 1, demodulates the received signal received by quadrature detection or the like, and then sends it to each processing unit. That is, the output (demodulation output (i, q signals, etc.)) of the transmission / reception unit 2 is supplied to the B-mode processing unit 3 and the CFM calculation unit 4, respectively.

The B-mode processing unit 3 performs amplification, logarithmic compression, detection, etc., outputs a signal for B-mode display, and supplies it to the image processing unit 5. The demodulated output of the transmitter / receiver 2 is input to the CFM calculator 4. The CFM calculation unit 4 extracts the reflected wave of only the moving target by using the MTI filter or the like, and extracts the reflected wave from the blood flow, for example, to calculate the blood flow velocity. Also, due to variations in blood flow rate,
Detect dispersion (velocity dispersion).

The respective outputs of the B mode processing unit 3 and the CFM calculation unit 4 are supplied to the image processing unit 5, and an image colored according to a moving object (blood flow velocity, velocity dispersion) is displayed on the B mode display. Generate and CR display this image
Perform on the T display unit 7.

For example, the display is performed by changing the color (hue) in the moving direction (red / blue) and changing the brightness of red / blue according to the moving speed. In addition, the display is made so that green is mixed according to the velocity dispersion. Usually, red represents a flowing flow, blue represents a flowing flow, and the magnitude of dispersion is represented by the difference in the brightness of green. Therefore, depending on the site, blue and green are mixed, and red and green are mixed. In this case, since red, blue, and green are the three primary colors of light, the direction, velocity, and magnitude of dispersion can be read by changing the mixed colors.

FIG. 7 shows an example of the internal circuit configuration of the CFM calculator 4. In FIG. 7, the demodulated outputs of the transmitter / receiver 2 of FIG. 6 described above are signals whose phases are orthogonal (i signal, q signal)
, The i and q signals are respectively MTI filter 4
The signal of only the signal component from the moving object is extracted after being filtered by 00 and 401.

The signals from the moving object after passing through the MTI filters 400 and 401 are referred to as I and Q signals, respectively. Here, the I and Q signals are supplied to the delay units 402 and 403, respectively. The delay time of the delay units 402 and 403 is Δt. Further, this delay time Δt is an interval (or an integral multiple thereof) at which the signal of the same sound ray is received by the transmitter / receiver 2.
Interval. Then, the signals delayed by the delay units 402 and 403 and the signals not delayed are respectively multiplied by the multipliers 405 to 408, and further added and subtracted by the adder 409 and the subtractor 410.

Here, as the I signal, I1, I2, I
Consider 3 signals, I 4 and 4 signals for each Δt. Similarly, four Q signals Q1, Q2, Q3, and Q4 for each Δt are considered. When such a signal is given, the adder 40
The output of 9 is I1I2 + Q1Q2, I2I3 for each Δt.
+ Q2 Q3, I3 I4 + Q3 Q4 are obtained. This signal will be called DEN.

Similarly, the output of the subtractor 410 has Δt
I1 Q2 -Q1 I2, I2 Q3 -Q2 I3, I3
Q4 -Q3 I4 is obtained. This signal will be called NUM.

Further, the power calculation unit 404 adds squares.
Processing is performed and I1² ＋ Q1², I2²+
Q2², I3²+ Q3², I4²+ Q4²Is obtained.
This signal is called a power value and is abbreviated as P.

Then, the delay adder 411 performs delay addition (cumulative averaging) for each Δt to obtain ((I1 I2 + Q
1 Q2) + (I2 I3 + Q2 Q3) + (I3 I4 + Q3
Q4)) / 3 is obtained. Here it is * DEN *
Abbreviated as.

Similarly, in the delay adder 412, Δt
Delay addition (cumulative averaging) is performed for each ((I1 Q2
-Q1 I2) + (I2 Q3 -Q2 I3) + (I3 Q4-
Q3I4)) / 3 is obtained. Similarly, set this to * NUM *
Abbreviated.

Further, the delay adder 413 performs delay addition (cumulative averaging) for each Δt to obtain ((I1 ² + Q1
² ) + (I2 ² + Q2 ² ) + (I3 ² + Q3 ² ) +
(I4 ² + Q4 ² )) / 4 is obtained. This is abbreviated as * P *.

Such * DEN *, * NUM *, * P
When * is obtained, the average speed calculation unit 414 indicates ta
The process of n ^-1 ((* NUM *) / (* DEN *)) is executed to obtain the average speed * v *.

Further, in the variance calculation unit 415, (1-
((* DEN *²+ * NUM *²) ^1/2) / * P *)
Such processing is executed to obtain the variance * var *.
An image that has been subjected to the average velocity and variance thus obtained
The processing unit 5 uses red / blue, green, etc. according to each signal value.
The color is displayed by changing the brightness of.

FIG. 8 shows the relationship between the average velocity and dispersion and the blood flow as described above. FIG. 8A shows the blood flow velocity,
The horizontal axis represents time t, and the vertical axis represents blood flow velocity v.
Incidentally, the hatched portions mean variations. Here, the time corresponding to one heartbeat is shown, and here, the processing for obtaining the above-mentioned average velocity and variance is executed at each timing of the time phases I, II, III, IV, and V.

Therefore, the average velocity and the dispersion are obtained according to the respective time phases I to V, and the velocity spectra as shown in FIGS. 8B to 8F are obtained. In each of these figures, the position of the peak of the mountain shows the average velocity, the spread of the mountain shows the dispersion, and the vertical axis shows the spectrum showing the intensity.

Here, although the average speed and the dispersion of each time phase are shown in the graph, the color display is actually performed by the processing of the image processing unit 5. So in a real device,
According to FIGS. 8B to 8F, the color display of the average velocity and the variance is shown to be changed every moment.

[0025]

The ultrasonic diagnostic apparatus which displays the average velocity and the dispersion as described above displays the average velocity and the dispersion of the blood flow for each different time phase.

Therefore, it is not possible to display temporal pulsatility, and whether the blood flow is a pulsatile flow (a flow in which the blood flow velocity or dispersion changes periodically) or a steady flow (the blood flow velocity or dispersion is It was difficult to instantly identify whether the flow was almost constant).

In such a case, in order to display the pulsatility so that the pulsatility can be identified, it is possible to use FFT by pulse Doppler or the like.
It is necessary to perform a frequency analysis in order to verify, and there is a drawback that the device becomes complicated.

Further, the discrimination can be made by providing a circuit for tracing the output of the CFM calculating section 4 for a long time, but there is a problem that a large scale circuit needs to be added.

Due to the above problems, it was extremely difficult to display the pulsatility so as to be distinguishable with a simple structure. The present invention has been made in view of the above points, and a first object thereof is to realize an ultrasonic imaging display method capable of displaying a pulsatile flow or a steady flow with respect to a blood flow in a distinguishable state. That is.

A second object is to realize an ultrasonic imaging apparatus capable of displaying a pulsatile flow or a steady flow with respect to the blood flow in a distinguishable state.

[0031]

A first means for solving the above-mentioned problems is a predetermined number for every interval ΔT which is larger than the sampling interval Δt of the same sound ray data in the moving object reflection signal obtained from the received wave signal. The ultrasonic imaging display method is characterized by performing delayed addition of each moving object reflection signal, and calculating flow velocity data from the delayed addition moving object reflection signal to perform ultrasonic imaging display by color flow mapping.

Here, the moving object reflection signal is a signal of a reflected wave component from the moving object detected from the received signal,
Data for the same sound ray is obtained at Δt intervals. Further, it means a time interval having a time phase different from the interval ΔT larger than Δt. The flow velocity data is data indicating the velocity of blood flow and the like.

The second means for solving the above-mentioned problems is to analyze the received signal to obtain B-mode data, and a B-mode processing unit to analyze the received signal to obtain a moving object reflection signal, and to obtain the same sound line. An interval ΔT larger than the data sampling interval Δt
A CFM calculation unit for delay-adding a predetermined number of moving object reflection signals for each time to obtain flow velocity data, a B mode data obtained by the B mode processing unit, and a flow velocity obtained by delay addition by the CFM calculation unit. And an image processing unit for generating image data for ultrasonic imaging display by color flow mapping using the data and the image processing unit.

Here, the flow velocity data is data indicating the velocity and dispersion of the blood flow obtained from the received wave signal.
A third means for solving the above problems is a B-mode processing unit that analyzes a received signal to obtain B-mode data, and a received object signal is analyzed to obtain a moving object reflection signal, and the same sound ray data is sampled. A CFM calculating unit for delay-adding a predetermined number of moving object reflection signals at intervals ΔT larger than the interval Δt to obtain velocity data and dispersion data, B-mode data obtained by the B-mode processing unit, and the CFM calculating unit And an image processing unit for generating image data for ultrasonic imaging display by color flow mapping using the velocity data and the dispersion data obtained by delaying and adding in the ultrasonic imaging apparatus.

Here, the velocity data indicates the velocity of blood flow and the like, and the dispersion data indicates the variation of velocity such as blood flow.

[0036]

In the ultrasonic imaging display method which is the first means for solving the problem, the flow velocity data is obtained from the moving object reflection signal obtained at the Δt intervals.
The flow velocity data is obtained by delaying and adding the moving object reflection signals for each ΔT of different time phases at intervals larger than t. Then, the CFM ultrasonic imaging display is performed based on the flow velocity data thus obtained.
By doing so, it becomes possible to display the pulsating flow and the steady flow in a distinguishable state.

In the ultrasonic imaging apparatus which is the second means for solving the problem, the flow velocity data is obtained from the moving object reflection signal obtained at Δt intervals.
The flow velocity data is obtained by delaying and adding the moving object reflection signals for each ΔT of different time phases at intervals larger than t. Then, the CFM ultrasonic imaging display is performed based on the flow velocity data thus obtained.
By doing so, it becomes possible to display the pulsating flow and the steady flow in a distinguishable state.

In the ultrasonic imaging apparatus which is the third means for solving the problem, the velocity data and the dispersion data are obtained from the moving object reflection signal obtained at the Δt intervals. At this time, the intervals are larger than Δt. Then, the velocity data and the dispersion data are obtained by the delayed addition of the moving object reflection signals for each ΔT of different time phases. Then, the CFM ultrasonic imaging display is performed based on the velocity data and the dispersion data thus obtained. By doing so, it becomes possible to display the pulsating flow and the steady flow in a distinguishable state.

[0039]

Embodiments of the present invention will be described below in detail with reference to the drawings. 1 is an apparatus for realizing an embodiment of the ultrasonic imaging display method of the present invention, and is a configuration diagram showing a schematic configuration of an embodiment of the ultrasonic imaging apparatus of the present invention. First, the outline of the ultrasonic imaging apparatus will be described with reference to FIG.

FIG. 1 is a block diagram showing an example of the internal circuit configuration of the CFM calculator 4 described above. In FIG. 1, when the demodulated output of the transmission / reception unit 2 of FIG. 6 described above is a signal (I signal, Q signal) whose phases are orthogonal to each other, the I and Q signals are filtered by the MTI filters 400 and 401, respectively. A signal (moving object reflection signal) containing only the signal component from the moving object is extracted.

The moving object reflection signals after passing through the MTI filters 400 and 401 are respectively I and Q signals. Here, the I and Q signals are supplied to the delay units 402 and 403, respectively. The delay time of the delay units 402 and 403 is Δt. Further, this delay time Δt is an interval (or an integral multiple thereof) at which the signal of the same sound ray is received by the transmitter / receiver 2.
Interval. Then, the signals delayed by the delay units 402 and 403 and the signals not delayed are respectively multiplied by the multipliers 405 to 408, and further added and subtracted by the adder 409 and the subtractor 410.

Here, as the I signal, I1, I2, I
Consider 3 signals, I 4 and 4 signals for each Δt. Similarly, four Q signals Q1, Q2, Q3, and Q4 for each Δt are considered. When such a signal is given, the adder 40
The output of 9 is I1I2 + Q1Q2, I2I3 for each Δt.
+ Q2 Q3, I3 I4 + Q3 Q4 are obtained. This signal will be called DEN.

Similarly, the output of the subtractor 410 has Δt
I1 Q2 -Q1 I2, I2 Q3 -Q2 I3, I3
Q4 -Q3 I4 is obtained. This signal will be called NUM.

Further, the power calculation unit 404 adds squares.
Processing is performed and I1 ²＋ Q1², I2²
+ Q2², I3²+ Q3², I4²+ Q4²Is obtained
It This signal is called a power value and is abbreviated as P.
It

Then, the delay adder 411 performs delay addition (cumulative averaging) for each Δt to obtain ((I1 I2 + Q
1 Q2) + (I2 I3 + Q2 Q3) + (I3 I4 + Q3
Q4)) / 3 is obtained. Similarly, this is abbreviated as * DEN *. Then, corresponding to the time phases I to V described in FIG. 8, the * DEN * of each time phase is changed to * DEN * I, * DEN.
* II, * DEN * III, * DEN * IV, * DEN
* Indicated as V.

Similarly, in the delay adder 412, Δt
Delay addition (cumulative averaging) is performed for each ((I1 Q2
-Q1 I2) + (I2 Q3 -Q2 I3) + (I3 Q4-
Q3 I4)) / 3 is obtained. This is here, * NU
Abbreviated as M *.

Then, the time phases I to V explained in FIG.
Corresponding to, * NUM * of each time phase, * NUM * I, *
NUM * II, * NUM * III, * NUM * IV, *
It is shown as NUM * V.

The delay adder 413 performs delay addition (cumulative averaging) for each Δt to obtain ((I1 ² + Q1
² ) + (I2 ² + Q2 ² ) + (I3 ² + Q3 ² ) +
(I4 ² + Q4 ² )) / 4 is obtained. This is abbreviated as * P *. Then, corresponding to the time phases I to V described in FIG. 8, the * P * of each time phase is changed to * P * I, * P * II, *.
It is shown as P * III, * P * IV, * P * V.

Here, in the delay adder 416, an interval ΔT larger than Δt (intervals having different time phases: here, when ΔT is adjusted to the intervals of the time phases I, II, III, IV, V). (Indicating) is performed for each delay addition (cumulative average). As a result, ((* DEN * I) + (* DEN * I
I) + (* DEN * III) + (* DEN * IV) +
An operation such as (* DEN * V) / 5) is performed. The result of this calculation is called * DEN * T. This * DEN * T
Is an average value of data DEN of different time phases I to V.

Similarly, in the delay adder 417, Δt
Delay addition (cumulative averaging) is performed for each larger interval ΔT (intervals having different time phases). As a result,((*
NUM * I) + (* NUM * II) + (* NUM * II
I) + (* NUM * IV) + (* NUM * V) / 5) is performed. This calculation result is * NUM * T
Call. This * NUM * T is an average value of the data NUM of different time phases I to V.

Similarly, in the delay adder 418, Δt
Delay addition (cumulative averaging) is performed for each larger interval ΔT (intervals having different time phases). As a result,((*
P * I) + (* P * II) + (* P * III) + (* P
Calculation such as * IV) + (* P * V) / 5) is performed. The result of this calculation is called * P * T. This * P * T
Is an average value of data P of different time phases I to V.

Such * DEN * T, * NUM * T,
When * P * T is obtained, the average speed calculation unit 414 calculates tan ⁻¹ ((* NUM * T) / (* DEN * T)).
Is executed to obtain the average speed * v * T.

Further, in the variance calculation unit 415, (1-
((* DEN * T²+ * NUM * T ²)^1/2) / * P *
T) is executed to obtain the variance * var * T
Can be

The image processing unit 5, which receives the average speed and the variance thus obtained, changes the brightness to the hue of red / blue according to the respective signal values, and changes the brightness of the red / blue to green or the like. The color display is performed by superimposing the display in which the luminance of is changed.

Therefore, in this embodiment, different time phases (I
.About.V), the average value of the average velocity and variance of the blood flow is displayed. For this reason, it becomes possible to display temporal pulsatility, and whether the blood flow is a pulsatile flow (a blood flow velocity or dispersion changes periodically) or a steady flow (blood flow velocity or dispersion is It is possible to instantly identify whether or not the flow is almost constant).

In the above embodiment, the time phase I shown in FIG.
Although the data of 5 time phases at ΔT intervals of ˜V are delayed and added, other numbers of data may be delayed and added.

FIG. 2 shows changes in pulsatile blood flow velocity with time. The horizontal axis represents time t and the vertical axis represents blood flow velocity v. Incidentally, the hatched portions mean variations. Here, the time corresponding to one heartbeat is shown, and for example, the above-described processing for obtaining the average velocity and the variance is executed at the timings corresponding to the above-mentioned time phases I, II, III, IV, and V.

FIG. 3 shows the change over time of the steady blood flow velocity. The horizontal axis shows the time t and the vertical axis shows the blood flow velocity v. Incidentally, the hatched portions mean variations. Here, the same time as in FIG. 2 is shown, and for example, the processing for obtaining the above-mentioned average velocity and dispersion is executed at the timings corresponding to the above-mentioned time phases I, II, III, IV, V.

With respect to the blood flow velocity as shown in FIGS. 2 and 3, the average velocity and the variance when the above calculation is executed are as shown in FIGS. 4 and 5, respectively. That is, in the pulsatile flow, the average velocity is distributed in a wide range. on the other hand,
In steady flow, the average velocity is concentrated at a nearly constant value.

According to the above embodiment, since the display is colored according to the characteristics shown in FIGS. 4 and 5, it is possible to instantly discriminate between the pulsatile flow and the steady flow. it can. In addition, in the configuration of FIG. 1, the delay addition for each ΔT is performed for both the average speed data and the distributed data, but a configuration for performing the delay addition for only one of them is also possible. Also in this case, it is possible to distinguish between the steady flow and the pulsating flow by displaying the CFM based on one of the flow velocity data subjected to the delay addition, and there is also an advantage that the circuit configuration can be simplified. There is.

As described in detail above, in the ultrasonic imaging display method, when the flow velocity data is obtained from the moving object reflection signal obtained at the Δt interval, the ΔT is different for each ΔT of the different time phase with the interval larger than Δt. Velocity data can be obtained by delaying and adding moving object reflection signals, and pulsatile flow or steady flow can be identified by performing CFM ultrasonic imaging display based on the thus obtained flow velocity data. It is possible to display in a simple state.

In the ultrasonic imaging apparatus,
When the flow velocity data is obtained from the moving object reflection signal obtained at the Δt interval, the flow velocity data is obtained by the delay addition of the moving object reflection signal for each ΔT of an interval larger than Δt and different time phases. By performing the ultrasonic imaging display of the CFM based on the flow velocity data obtained as described above, it becomes possible to display the pulsatile flow and the steady flow in a distinguishable state.

Then, in the ultrasonic imaging apparatus, when the velocity data and the dispersion data are obtained from the moving object reflection signal obtained at the Δt intervals, the moving object reflection signal for each ΔT having a different time phase with an interval larger than Δt. The speed data and the distributed data are obtained by the delayed addition of
By performing ultrasonic imaging display of the CFM based on the velocity data and the dispersion data obtained in this way, it becomes possible to display the pulsatile flow and the steady flow in a distinguishable state.

[0064]

As described in detail above, in the ultrasonic imaging display method, when the flow velocity data is obtained from the moving object reflection signal obtained at the Δt interval, the ΔT of the different time phase is obtained at the interval larger than Δt. Velocity data is obtained by delay-adding the moving object reflection signals for each of the signals, and CFM ultrasonic imaging display is performed based on the thus obtained flow velocity data. It becomes possible to display in an identifiable state.

In the ultrasonic imaging apparatus,
When the flow velocity data is obtained from the moving object reflection signal obtained at the Δt interval, the flow velocity data is obtained by the delay addition of the moving object reflection signal for each ΔT of an interval larger than Δt and different time phases. By performing the ultrasonic imaging display of the CFM based on the flow velocity data obtained as described above, it becomes possible to display the pulsatile flow and the steady flow in a distinguishable state.

Then, in the ultrasonic imaging apparatus, when the velocity data and the dispersion data are obtained from the moving object reflection signals obtained at the Δt intervals, the moving object reflection signals for each ΔT of different time phases with an interval larger than Δt. The speed data and the distributed data are obtained by the delayed addition of
By performing ultrasonic imaging display of the CFM based on the velocity data and the dispersion data obtained in this way, it becomes possible to display the pulsatile flow and the steady flow in a distinguishable state.

[Brief description of drawings]

FIG. 1 is a block diagram of an ultrasonic imaging apparatus according to an embodiment of the present invention.

FIG. 2 is a characteristic diagram showing a velocity spectrum of pulsatile flow.

FIG. 3 is a characteristic diagram showing a velocity spectrum of a steady flow.

FIG. 4 is a characteristic diagram showing average velocity and dispersion of pulsatile flow.

FIG. 5 is a characteristic diagram showing the average velocity and dispersion of a steady flow.

FIG. 6 is a configuration diagram showing an overall configuration of an ultrasonic imaging apparatus.

FIG. 7 is a configuration diagram showing a circuit configuration of a conventional CFM calculation unit.

FIG. 8 is a characteristic diagram showing a velocity spectrum of a pulsatile flow, an average velocity, and a state of dispersion.

[Explanation of symbols]

 400, 401 MTI filter 402 to 404 delay unit 405 to 408 multiplier 409 adder 410 subtractor 411 to 413 delay adder 414 average speed calculation unit 415 dispersion calculation unit 416 to 418 delay addition unit

Claims (3)

[Claims] 1. A delay addition of a predetermined number of moving object reflection signals is performed at every interval ΔT that is larger than the sampling interval Δt of the same sound ray data in the moving object reflection signal obtained from the received signal, and the delay addition is performed. An ultrasonic imaging display method, characterized in that flow velocity data is obtained from a moving object reflection signal and ultrasonic imaging display is performed by color flow mapping. 2. A B-mode processing unit for analyzing received signals to obtain B-mode data, and a received object signal for analyzing moving object reflection signals for each interval ΔT larger than a sampling interval Δt of the same sound ray data. To the C-mode calculation unit for delay-adding a predetermined number of moving object reflection signals to obtain flow velocity data, the B-mode data obtained by the B-mode processing unit, and the C-mode.
An ultrasonic imaging apparatus comprising: an image processing unit that generates image data for ultrasonic imaging display by color flow mapping using flow velocity data obtained by delay addition in the FM calculation unit. 3. A B-mode processing unit for analyzing a received signal to obtain B-mode data, and a received object signal for analyzing a moving object reflection signal for each interval ΔT larger than a sampling interval Δt of the same sound ray data. A delay time addition of a predetermined number of moving object reflection signals to obtain velocity data and dispersion data; B mode data obtained by the B mode processing unit;
An ultrasonic imaging apparatus, comprising: an image processing unit for generating image data for ultrasonic imaging display by color flow mapping using velocity data and dispersion data obtained by delay addition in the FM calculation unit. .