JPH08154935A - Ultrasonic imaging display method and ultrasonic imaging apparatus - Google Patents

Abstract

PURPOSE: To realize an ultrasonic imaging display method and an ultrasonic imaging apparatus which have a power Doppler mode allowing stable display of the direction of blood stream as well. CONSTITUTION: This ultrasonic imaging apparatus has a CFM computing section 4 and an image processing section 5. At the computing section 4, a received signal is analyzed to determine a reflection signal of a moving object, the same sound ray data undergoes a velocity measurement containing at least the direction of moving based on a data obtained at a sampling interval ΔTv and a measurement of a power value is performed based on data obtained at a sampling interval ΔTp slower in speed than at the ΔTv to determine sound velocity data. The image processing section 5 uses the direction of moving and the power value obtained by the CFM computing section to generate image data for ultrasonic imaging display by a color flow mapping.

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 method and an ultrasonic imaging apparatus having a power Doppler mode capable of displaying a blood flow direction.

[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 an 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 echo from the blood cells. And a power value are calculated, and various amounts thereof are two-dimensionally displayed in real time on a B mode (tomographic image) screen by color. This mode is called a CFM mode, and a device having these functions is a CFM ultrasonic diagnostic device.

When such a CFM mode is displayed, there are two modes, a speed mode using speed data (v) obtained from the shift of the frequency of the Doppler signal due to the Doppler effect and a power Doppler mode based on the power value of the Doppler signal. Types of modes are known.

The velocity mode has a problem that the velocity value and the moving direction can be known and the real-time property is excellent, but it has a problem that aliasing occurs due to aliasing and that it is easily affected by noise.

On the other hand, in the power Doppler mode, the velocity value and the moving direction are unknown, and the real-time property is poor, but
No aliasing aliasing occurs, and S /
It has an advantage that the blood flow of a thin blood vessel having a high N and a low flow velocity can be visualized. CFM in such a power Doppler mode
When the display is performed, it is possible to clearly color-code a portion with blood flow and a portion without blood flow. Further, there is an advantage that a clear display is possible because noise does not particularly enter a portion where there is no blood flow. In addition, PRF (Pulse Repe
It also has the advantage that the sensitivity of low-speed flow can be increased by lowering the tition frequency (pulse repetition frequency).

FIG. 2 is a block diagram for explaining the schematic structure of a general ultrasonic diagnostic apparatus having a CFM mode. In the configuration of FIG. 2, 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. It is an electroacoustic conversion element for converting into. The transmission / reception unit 2 is a circuit for amplifying the transmission signal and transmitting it to the ultrasonic probe 1, and for demodulating the received signal received by quadrature detection or the like and then transmitting it to each processing unit. That is, the reception 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 and the like to output a signal for B-mode display of a tomographic image, 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 a reflected wave of only the moving target by an MTI filter or the like, and extracts a reflected wave from the blood flow, for example, and calculates the blood flow velocity, dispersion (velocity dispersion), and power value. .

The respective outputs of the B-mode processing unit 3 and the CFM calculation unit 4 are supplied to the image processing unit 5. The image processing unit 5 generates the following colored image on the B-mode display according to the moving object (blood flow velocity, velocity dispersion), and matches the scanning frequency of the CRT display unit 7 from this image. Such a video signal is generated.

For example, the display is performed by changing the color (hue) in the moving direction (red / blue) and changing the luminance of red / blue according to the moving speed. It is also possible to perform a display in which green is mixed according to the velocity dispersion. Normal,
Red represents the approaching flow, blue represents the distant flow, and the magnitude of the 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.

It is also possible to perform color display in the power Doppler mode according to the power value. For example, yellow colored display having different brightness depending on the power value is displayed, and another color (purple or the like) is displayed in the portion where the power value = 0 (a region where blood flow does not exist).

For details of such color display,
Further description will be given with reference to FIG. FIG. 3 is a configuration diagram showing an example of the internal circuit configuration of the CFM calculation unit 4. In FIG. 3, when the demodulated output of the transmitter / receiver 2 of FIG. 2 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 401 and 402, respectively. A signal of only the signal component from the moving object is extracted.

Signals from the moving object after passing through the MTI filters 401 and 402 are I and Q signals, respectively. Here, each of the I and Q signals is supplied to the autocorrelator 403. In the following description, I1, which has a time difference for each Δt,
It is assumed that a plurality of signals I2, Q1, Q2, ... Are considered. Further, the delay time Δt is set to an interval (or an integral multiple thereof) at which the transmitting / receiving unit 2 receives signals of the same sound ray and the same depth.

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, one output of the autocorrelator 403 outputs I1 I2 + Q1 Q for each Δt.
2, I2 I3 + Q2 Q3, I3 I4 + Q3 Q4 are obtained. This signal will be called DEN.

Similarly, at the other terminal of the autocorrelator 403, I1 Q2 -Q1 I2, I2 Q3 is provided for each Δt.
-Q2 I3, I3 Q4 -Q3 I4 are obtained. This signal will be called NUM.

Then, the delay adder 405 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 406, Δt
Delay addition (cumulative averaging) is performed for each ((I1 Q2
-Q1 I2) + (I2 Q3 -Q2 I3) + (I3 Q4-
Q3 I4)) / 3 is obtained. Similarly, set this to * NUM *
Abbreviated.

Further, the power calculation unit 404 performs a square addition process, and for each Δt, I1 ² + Q1 ² and I2 ²
+ Q2 ² , I3 ² + Q3 ² , I4 ² + Q4 ² are obtained. This signal is abbreviated as P.

The delay adder 407 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 power value * P *.

Such * DEN *, * NUM *, * P
When * is obtained, tan ^{−1 is} calculated in the speed calculation unit 408.
The process of ((* NUM *) / (* DEN *)) is executed to obtain the average speed * v * and the moving direction (sign (v)).

The average velocity * v obtained as described above
One of * and the power value * P * is output to the outside according to the switching state of the selector 409 that is switch-controlled by the control unit 7.

[0027]

In the case of such a configuration, the detection of the average speed and the calculation of the power value are performed at the same data rate (PRF).

With this structure, the PRF is increased in order to improve the real-time property of speed detection. However, this causes a problem that the sensitivity of low-speed blood flow is insufficient.

Further, when the power Doppler mode is used, in order to know the moving direction (sign (v)), the speed detecting unit 408 receives the data of the moving direction. In such a case, it is preferable to set the PRF small so as to improve the sensitivity of low-speed blood flow. However, when the PRF is reduced, there is a problem in that the direction display (sign (v)) obtained by detecting the average speed is folded back, and the sign is inverted due to this.

The aliasing is a phenomenon known to occur in the color flow mapping function of the pulse Doppler system, which occurs when the detectable flow velocity limit is exceeded, and it is mixed on the color display and mixed on the display image. However, it is a trouble that it becomes impossible to judge visually whether it is due to turbulent flow or due to a turning back phenomenon.

For the above reasons, it was extremely difficult to make both high-speed blood flow and low-speed blood flow detection compatible.
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 having a power Doppler mode capable of stably displaying the blood flow direction.

A second object is to realize an ultrasonic imaging apparatus having a power Doppler mode capable of stably displaying the blood flow direction.

[0033]

The inventor of the present application has conducted earnest research to improve the drawbacks of the conventional power Doppler mode display, and as a result, the optimum PRF differs between the speed mode and the power Doppler mode. The present invention has been completed by discovering that it is a thing.

Therefore, the present invention, which is means for solving the problems, is configured as described below. The first means for solving the above-mentioned problem is to perform velocity measurement including at least the moving direction by the data obtained at the sampling interval ΔTv for the same sound ray data in the moving object reflection signal obtained from the received wave signal, An ultrasonic imaging display method is characterized in that a power value is measured by data obtained at a sampling interval ΔTp slower than ΔTv, and ultrasonic imaging display is performed by color flow mapping based on the measured moving direction and power value.

Here, the moving object reflection signal is a signal of the reflected wave component of 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 sampling interval ΔT which is later than Δt.

A second means for solving the above problem is to analyze a received signal to obtain a moving object reflection signal, and for the same sound ray data, a velocity including at least a moving direction based on data obtained at a sampling interval ΔTv. Measure and measure Δ
A CFM calculation unit that obtains flow velocity data by measuring a power value with data obtained at a sampling interval ΔTp slower than Tv, and an ultrasonic imaging display by color flow mapping using the moving direction and the power value obtained by the CFM calculation unit. And an image processing unit for generating image data for use in the ultrasonic imaging apparatus.

A third means for solving the above problem is to analyze a received signal to obtain a moving object reflection signal, and for the same sound ray data, a velocity including at least a moving direction based on data obtained at a sampling interval ΔTv. Measure and measure Δ
A CFM calculation unit that obtains flow velocity data by measuring a power value with data obtained at a sampling interval ΔTp slower than Tv, and a hue is changed according to the moving direction obtained by the CFM calculation unit, and the brightness is changed according to the power value. An ultrasonic imaging apparatus comprising: an image processing unit that generates image data for ultrasonic imaging display by changing color flow mapping.

A fourth means for solving the above problem is to analyze a received signal to obtain a moving object reflection signal, and for the same sound ray data, a velocity including at least a moving direction based on data obtained at a sampling interval ΔTv. Measure and measure Δ
A CFM calculation unit that obtains flow velocity data by measuring a power value based on data obtained at a sampling interval ΔTp slower than Tv, and determines the first and second hues according to the moving direction obtained by the CFM calculation unit. Image for ultrasonic imaging display by color flow mapping in which the brightness is changed according to the power value, and when the moving direction cannot be detected by the CFM calculator, the brightness is changed on the third hue with respect to the power value. An ultrasonic imaging apparatus, comprising: an image processing unit that generates data.

[0039]

In the ultrasonic imaging display method as the first means for solving the problem, the moving direction is obtained from the moving object reflection signal obtained at the ΔTv interval, and the power is obtained by the data obtained at the sampling interval ΔTp slower than the interval ΔTv. Value measurement is performed. Then, ultrasonic imaging display by color flow mapping is performed based on the measured moving direction and power value. By doing so, the optimum PRF is obtained in the velocity mode for measuring the moving direction and the power Doppler mode for measuring the power value, and the blood flow direction can be stably displayed in the power Doppler mode.

In the ultrasonic imaging apparatus which is the second means for solving the problem, the moving direction is obtained from the moving object reflection signal obtained at the ΔTv interval, and the power value is obtained by the data obtained at the sampling interval ΔTp slower than the interval ΔTv. Measurement is performed. Then, ultrasonic imaging display by color flow mapping is performed based on the measured moving direction and power value. By doing so, the optimum PRF is obtained in the velocity mode for measuring the moving direction and the power Doppler mode for measuring the power value, and the blood flow direction can be stably displayed in the power Doppler mode.

In the ultrasonic imaging apparatus as the third means for solving the problem, the moving direction is obtained from the moving object reflection signal obtained at the ΔTv interval, and the power value is obtained by the data obtained at the sampling interval ΔTp slower than the interval ΔTv. Measurement is performed. Then, the hue is changed according to the measured moving direction, and the ultrasonic imaging display is performed by the color flow mapping in which the brightness is changed according to the power value. By doing so, the optimum PRF is obtained in the velocity mode for measuring the moving direction and the power Doppler mode for measuring the power value, and the blood flow direction can be stably displayed in the power Doppler mode.

In the ultrasonic imaging apparatus as the fourth means for solving the problem, the moving direction is obtained from the moving object reflection signal obtained at the ΔTv interval, and the power value is obtained by the data obtained at the sampling interval ΔTp slower than the interval ΔTv. Measurement is performed. Then, the first and second hues are determined according to the measured moving direction, and ultrasonic imaging display is performed by color flow mapping in which the brightness is changed by the power value. By doing so, the optimum PRF is obtained in the velocity mode for measuring the moving direction and the power Doppler mode for measuring the power value, and the blood flow direction can be stably displayed in the power Doppler mode.
If the moving direction cannot be detected, ultrasonic imaging display is performed by color flow mapping in which the brightness is changed on the third hue with respect to the power value.

[0043]

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 in FIG. 2 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 401 and 402, 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 401 and 402 are I and Q signals, respectively. Here, each of the I and Q signals is supplied to the autocorrelator 403. Here, as the I signal, I1, I2, I3, I4
And four signals for each ΔTv. Similarly, as the Q signal, four signals for each ΔTv of Q1, Q2, Q3 and Q4 are considered. Further, the delay time Δt is set to an interval (or an integral multiple thereof) at which the transmitting / receiving unit 2 receives signals of the same sound ray and the same depth.

When such a signal is given, one output of the autocorrelator 403 is I1 I2 + for each ΔTv.
Q1 Q2, I2 I3 + Q2 Q3, I3 I4 + Q3 Q4 are obtained. This signal will be called DEN.

Similarly, at the other terminal of the autocorrelator 403, I1 Q2-Q1 I2 and I2 Q3 are provided for each ΔTv.
-Q2 I3, I3 Q4 -Q3 I4 are obtained. This signal will be called NUM.

Then, the delay adder 405 performs delay addition (cumulative averaging) for each ΔTv to obtain ((I1 I2 +
Q1 Q2) + (I2 I3 + Q2 Q3) + (I3 I4 + Q
3 Q4)) / 3 is obtained. This is here * DEN
Abbreviated as *.

Similarly, in the delay adder 406, ΔT
Delay addition (cumulative averaging) is performed for each v, and ((I1 Q
2-Q1 I2) + (I2 Q3 -Q2 I3) + (I3 Q4
-Q3 I4)) / 3 is obtained. Similarly, * NUM
Abbreviated as *.

When such * DEN * and * NUM * are obtained, the speed calculation unit 408 calculates tan ^-1 ((* N
UM *) / (* DEN *)) is executed,
The average speed * v * is calculated, and the moving direction (sign
(V)) is required.

Further, the demodulation outputs i, q signals (i1, i2, i3, i4, i5, i6, i) of the transmitter / receiver 2 shown in FIG.
7, i8, i9, ..., q1, q2, q3, q4, q5,
Each of q6, q7, q8, q9, ... Is thinned out by the 1 / N decimator 411 which constitutes data thinning means. The decimation of the 1 / N decimator 411 is performed by the control unit 7.
Is controlled by a coefficient N designated by. For example, when N = 3, i3, i6, i9, ..., q3,
Thinning out is performed like q6, q9, .... Thus, for the sampling interval ΔTp of the i and q signals that have passed through the 1 / N decimator 411, ΔTp = NΔTv
You can see that the relationship is established.

The i and q signals decimated in this way are filtered by the MTI filters 412 and 413 to extract signals (moving object reflection signals) containing only signal components from the moving object.

After passing through the MTI filters 412 and 413
Let the moving object reflection signals be I and Q signals, respectively. this
The I and Q signals are supplied to the power calculation unit 404.
It The power calculation unit 404 performs a square addition process.
Then, for every ΔTp (= NΔTv) described above, I3²+ Q3
 ², I6²+ Q6², I9²＋ Q9², I12²+ Q12
²,… Is obtained. This signal is abbreviated as P.

Then, in the delay adder 407, every ΔTp
Delay addition (cumulative averaging) of ((I3²+ Q
3²) + (I6²+ Q6²) + (I9²＋ Q9²) +
(I12 ²+ Q12²)) / 4 is obtained. This is the power value
Abbreviated as * P *.

Based on the power value * P * and the moving direction (sign (v)) obtained in this way, the color conversion unit 501 in the image processing unit 5 determines whether red / blue, Image data for color display is generated by changing the brightness to a hue such as yellow.

Then, the DSC 502 changes the color conversion unit 50.
CRT by scanning conversion of image data from 1
Generates a video signal in a signal format suitable for the display unit 6 to perform CRT
It is supplied to the display unit 6.

As described above, the power calculation in the power calculation unit 404 is performed at the sampling interval ΔTp slower than ΔTv, so that the speed calculation and the power calculation can be performed with different optimum PRFs. It became possible to obtain the moving direction and the power value in the optimum state. As a result, it becomes possible to have a power Doppler mode capable of stably displaying the blood flow direction.

Various methods can be considered for the image data generated by the color conversion unit 501 described above. Color display is performed by assigning either hue or brightness to each of the moving direction and the power value.

By doing so, the relationship between the moving direction and the power value can be clearly displayed. Different hues (first and second hues: red and blue, for example) are assigned according to the moving direction, and a power value is assigned to luminance to perform color display.

By doing so, the display of the luminance in each hue is performed, so that a clear display can be performed. In addition to the above, when the moving direction cannot be specified for some reason, a different hue (third hue: yellow, for example) is assigned, and the brightness is set to each hue according to the power value. Change the color display.

By doing so, even when the moving direction cannot be specified, a clear display without noise can be performed. In addition to the above, it is possible to change not only the brightness of the power value but also the color within the hue of the same system.

For example, the first hue (hue group): a plurality of colors included in the red system (for example, red, red, vermilion, ...), the second hue (hue group): a plurality of colors included in the blue system Color (eg,
Blue, indigo, navy blue, ...), Third hue (hue group): Set as multiple colors (yellow, lemon yellow, ...) included in the yellow system, not the brightness (or in combination with the brightness), the power Depending on the value (or range of power value), the display is performed by changing the color within the hue of the same system.

By doing so, a clearer display can be performed. Further, the coefficient N of the 1 / N decimator 411 can be variously changed and can be rewritten by an instruction from the control unit 7. Therefore, even if the optimum value varies depending on the usage situation, it is possible to select the optimum value for the usage situation.

It is also possible to write a predetermined value as an initial value and use it without changing it. By doing so, there is an advantage that the circuit configuration is simplified. Further, by writing a plurality of values as N in advance and selecting them, it becomes possible to deal with each usage situation with a simple configuration.

By using a digital circuit,
It is also possible to choose N as a value other than an integer. As a result, the optimum value can be obtained more strictly and used.
It should be noted that the 1 / N decimator 411 is provided not only on the power calculation side but also on the speed calculation side, and the sampling interval Δ is set on both sides.
It is also possible to change Tv and ΔTp. In this case, the sampling interval ΔTv on the speed calculation side can be oversampled, and in this case, the optimum interval on the speed calculation side can be freely selected.

As described in detail above, in the ultrasonic imaging display method or ultrasonic imaging apparatus, the moving direction is obtained from the moving object reflection signal obtained at the ΔTv interval, and the sampling interval ΔTp slower than the interval ΔTv is obtained.
By measuring the power value with the data obtained in, and performing ultrasonic imaging display by color flow mapping with the measured moving direction and power value, there are a speed mode for measuring the moving direction and a power Doppler mode for measuring the power value. Thus, the optimum PRF is obtained, and the blood flow direction can be stably displayed in the power Doppler mode.

Further, in the ultrasonic imaging display method or the ultrasonic imaging apparatus, the moving direction is obtained from the moving object reflection signal obtained at the ΔTv interval, and the power value is measured by the data obtained at the sampling interval ΔTp slower than the interval ΔTv. By changing the hue according to the measured moving direction and changing the brightness according to the power value to perform ultrasonic imaging display by color flow mapping, the speed mode for measuring the moving direction and the power Doppler mode for measuring the power value With, the optimum PRF is obtained, and in the power Doppler mode, the blood flow direction can be stably displayed in a clear state.

Then, in the ultrasonic imaging display method or ultrasonic imaging apparatus, the moving direction is obtained from the moving object reflection signal obtained at the ΔTv interval, and the interval ΔTv is obtained.
Power value measurement is performed using data obtained at a slower sampling interval ΔTp, the first and second hues are determined according to the measured moving direction, and ultrasonic imaging display by color flow mapping in which the brightness is changed according to the power value By performing, the optimum PRF is obtained in the velocity mode for measuring the moving direction and the power Doppler mode for measuring the power value, and the blood flow direction can be stably displayed in a clear state in the power Doppler mode. Further, when the moving direction cannot be detected, ultrasonic wave imaging display is performed by color flow mapping in which the brightness is changed on the third hue with respect to the power value, so that even if the moving direction cannot be specified, it is clear and clear. A clear display without noise can be performed.

[0069]

As described in detail above, in the ultrasonic imaging display method or ultrasonic imaging apparatus, the moving direction is obtained from the moving object reflection signal obtained at the ΔTv interval, and the sampling interval ΔTp slower than the interval ΔTv is obtained.
By measuring the power value with the data obtained in, and performing ultrasonic imaging display by color flow mapping with the measured moving direction and power value, there are a speed mode for measuring the moving direction and a power Doppler mode for measuring the power value. Thus, the optimum PRF is obtained, and the blood flow direction can be stably displayed in the power Doppler mode.

Further, by changing the hue according to the measured moving direction and changing the brightness according to the power value to perform ultrasonic imaging display by color flow mapping, the blood flow direction can be made clearer in the power Doppler mode. It becomes possible to display stably in the state.

Then, according to the measured moving direction, the first
Then, the second hue is determined, ultrasonic imaging display is performed by color flow mapping in which the brightness is changed according to the power value, and when the moving direction cannot be detected, the brightness is changed on the third hue with respect to the power value. By performing ultrasonic imaging display by color flow mapping, clear display without noise can be performed even when the moving direction cannot be specified.

[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 configuration diagram showing an overall configuration of an ultrasonic imaging apparatus.

FIG. 3 is a configuration diagram showing a circuit configuration of a conventional CFM calculation unit.

[Explanation of symbols]

 401, 402 MTI filter 403 autocorrelator 404 power calculator 405, 406, 407 delay adder 408 speed calculator 501 color converter 502 DSC

Claims (4)

[Claims] 1. A sampling interval ΔTv for the same sound ray data in a moving object reflection signal obtained from a received signal.
A velocity measurement including at least the moving direction is performed based on the data obtained in step S1, and a sampling interval ΔTp slower than ΔTv
An ultrasonic imaging display method, characterized in that a power value is measured based on the data obtained in step 1, and ultrasonic imaging display is performed by color flow mapping based on the measured moving direction and power value. 2. The received signal is analyzed to obtain a moving object reflection signal, and the sampling interval ΔT is applied to the same sound ray data.
The velocity measurement including at least the moving direction is performed based on the data obtained in v, and the sampling interval ΔT slower than ΔTv is obtained.
A CFM calculation unit that obtains flow velocity data by measuring a power value based on the data obtained in p, and image data for ultrasonic imaging display by color flow mapping using the moving direction and the power value obtained by the CFM calculation unit. An ultrasonic imaging apparatus, comprising: an image processing unit for generating. 3. The received signal is analyzed to obtain a moving object reflection signal, and the sampling interval ΔT is applied to the same sound ray data.
The velocity measurement including at least the moving direction is performed based on the data obtained in v, and the sampling interval ΔT slower than ΔTv is obtained.
A CFM calculation unit that obtains flow velocity data by measuring a power value based on the data obtained in p, and a color flow mapping that changes the hue according to the moving direction obtained by the CFM calculation unit and changes the brightness according to the power value. And an image processing unit for generating image data for ultrasonic imaging display by the ultrasonic imaging apparatus. 4. The received signal is analyzed to obtain a moving object reflection signal, and the sampling interval ΔT for the same sound ray data.
The velocity measurement including at least the moving direction is performed based on the data obtained in v, and the sampling interval ΔT slower than ΔTv is obtained.
A CFM calculation unit that obtains flow velocity data by measuring a power value based on the data obtained in p, and determines the first and second hues according to the moving direction obtained by the CFM calculation unit and according to the power value. An image for generating image data for ultrasonic imaging display by color flow mapping in which the brightness is changed, and when the moving direction cannot be detected by the CFM calculator, the brightness is changed on the third hue with respect to the power value. An ultrasonic imaging apparatus comprising: a processing unit.