JP2003052694A - Ultrasonograph - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an ultrasonograph which takes images indicating the intensities of heart beats at moving speeds of an echo source. SOLUTION: The moving speed V of the echo source is detected based on the Doppler shifts of ultrasonic echoes and the intensity P of heart beats at the moving speed V is detected by a heart beat detection means 132 by arithmetic operation using a value Vn in the current time phase and a value Vo in the past time phase at the moving speed V.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ultrasonic imaging method and apparatus, and more particularly, to a pulse of a moving velocity of an echo source in a subject by utilizing a Doppler shift of an ultrasonic echo (echo). The present invention relates to an ultrasonic imaging method and apparatus for imaging an image showing dynamic intensity.

[0002]

2. Description of the Related Art In ultrasonic imaging, a blood flow image is taken by utilizing the Doppler shift of ultrasonic echo.
The blood flow image shows CFM (col
r flow mapping image or power Doppler showing the location of blood flow
It is displayed as an image. Region of interest (ROI)
For example, a tumor diagnosis or the like is performed based on the blood flow image in the “n of interest”. When performing a tumor diagnosis or the like based on a blood flow image, whether the blood flow in that portion is arterial or venous is an important clue for diagnosis.

[0003]

However, since the pulsatility of the blood flow cannot be detected in the CFM image or power Doppler image as described above, it is difficult to determine whether it is arterial or venous. . For this reason, in order to investigate the pulsatility, it is necessary to collect the Doppler signal of the point of interest again by the point Doppler method or the like, and observe the spectrum (spectrum) or listen to the Doppler sound. There was a problem of not becoming.

The present invention has been made to solve the above problems, and an object thereof is to realize an ultrasonic imaging method and apparatus for imaging an image showing the pulsation intensity of the moving speed of an echo source. is there.

[0005]

(1) A first invention for solving the above-mentioned problems is to repeatedly scan an imaging range with ultrasonic waves to receive echoes, and based on the Doppler shift of the received echoes, an echo source. Of the moving speed of the moving speed is detected, and the intensity of the pulsation of the moving speed is detected by a calculation using the value of the moving speed in the current time phase and the value in the past time phase,
The ultrasonic imaging method is characterized in that an image representing the intensity of the detected pulsation is generated.

In the first aspect of the present invention, the calculation is performed using the difference value between the value of the moving speed at the present time phase and the value at the past time phase, in that the pulsation intensity is appropriately detected. preferable.

Further, in the first invention, the calculation is performed by using an average value of the values of the moving speed in the present time phase and values in the past time phase, so that the pulsation intensity is appropriately detected. It is preferable in terms.

(2) A second invention for solving the above-mentioned problems is to repeatedly scan an imaging range with ultrasonic waves to receive an echo, and detect the moving speed of the echo source based on the Doppler shift of the received echo. Detecting the intensity of the pulsation of the moving speed by calculation using the value of the moving speed in the current time phase and the average value from the past time phase to the current time phase, An ultrasonic imaging method is characterized in that a representative image is generated.

In the first invention or the second invention, it is preferable that the dispersion of the moving speed is detected and the calculation is performed using the detected dispersion value in order to properly detect the pulsation intensity.

In the first invention or the second invention, outputting the result of the calculation at a specific time in the pulsation cycle of the heart is preferable from the viewpoint of appropriately detecting the pulsation intensity.

Further, in the first invention or the second invention, detecting the electrocardiographic signal of the object to be imaged and determining the specific time based on the electrocardiographic signal appropriately detects the pulsation intensity. It is preferable in terms.

Further, in the first invention or the second invention, the velocity average value of the moving velocity through the pulsation cycle of the heart is calculated, and the moving velocity in the present time phase and in the past time phase are calculated. It is preferable from the viewpoint of appropriately detecting the pulsation intensity that the difference between the pulsation intensity and the moving speed average value and the difference value is calculated and the pulsation intensity is detected.

Further, in the first invention or the second invention, the velocity average value of the moving velocity through the pulsation cycle of the heart is obtained, and the moving velocity in the present time phase and in the past time phase are calculated. The difference value with the value is obtained, the difference average value is obtained through the heart beat cycle for the difference value, and the beat intensity of the moving speed is detected by calculation using the velocity average value and the difference average value. Is preferable in that the pulsation intensity is appropriately detected.

Further, in the first invention or the second invention, the variance of the moving velocity is detected, a variance average value through the pulsation cycle of the heart is obtained for the detected variance, and the variance average value is used. It is preferable to perform the above calculation by appropriately detecting the pulsation intensity.

Further, in the first invention or the second invention, a maximum velocity value is obtained for the moving velocity through the pulsation cycle of the heart, and the moving velocity at the present time phase and the past time phase are obtained. It is preferable from the viewpoint of appropriately detecting the pulsation intensity that the difference between the pulsation intensity and the moving speed maximum value and the difference value is obtained and the pulsation intensity of the moving speed is detected.

In the first invention or the second invention, a maximum velocity value through the pulsation cycle of the heart is calculated for the moving velocity, and the moving velocity at the present time phase and the past time phase are obtained. A difference value with a value is obtained, a difference maximum value is obtained for the difference value through a heart beat cycle, and the intensity of the pulsation of the moving speed is detected by calculation using the velocity maximum value and the difference maximum value. Is preferable in that the pulsation intensity is appropriately detected.

Further, in the first invention or the second invention, the dispersion of the moving speed is detected, the dispersion maximum value through the pulsation cycle of the heart is obtained for the dispersion, and the dispersion maximum value is used to calculate the dispersion maximum value. It is preferable to perform the calculation in terms of appropriately detecting the pulsation intensity.

Further, in the first invention or the second invention, the electrocardiographic signal of the object to be imaged is detected, and the pulsation cycle is obtained based on the electrocardiographic signal, whereby the pulsation intensity is appropriately detected. It is preferable in terms.

Further, in the first invention or the second invention, it is preferable to obtain the pulsation period based on the periodic change of the Doppler shift, in order to appropriately detect the pulsation intensity.

In the first invention or the second invention, it is preferable to obtain the pulsation intensity properly by obtaining the pulsation period based on the periodic change of the pulsation intensity. Further, in the first invention or the second invention, it is preferable to perform the above-mentioned calculation by using an output signal in a past time phase, in order to appropriately detect the pulsation intensity.

In the first invention or the second invention, it is preferable to generate an image based on the instantaneous value of the pulsation intensity in order to properly display the pulsation intensity. Moreover, in the first invention or the second invention, generating an image based on a temporal average value of the intensity of the pulsation,
This is preferable in that the pulsation intensity is properly displayed.

In the first invention or the second invention, it is preferable to generate an image based on the peak hold value of the pulsation intensity in order to properly display the pulsation intensity.

Further, in the first invention or the second invention, a B-mode image is generated based on the received echo, and the B-mode image and the image showing the intensity of the pulsation are superimposed and displayed. Is preferable in that the pulsation intensity is appropriately displayed.

In the first invention or the second invention, generating the image showing the moving speed and displaying the speed image and the image showing the intensity of the beat in an overlapping manner are It is preferable in that the strength is properly displayed.

Further, in the first invention or the second invention, a power Doppler image representing the power of the Doppler shift signal is generated, and the power Doppler image and the image showing the intensity of the beat are displayed in an overlapping manner. It is preferable to properly display the pulsation intensity.

In the first invention or the second invention, it is preferable to display the image as a three-dimensional image in terms of properly displaying the pulsation intensity. (3) A third invention for solving the above-mentioned problems, an ultrasonic wave transmitting / receiving means for repeatedly scanning an imaging range with ultrasonic waves to receive an echo, and a moving speed of an echo source based on the Doppler shift of the received echo. A speed detecting means for detecting, a pulsation detecting means for detecting the intensity of the pulsation of the moving speed by a calculation using the value of the moving speed at the present time phase and the value at the past time phase; and the detected beat. An ultrasonic imaging apparatus, comprising: an image generating unit that generates an image representing the intensity of motion.

(4) In the fourth invention for solving the above-mentioned problems, the pulsation detecting means uses the difference value between the value of the moving speed in the present time phase and the value in the past time phase, The ultrasonic imaging apparatus described in (3) is characterized in that calculation is performed.

(5) In the fifth invention for solving the above-mentioned problems, the pulsation detecting means uses the average value of the values of the moving speed at the current time phase and the past time phase to calculate the moving speed. The ultrasonic imaging apparatus according to (3) or (4) is characterized in that calculation is performed.

(6) A sixth invention for solving the above-mentioned problems is an ultrasonic wave transmitting / receiving means for repeatedly scanning an imaging range with ultrasonic waves to receive an echo, and an echo source of an echo source based on the Doppler shift of the received echo. A velocity detecting means for detecting the moving velocity, and a beat intensity of the moving velocity are detected by a calculation using a value of the moving velocity at the present time phase and an average value from the past time phase to the current time phase. An ultrasonic imaging apparatus comprising: a pulsation detecting means; and an image generating means for generating an image representing the detected strength of the pulsation.

(7) A seventh invention for solving the above-mentioned problems is provided with a dispersion detecting means for detecting the dispersion of the moving speed, and the pulsation detecting means uses the dispersion value detected by the dispersion detecting means. The ultrasonic imaging apparatus according to any one of (3) to (6), wherein the calculation is performed using the ultrasonic imaging apparatus.

(8) The eighth invention for solving the above-mentioned problems is characterized in that the pulsation detecting means outputs the result of the calculation at a specific time in the pulsation cycle of the heart ( The ultrasonic imaging apparatus according to any one of 3) to (7).

(9) A ninth invention for solving the above-mentioned problems is provided with an electrocardiographic signal detecting means for detecting an electrocardiographic signal of an object to be imaged, and the pulsation detecting means is based on the electrocardiographic signal. The ultrasonic imaging apparatus described in (8) is characterized in that the specific time is determined.

(10) A tenth invention for solving the above-mentioned problems is an ultrasonic wave transmitting / receiving means for repeatedly scanning an imaging range with ultrasonic waves to receive an echo, and an echo source of an echo source based on the Doppler shift of the received echo. A speed detecting means for detecting a moving speed, a speed averaging means for obtaining a speed average value of the moving speed through a heart beat cycle, a value of the moving speed at a current time phase and a value at a past time phase. A difference means for obtaining a difference value of, a pulsation detecting means for detecting a pulsation intensity of the moving speed by an operation using the velocity average value and the difference value, and an image representing the detected pulsation intensity. And an image generating unit that generates the ultrasonic image.

(11) An eleventh invention for solving the above-mentioned problems is an ultrasonic wave transmitting / receiving means for repeatedly scanning an imaging range with ultrasonic waves to receive an echo, and an echo source of an echo source based on the Doppler shift of the received echo. A speed detecting means for detecting a moving speed, a speed averaging means for obtaining a speed average value of the moving speed through a heart beat cycle, a value of the moving speed at a current time phase and a value at a past time phase. Difference means for obtaining a difference value of the moving speed, a difference averaging means for obtaining a difference average value for the difference value through a heart beat cycle, and a velocity average value and a beat of the moving velocity by calculation using the difference average value. An ultrasonic imaging apparatus comprising: a pulsation detection unit that detects the intensity of a motion; and an image generation unit that generates an image representing the detected intensity of the pulsation.

(12) A twelfth invention for solving the above-mentioned problems comprises a dispersion detecting means for detecting the dispersion of the moving speed,
And a variance averaging unit that obtains a variance average value through the pulsation cycle of the heart for the variance, and the pulsation detection unit performs the calculation using the variance average value ( It is an ultrasonic imaging device as described in 10) or (11).

(13) A thirteenth invention for solving the above-mentioned problems is characterized in that the pulsation detecting means performs the calculation by using a value of the moving speed in a current time phase (10). ) To (12), the ultrasonic imaging device according to any one of the above.

(14) A fourteenth invention for solving the above-mentioned problems is characterized in that the pulsation detecting means performs the calculation by using a value of the difference value in a current time phase. ) To (13), the ultrasonic imaging device described in any one of.

(15) A fifteenth invention for solving the above-mentioned problems is characterized in that the pulsation detecting means carries out the calculation by using a value of the dispersion value in the current time phase. The ultrasonic imaging device according to any one of (1) to (14).

(16) According to a sixteenth invention for solving the above-mentioned problems, an ultrasonic wave transmitting / receiving means for repeatedly scanning an imaging range with ultrasonic waves to receive an echo, and an echo source of an echo source based on the Doppler shift of the received echo. A speed detecting means for detecting the moving speed, a maximum speed detecting means for obtaining the maximum speed value of the moving speed through the pulsation cycle of the heart, a value of the moving speed at the present time phase and a value at the past time phase A difference means for obtaining a difference value between the moving speed, a pulsation detecting means for detecting the pulsation intensity of the moving speed by an operation using the velocity maximum value and the difference value, and an image representing the detected pulsation intensity And an image generating unit that generates the.

(17) According to a seventeenth invention for solving the above-mentioned problems, an ultrasonic wave transmitting / receiving means for repeatedly scanning an imaging range with ultrasonic waves to receive an echo, and an echo source of an echo source based on the Doppler shift of the received echo. A speed detecting means for detecting the moving speed, a maximum speed detecting means for obtaining the maximum speed value of the moving speed through the pulsation cycle of the heart, a value of the moving speed at the present time phase and a value at the past time phase A difference means for obtaining a difference value between the moving speed and a maximum difference detecting means for obtaining a maximum difference value for the difference value through a heart beat cycle, and the moving speed by a calculation using the maximum speed value and the maximum difference value. An ultrasonic imaging apparatus comprising: a pulsation detection unit that detects the pulsation intensity of 1. and an image generation unit that generates an image representing the detected pulsation intensity.

(18) The eighteenth invention for solving the above-mentioned problems is a dispersion detecting means for detecting the dispersion of the moving speed, and a maximum dispersion detecting means for obtaining the maximum dispersion value of the dispersion through the pulsation cycle of the heart. And the pulsation detecting means performs the calculation using the maximum dispersion value. The ultrasonic imaging apparatus according to (16) or (17) is characterized in that.

(19) The nineteenth invention for solving the above-mentioned problems is characterized in that the pulsation detecting means carries out the calculation by using a value of the moving speed in a current time phase (16). ) To (18), the ultrasonic imaging device according to any one of the above.

(20) A twentieth invention for solving the above-mentioned problems is characterized in that the pulsation detecting means carries out the calculation by using a value of the difference value in a current time phase (17). ) To (19), the ultrasonic imaging apparatus described in any one of

(21) The twenty-first invention for solving the above-mentioned problems is characterized in that the pulsation detecting means carries out the calculation by using a value of the dispersion value in a current time phase (18). ) To (20). The ultrasonic imaging device according to any one of the above.

(22) A twenty-second invention for solving the above-mentioned problems is provided with an electrocardiographic signal detecting means for detecting an electrocardiographic signal of an object to be imaged, and the pulsation detecting means is based on the electrocardiographic signal. The ultrasonic imaging apparatus according to any one of (10) to (21), wherein the pulsation cycle is obtained.

(23) The twenty-third invention for solving the above-mentioned problems is characterized in that the pulsation detecting means obtains the pulsation cycle based on a periodic change of the Doppler shift. ) To (21), the ultrasonic imaging device described in any one of.

(24) A twenty-fourth invention for solving the above-mentioned problems is characterized in that the pulsation detecting means obtains the pulsation cycle based on a periodical change in the strength of the pulsation detected by itself. The ultrasonic imaging apparatus according to any one of (10) to (21).

(25) The twenty-fifth invention for solving the above-mentioned problems is characterized in that the pulsation detecting means carries out the calculation by using an output signal in the past time phase output by itself. The ultrasonic imaging apparatus according to any one of 3) to (24).

(26) The twenty-sixth invention for solving the above-mentioned problems is characterized in that the image generating means generates an image based on the instantaneous value of the intensity of the pulsation. 25) The ultrasonic imaging device according to any one of 25).

(27) The twenty-seventh invention for solving the above-mentioned problems is characterized in that the image generating means generates an image based on a temporal average value of the intensity of the pulsation (3). The ultrasonic imaging apparatus according to any one of (1) to (25).

(28) The twenty-eighth invention for solving the above-mentioned problems is characterized in that the image generating means generates an image based on the peak hold value of the intensity of the pulsation (3) to (3). (25) The ultrasonic imaging device according to any one of (25).

(29) A twenty-ninth invention for solving the above-mentioned problems is characterized by comprising display means for displaying the image showing the intensity of the pulsation as a three-dimensional image. The ultrasonic imaging device according to any one of 1).

(30) A thirtieth invention for solving the above-mentioned problems shows a B-mode image generating means for generating a B-mode image based on the received echo, and the B-mode image and the intensity of the pulsation. (3) to (2), characterized by comprising: display means for displaying the image in an overlapping manner.
8) The ultrasonic imaging device according to any one of 8).

(31) According to a thirty-first invention for solving the above-mentioned problems, a speed image generating means for generating an image showing the moving speed and the speed image and the image showing the intensity of the beat are superposed. The ultrasonic imaging apparatus according to any one of (3) to (28), further comprising: a display unit for displaying.

(32) A thirty-second invention for solving the above-mentioned problems is a power Doppler image generating means for generating a power Doppler image representing the power of the Doppler shift signal,
The display device for displaying the power Doppler image and the image showing the intensity of the pulsation in an overlapping manner, and (3) to (28). It is a sound wave imaging device.

(33) In the thirtieth invention for solving the above-mentioned problems, any one of (30) to (32) is characterized in that the display means displays the image as a three-dimensional image. 3 is an ultrasonic imaging apparatus.

(Operation) In the present invention, the strength of the pulsation of the moving speed is calculated by using the value of the moving speed of the echo source obtained from the Doppler shift of the ultrasonic echo at the present time phase and the value at the past time phase. Is detected and an image representing the intensity of the beat is generated.

[0058]

BEST MODE FOR CARRYING OUT THE INVENTION Hereinafter, embodiments of the present invention will be described in detail with reference to the drawings. The present invention is not limited to the embodiment. FIG. 1 shows a block diagram of the ultrasonic imaging apparatus. This device is an example of an embodiment of the present invention. The configuration of this device shows an example of an embodiment relating to the device of the present invention. The operation of the apparatus shows an example of an embodiment relating to the method of the present invention.

As shown in FIG. 1, this device has an ultrasonic probe 2 (probe). The ultrasonic probe 2
Multiple ultrasonic transducers (not shown)
). The individual ultrasonic transducers are, for example, PZT (titanium (T
i) Zirconate (Zr) lead) ceramics (cera
mics) or other piezoelectric material. The ultrasonic probe 2 is used by being brought into contact with the subject 4 by an operator.

The ultrasonic probe 2 is connected to the transmitting / receiving section 6. The transmission / reception unit 6 gives a drive signal to the ultrasonic probe 2 to transmit an ultrasonic wave. The transmitting / receiving unit 6 also receives the echo signal received by the ultrasonic probe 2. The ultrasonic probe 2 and the transmission / reception unit 6 are an example of the embodiment of the ultrasonic transmission / reception means in the present invention.

A block diagram of the transmission / reception unit 6 is shown in FIG. As shown in the figure, the transmission / reception unit 6 determines the transmission timing (tim
ing) generating unit (602). The transmission timing generation unit 602 periodically generates a transmission timing signal to generate a transmission beam former (beamf).
input).

The transmission beamformer 604 performs beamforming of the transmission wave, and generates a beamforming signal for forming an ultrasonic beam in a predetermined direction based on the transmission timing signal. The beamforming signal is composed of a plurality of drive signals provided with a time difference corresponding to the azimuth. The transmission beamformer 604 inputs the transmission beamforming signal to the transmission / reception switching unit 606.

The transmission / reception switching unit 606 inputs the beamforming signal to the ultrasonic transducer array. In the ultrasonic transducer array, a plurality of ultrasonic transducers forming a transmission aperture respectively generate ultrasonic waves having a phase difference corresponding to a time difference between drive signals. An ultrasonic beam along a sound ray in a predetermined direction is formed by wavefront synthesis of the ultrasonic waves.

A reception beam former 610 is connected to the transmission / reception switching unit 606. Transmission / reception switching unit 60
Reference numeral 6 denotes a reception beamformer 6 for receiving a plurality of echo signals received by the reception aperture in the ultrasonic transducer array.
Enter in 10. The reception beamformer 610 performs reception beamforming corresponding to the sound ray of the transmission wave. The reception beamformer 610 imparts a time difference to a plurality of reception echoes to adjust their phases, and then adds them to add sound in a predetermined direction. Form an echo received signal along the line.

The transmission of the ultrasonic beam is repeated at predetermined time intervals by the transmission timing signal generated by the transmission timing generation unit 602. In accordance therewith, the transmitting beam former 604 and the receiving beam former 610 change the direction of the sound ray by a predetermined amount.
As a result, the inside of the subject 4 is sequentially scanned by the sound ray. The transmission / reception unit 6 having such a configuration performs scanning as shown in FIG. 3, for example. That is, the fan-shaped two-dimensional area 206 is defined by the sound ray 202 extending from the radiating point 200 in the z direction.
Is scanned in the θ direction, so-called sector scan (sect scan
or scan).

When the transmitting and receiving apertures are formed by using a part of the ultrasonic transducer array, the apertures are sequentially moved along the array to perform scanning as shown in FIG. 4, for example. You can
That is, the sound ray 202 emitted from the radiating point 200 in the z direction
Is moved in parallel along the linear locus 204 to scan the rectangular two-dimensional area 206 in the x direction, and so-called linear scan is performed.

The ultrasonic transducer array is
A so-called convex array (convex array) formed along an arc extending in the ultrasonic wave transmission direction.
In the case of y), a sound ray scan similar to the linear scan is performed, and as shown in FIG.
Needless to say, so-called convex scan can be performed by moving 00 along the arcuate locus 204 and scanning the fan-shaped two-dimensional region 206 in the θ direction.

The transmitting / receiving unit 6 is connected to the B mode processing unit 10 and the Doppler processing unit 12. The echo reception signal for each sound ray output from the transmitter / receiver 6 is B
It is input to the mode processing unit 10 and the Doppler processing unit 12. The electrocardiographic signal detection unit 8 is connected to the Doppler processing unit 12, and the electrocardiographic signal of the subject 4 is input. The electrocardiographic signal detection unit 8 is an example of an embodiment of electrocardiographic signal detection means in the present invention.

The B-mode processing section 10 forms B-mode image data. As shown in FIG. 6, the B-mode processing unit 10 includes a logarithmic amplification unit 102 and an envelope detection unit 104. The B-mode processing unit 10 logarithmically amplifies the echo reception signal by the logarithmic amplification unit 102, envelope-detects it by the envelope detection unit 104, and represents the intensity of the echo at each reflection point on the acoustic line, that is, the A scope. A (scope) signal is obtained, and B-mode image data is formed by using each instantaneous amplitude of the A scope signal as a luminance value.

The Doppler processing unit 12 forms Doppler image data. The Doppler image data includes velocity data, dispersed data, power data, and pulsation intensity data, which will be described later. As shown in FIG. 7, the Doppler processing unit 12 includes a quadrature detection unit 120 and an MTI filter (moving target indication).
filter) 122, autocorrelation calculation unit 124,
Average velocity calculation unit 126, distributed calculation unit 128
And a power calculation unit 130.

The portion consisting of the quadrature detection unit 120, the MTI filter 122, the autocorrelation calculation unit 124 and the average flow velocity calculation unit 126 is an example of the embodiment of the velocity detecting means in the present invention. The part including the quadrature detection unit 120, the MTI filter 122, the autocorrelation calculation unit 124, and the dispersion calculation unit 128 is
It is an example of an embodiment of the dispersion detecting means in the present invention.

In the Doppler processing unit 12, the quadrature detection unit 120 performs quadrature detection on the echo reception signal, and the MTI filter 122 performs MTI processing to obtain the Doppler shift of the echo signal. Further, the autocorrelation calculation unit 124 performs autocorrelation calculation on the output signal of the MTI filter 122,
The average flow velocity calculation unit 126 obtains the average flow velocity V from the autocorrelation calculation result, the variance calculation unit 128 obtains the variance T of the flow velocity from the autocorrelation calculation result, and the power calculation unit 1
The power PW of the Doppler signal from the autocorrelation calculation result at 30
Ask for.

As a result, each data representing the average flow velocity V of the echo source moving in the subject 4, for example, blood, its dispersion T, and the power PW of the Doppler signal is obtained for each sound ray. These image data show the average flow velocity, variance, and power of each point (pixel: pixel) on the sound ray. Hereinafter, the average flow velocity is simply referred to as velocity. The velocity is obtained as a component in the sound ray direction. Further, a direction approaching the ultrasonic probe 2 and a direction approaching the ultrasonic probe 2 are distinguished from each other. The echo source is not limited to blood, but may be, for example, a microball injected into a blood vessel or the like.
oon) A contrast agent or the like may be used. Hereinafter, an example of blood will be described, but the same applies to the case of a microballoon contrast agent.

The Doppler processing section 12 also has a beat detection unit 132 and a memory 134, as shown in FIG. The beat detection unit 132 is, for example, a DSP (d
digital signal processor (MPU) and MPU (micro processing uni)
t) and the like. The beat detection unit 132 is an example of an embodiment of the beat detection means in the present invention.

Beat detection unit 132 and memory 13
4, the output data of the average flow velocity calculation unit 126, that is, the velocity V is input for each pixel. Further, the variance T is input from the variance calculation unit 128 to each pixel in the pulsation detection unit 132, and the R wave timing signal R of the electrocardiographic signal is input from the electrocardiographic signal detection unit 8.

The memory 134 stores one frame (f
The input speed data V corresponding to (frame) is stored. As the stored speed data, the data one frame before regarding the same pixel as the pixel of the input speed data V is read out and input to the beat detection unit 132. As a result, the velocity data V is input to the beat detection unit 132 via the memory 134 with a delay of one frame.

The memory 134 may store not only one frame but also several frames of speed data and read them out with a delay of several frames. Hereinafter, an example of one frame delay will be described, but the same applies to the case of several frame delay. Also, the memory 134 does not necessarily have to be a storage device,
The delay unit may have a delay time corresponding to one frame time or several frame times. Although an example of the memory will be described below, the same applies to the case of the delay unit. One frame time is 1/30 second, for example.

The pulsation detection unit 132 calculates the pulsation of the blood flow velocity based on the calculation using the velocity data Vn input from the average velocity calculation unit 126, the velocity data Vo read from the memory 134, and the variance T. Detect intensity. The speed data Vn is an example of an embodiment of the value of the moving speed in the present time phase in the present invention. The speed data Vo is an example of an embodiment of the value of the moving speed in the past time phase in the present invention. Beat detection unit 13
2 outputs the detected pulsation intensity data P. The beat intensity data P represents the beat intensity for each pixel on the sound ray. The pulsation intensity is detected as follows.

FIG. 9 schematically shows changes in the velocity of the blood flow with the pulsation of the heart, that is, the pulsation of the blood flow velocity. (A) in the figure
Shows an electrocardiographic signal, (b) shows arterial flow velocity, and (c) shows venous flow velocity. As shown in (b), the arterial flow velocity rapidly increases from time t1 to t2, which is slightly delayed from the generation of the R wave of the electrocardiographic signal, and quickly after time t4 to t5, after passing the peak. It then decreases, and then gradually decreases over the rest of the period. The venous flow velocity is, as shown in (c), time t that is later than time t2.
The speed increase starts from 3, but the speed increase is small.

The velocity data Vn also changes as shown in (b) or (c) according to such a change in the flow velocity. Also,
The speed data Vo read from the memory 134 similarly changes with a delay of one frame time. Hereinafter, the speed data Vn is the current speed Vn, and the speed data Vo is the past speed V.
Call it o.

The pulsation detecting unit 132 detects the strength P of the pulsation by the following equation using these input data.

[0082] P = k · | Vn-Vo | (1)

Here, k: constant, that is, as shown schematically in FIG. 10, the strength of the pulsation is detected based on the difference between the current speed Vn and the past speed Vo. Then, it is assumed that the greater the difference value ΔV, the greater the pulsation intensity.

Alternatively, the difference value ΔV may be divided by the current velocity Vn, and the pulsation intensity P may be detected by the following equation.

[0085]

Here, it is convenient to use the equation m: constant (2) because the pulsatility intensity P can be normalized and expressed. For example, as shown in FIG. 11, the constant m may be a variable constant that changes according to the current speed Vn, and weighting may be performed according to the current speed Vn. That is, for speeds below the predetermined value Vth, the value of the constant m is reduced to reduce the weighting. As a result, the sensitivity of pulsation detection for venous blood flow, which is generally slow, can be reduced, and the pulsation detection of arterial blood flow can be reliably performed. The characteristic curve of the variable constant m is not limited to that shown in the figure, and may be set appropriately.

The pulsation detection unit 132 detects the pulsation intensity by referring to the variance value T in addition to the calculation by the above equation. Since the arterial flow velocity has a larger variance in velocity than the venous flow velocity, by referring to the variance value T, the pulsation intensity can be detected with high reliability. That is, for example,
Even if the value of P according to the expression (1) or the expression (2) is large, if the variance value T is small, the value of P is correspondingly reduced, and excessive pulsation intensity detection is suppressed.

Further, by utilizing the characteristic of the arterial flow velocity, the pulsation intensity can be detected with high certainty. That is, as shown in (b) of FIG.
Since the rapid increase in velocity from t to t2 is a characteristic of arterial blood flow, this period is selected to detect the pulsation as described above.
During this period, the rate of change in arterial flow velocity is the largest and the change in venous flow velocity is gradual. You can The pulsation detection period is time t4 instead of or in addition to the period from time t1 to t2.
The period from to t5 may be used. The timing is set based on the R wave timing signal R. Alternatively, it may be performed based on a Doppler signal that periodically changes with a pulsation, or may be performed based on a periodical change that appears in the pulsation intensity P detected by itself.

In order to normalize the pulsation intensity P, an average value of the current speed Vn and the past speed Vo may be used instead of the current speed Vn. This is preferable in that the detected value P of the pulsation intensity is stabilized against noise or the like. In that case, the constant m is changed according to the average speed. In addition,
The average value of the current speed Vn and the past speed Vo is obtained by the beat detection unit 132.

Further, the average value of the velocity may be an average value of the electrocardiographic signal over one cycle or several cycles. This is preferable in that the detected value P of the pulsation intensity is further stabilized. In that case, the constant m is changed according to the average speed. The average value of the electrocardiographic signal over one cycle or several cycles is obtained by the pulsation detection unit 132. The period of the electrocardiographic signal is detected based on the R wave timing signal R.
Alternatively, it may be detected based on a periodic change in Doppler shift, or may be detected based on a periodic change that appears in the pulsation intensity P detected by itself.

The normalization may be performed by using the maximum value of the velocity of the electrocardiographic signal during one cycle or several cycles. This also contributes to the stabilization of the detected value P. In that case, the constant m is changed according to the maximum speed. The maximum value of the electrocardiographic signal during one cycle or several cycles is obtained by the beat detection unit 132.

In the above, as the difference value ΔV, instead of using the value at each time point, or in addition to it, an average value or a maximum value over one cycle or several cycles of the electrocardiographic signal may be used. This also contributes to the stabilization of the detected value P. The average value or the maximum value of the electrocardiographic signal over one cycle or several cycles is determined by the beat detection unit 132.

As the variance value T to be referred to, instead of or in addition to the value at each time point, an average value or maximum value of the electrocardiographic signal over one cycle or several cycles may be used. The average value or the maximum value of the electrocardiographic signal over one cycle or several cycles is determined by the beat detection unit 132. This also contributes to the stabilization of the detected value P.

The beat detection unit 132 is shown in FIG.
As shown in FIG. 7, a pulsation detection flag (flag) FLG is also output, and this is regressively input with a delay of one frame via the memory 134, and the pulsation intensity is detected by also referring to the input flag FLGo. You may do it. The pulsation detection flag FLG is a signal indicating whether or not a pulsation has been detected, and by inputting this with a delay of one frame, it is possible to refer to the detection result one frame before. The beat detection flag FLG is an example of an embodiment of the output signal of the beat detecting means in the present invention.

The beat detection flag FLG is used as follows. That is, for example, if the result of denying the existence of the beat is obtained one frame before, even if the beat is detected in the current frame, there is a possibility that it is an error due to noise or the like. Therefore, in such a case, the beat detected in the current frame is invalidated. By doing so, the stability of pulsation detection can be maintained.

The beat detection unit 132 uses the past velocity Vo.
Instead of, the average value of the velocities up to that point may be used to detect the intensity of the pulsation. An example of such a configuration is shown in FIG. As shown in the figure, an average calculation unit 136 is provided, and the average value V of the current speed Vn and the average speed data Vmo one frame before read from the memory 134.
m is calculated and input to the beat detection unit 132. The average value Vm is stored in the memory 134, read in the next frame, and input to the average calculation unit 136. As a result, the output data of the average calculation unit 136 becomes the average value of the speeds detected so far for each pixel on the sound ray.

The beat detection unit 132 uses the velocity data V
The beat intensity is detected by calculation using n, the average value Vm, and the variance T. The calculation formula is the above formula (1) or (2)
In the formula, the past speed Vo is replaced with the average value Vm. By setting the base value for obtaining the difference value to the average value Vm of the detected velocities up to now, it is possible to perform stable pulsation intensity detection that is less susceptible to noise and the like. With such a configuration, for example, as shown in FIG. 14, for arterial blood flow, the difference between Vn and Vm is clarified, and the intensity of pulsation is easily detected. Further, as shown in FIG. 15, even if the pulsation intensity is relatively weak, the pulsation intensity can be reliably captured.

In the example shown in FIG. 13, as in the example shown in FIG. 8, the average value or the maximum value of the electrocardiographic signal over one cycle or several cycles is used for the velocity, the difference value, and the dispersion value. Of course, it is okay. Further, in accordance with the example shown in FIG. 12, the beat detection flag FLG is recursively set via the memory 134.
Of course, you can type it and refer to it.

The B-mode processor 10 and the Doppler processor 12 are connected to the image processor 14. Image processing unit 1
4 is an example of an embodiment of the image generating means in the present invention. The image processing unit 14 generates a B-mode image, a Doppler image, and a pulsation intensity image based on the data input from the B-mode processing unit 10 and the Doppler processing unit 12, respectively.

B-mode processor 10 and image processor 14
The part consisting of is an example of the embodiment of the B-mode image generating means in the present invention. Quadrature detection unit 120,
An MTI filter 122, an autocorrelation calculation unit 124,
The portion including the average flow velocity calculation unit 126 and the image processing unit 14 is an example of the embodiment of the velocity image generating means in the present invention. The portion including the quadrature detection unit 120, the MTI filter 122, the autocorrelation calculation unit 124, the power calculation unit 130, and the image processing unit 14 is an example of the embodiment of the power Doppler image generation means in the present invention.

The image processing section 14, as shown in FIG.
A sound ray data memory 142 connected by a bus 140, a digital memory,
Scan converter (digital scan co)
The image processor 148 is provided with an image memory 146 and an image processor 148.

The B-mode image data and the Doppler image data input from the B-mode processing unit 10 and the Doppler processing unit 12 for each sound ray are stored in the sound ray data memory 142, respectively. In the sound ray data memory 142, a sound ray data space based on image data is formed. The digital scan converter 144 converts the data in the sound ray data space into the data in the physical space by scan conversion. As a result, the sound ray data space is converted into the physical data space. The image data converted by the digital scan converter 144 is stored in the image memory 146. The image processor 148 performs predetermined data processing on the data in the sound ray data memory 142 and the image memory 146.
Details of the data processing will be described later.

A display unit 16 is connected to the image processing unit 14. The display unit 16 is an example of an embodiment of the display means in the present invention. The display unit 16 is provided with an image signal from the image processing unit 14 and displays an image based on the image signal. The display unit 16 has a color (col
or) Graphic display that can display images (g
a graphic display).

The above transmitting / receiving section 6, B mode processing section 10,
Doppler processing unit 12, image processing unit 14, and display unit 16
A control unit 18 is connected to the. The control unit 18 gives a control signal to each of these units to control the operation thereof. Also,
Various notification signals are input from each controlled unit.

Under the control of the control unit 18, the B mode operation and the Doppler mode operation are executed. An operation unit 20 is connected to the control unit 18. The operation unit 20 is operated by an operator and inputs appropriate commands and information to the control unit 18. The operation unit 20 is composed of, for example, an operation panel equipped with a keyboard and other operation tools.

The operation of this apparatus will be described. The operator brings the ultrasonic probe 2 into contact with a desired portion of the subject 4,
By operating 0, for example, an imaging operation using both the B mode and the Doppler mode is performed. As a result, under the control of the control unit 18, the B mode imaging and the Doppler mode imaging are performed in time division. Thus, for example, the mixed scan of the B mode and the Doppler mode is performed at a rate of performing the B mode scan once every time the Doppler mode scan is performed several times.

In the B mode, the transmission / reception unit 6 scans the inside of the subject 4 in the sound ray sequence through the ultrasonic probe 2 and receives the echoes one by one. B-mode processing unit 10
Is a logarithmic amplification unit 102 that logarithmically amplifies the echo reception signal input from the transmission / reception unit 6, and the envelope detection unit 10
In step 4, envelope detection is performed to obtain an A scope signal, and B mode image data for each sound ray is formed based on the A scope signal. The image processing unit 14 stores the B-mode image data for each sound ray input from the B-mode processing unit 10 in the sound ray data memory 142. Thereby, in the sound ray data memory 142,
A sound ray data space for B-mode image data is formed.

In the Doppler mode, the transmission / reception unit 6 scans the inside of the subject 4 in the sound ray sequence through the ultrasonic probe 2 and receives the echoes one by one. At this time, ultrasonic waves are transmitted and echoes are received a plurality of times per sound ray.
The Doppler processing unit 12 performs quadrature detection on the echo reception signal with the quadrature detection unit 120, and uses the MTI filter 122 to perform MT detection.
I processing is performed, the autocorrelation calculation unit 124 obtains the autocorrelation, the average flow velocity calculation unit 126 obtains the average flow velocity from the autocorrelation result, the variance calculation unit 128 obtains the variance, and the power calculation unit 130 obtains the power. Further, the pulsation detection unit 132 obtains the pulsation intensity as described above. These calculated values serve as image data representing, for example, the average velocity of blood flow and its variance, the power of the Doppler signal, and the pulsation intensity of blood flow for each sound ray and for each pixel. It should be noted that the MTI processing in the MTI filter 122 is performed by using the echo reception signals a plurality of times per sound ray.

The image processing unit 14 stores in the sound ray data memory 142 each Doppler image data for each sound ray and each pixel input from the Doppler processing unit 12. As a result, a sound ray data space for each Doppler image data is formed in the sound ray data memory 142. The image processor 148 uses the sound ray data memory 1
The B-mode image data of 42 and the Doppler image data are scan-converted by the digital scan converter 144 and written in the image memory 146.

At this time, the Doppler image data is written as CFM image data, power Doppler image data and pulsation intensity image data in which dispersion is added to the velocity. Alternatively, it may be written as CFM-like image data in which pulsation intensity is added to velocity. Further, the power Doppler image data may be written as power Doppler similar image data in which pulsation intensity is added.

The image processor 148 writes the B-mode image data, CFM image data, power Doppler image data, pulsation intensity image data, CFM similar image data and power Doppler similar image data in separate areas. The B-mode image shows a tomographic image of the internal tissue on the sound ray scanning plane. The CFM image is an image showing a two-dimensional distribution such as the blood flow velocity on the sound ray scanning plane. In this image, the display color is changed according to the direction of blood flow. Also,
The brightness of the display color is changed according to the speed. In addition, the color mixing ratio of a predetermined color is increased and the purity of the display color is changed according to the dispersion.

The power Doppler image is an image showing the presence of blood flow or the like on the sound ray scanning plane. In the power Doppler image, the direction of blood flow is not distinguished, so only one display color is used. The display color is different from the color used for the CFM image. The brightness of the display color is changed according to the signal strength. This image substantially shows blood vessels and the like.

The pulsation intensity image is an image showing a two-dimensional distribution of pulsation intensity such as blood flow on the sound ray scanning plane. The beat intensity image is represented by one color. The display color is different from the colors used for the CFM image and the power Doppler image. The brightness of the display color is changed according to the intensity of the beat. By configuring the pulsation intensity image based on the instantaneous value of the pulsation intensity, it is possible to obtain an image showing a change in the pulsation intensity in real time. By configuring the pulsation intensity image based on the time average value of the pulsation intensity, it is possible to obtain an image in which changes in the pulsation intensity are smoothed and shown. By configuring the pulsation intensity image based on the peak-hold value of the pulsation intensity, the pulsation intensity can be displayed as an easy-to-see image with little flicker. The peak hold value may be one that decays over time.

When the pulsation intensity image is generated as the CFM-like image or the power Doppler-like image, the purity of the speed or power display color is changed according to the pulsation intensity. However, the type of color to be mixed is changed so that the distinction from dispersion is clear.

When displaying these images on the display unit 16, for example, the B-mode image and the CFM image are displayed in an overlapping manner. As a result, it is possible to observe a blood flow velocity distribution image having a clear positional relationship with internal tissues. In addition, the B-mode image and the power Doppler image are displayed in an overlapping manner. In this case, it is possible to observe the running state of the blood vessel having a clear positional relationship with the internal tissue.

The B-mode image and the pulsation intensity image are superimposed and displayed. In this case, it is possible to observe an arterial running state having a clear positional relationship with internal tissues. This makes it possible to confirm at a glance whether or not the blood vessel in the ROI is arterial. In particular, when the CFM-like image or the power Doppler-like image is displayed, the velocity distribution and its pulsation intensity, or the distribution of the flowing echo source and the velocity pulsation intensity can be visually recognized at once.

By moving the ultrasonic probe 2 in the direction perpendicular to the sound ray scanning plane, for example, the inside of the subject 4 is moved to 3
The dimension can be scanned. In that case, for each of the above-mentioned image data of the three-dimensional space obtained by the three-dimensional scanning, for example, maximum intensity projection (MIP: maximum in)
A three-dimensional image can be obtained by performing intensity projection) or the like. Then, by displaying those images on the display unit 16,
A pulsation intensity image and the like can be displayed three-dimensionally.

Although the example of displaying the arterial blood flow based on the pulsation intensity has been described above, it goes without saying that the venous blood flow can be displayed by focusing on the flow velocity having a small pulsation intensity. Absent. Therefore, it goes without saying that the venous blood flow can be displayed instead of or in addition to the arterial blood flow.

[0119]

As described in detail above, according to the present invention, it is possible to realize an ultrasonic imaging method and apparatus for imaging an image showing the pulsation intensity of the moving speed of an echo source.

[Brief description of drawings]

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

FIG. 2 is a block diagram of a transmission / reception unit in the device shown in FIG.

FIG. 3 is a schematic diagram of sound ray scanning by the apparatus shown in FIG.

FIG. 4 is a schematic diagram of sound ray scanning by the apparatus shown in FIG.

5 is a schematic diagram of sound ray scanning by the apparatus shown in FIG.

6 is a block diagram of a B-mode processing unit in the apparatus shown in FIG.

FIG. 7 is a block diagram of a part of the Doppler processing unit in the device shown in FIG.

8 is a block diagram of a part of a Doppler processing unit in the apparatus shown in FIG.

FIG. 9 is a schematic diagram showing a time change of an arterial flow velocity and a venous flow velocity.

FIG. 10 is an operation explanatory view of the device shown in FIG.

FIG. 11 is a graph showing an example of characteristics of a constant m.

12 is a block diagram of a part of a Doppler processing unit in the device shown in FIG.

FIG. 13 is a block diagram of a part of a Doppler processing unit in the device shown in FIG.

FIG. 14 is an explanatory diagram of the operation of the apparatus shown in FIG.

FIG. 15 is an explanatory diagram of the operation of the device shown in FIG.

FIG. 16 is a block diagram of an image processing unit in the apparatus shown in FIG.

[Explanation of symbols]

2 Ultrasonic probe 4 subject 6 transmitter / receiver 8 ECG signal detector 10 B mode processing unit 12 Doppler processing section 14 Image processing unit 16 Display 18 Control unit 20 Operation part 120 Quadrature detection unit 122 MTI filter 124 Autocorrelation calculation unit 126 Average velocity calculation unit 128 distributed computing units 130 Power calculation unit 132 Beat detection unit 134 memory 136 Average calculation unit

   ─────────────────────────────────────────────────── ─── Continued front page    F-term (reference) 4C301 AA02 BB01 BB02 CC02 DD02                       EE20 FF28 GB04 GB06 HH13                       HH31 HH43 HH52 HH54 JB11                       JB28 JB29 JB36 JB50 KK16                       LL02 LL04 LL06

Claims (26)

[Claims] 1. An ultrasonic wave transmitting / receiving means for repeatedly scanning an imaging range with ultrasonic waves to receive an echo, a speed detecting means for detecting a moving speed of an echo source based on a Doppler shift of the received echo, and the moving speed. Of the current time phase and a value using the values in the past time phase, the pulsation detecting means for detecting the pulsation intensity of the moving speed, and an image for generating an image representing the detected pulsation intensity An ultrasonic imaging apparatus comprising: a generating unit. 2. The pulsation detecting means performs the calculation by using a difference value between a value of the moving speed in a current time phase and a value in a past time phase. The ultrasonic imaging device described. 3. The pulsation detecting means performs the calculation using an average value of a value of the moving speed in a current time phase and a value in a past time phase. The ultrasonic imaging apparatus according to claim 2. 4. An ultrasonic wave transmitting / receiving means for repeatedly scanning an imaging range with ultrasonic waves to receive an echo, a speed detecting means for detecting a moving speed of an echo source based on a Doppler shift of the received echo, and the moving speed. Of the pulsation of the moving speed by the calculation using the value in the current time phase and the average value from the past time phase to the current time phase, and the strength of the detected pulsation And an image generating unit that generates an image representing the ultrasonic image. 5. The pulsation detecting means outputs the result of the calculation at a specific time in the pulsation cycle of the heart, according to any one of claims 1 to 4. The ultrasonic imaging device according to. 6. An electrocardiographic signal detecting means for detecting an electrocardiographic signal of an imaging target is provided, and the pulsation detecting means determines the specific time based on the electrocardiographic signal. Item 6. The ultrasonic imaging device according to item 5. 7. An ultrasonic wave transmitting / receiving means for repeatedly scanning an imaging range with ultrasonic waves to receive an echo, a speed detecting means for detecting a moving speed of an echo source based on a Doppler shift of the received echo, and the moving speed. A velocity averaging means for obtaining a velocity average value through a heart beat cycle, a difference means for obtaining a difference value between the value of the moving velocity in the current time phase and a value in the past time phase, and the velocity average value And a pulsation detecting unit that detects the intensity of the pulsation at the moving speed by calculation using the difference value, and an image generating unit that generates an image representing the detected intensity of the pulsation. Ultrasonic imaging device. 8. An ultrasonic wave transmitting / receiving means for repeatedly scanning an imaging range with ultrasonic waves to receive an echo, a speed detecting means for detecting a moving speed of an echo source based on a Doppler shift of the received echo, and the moving speed. For each of the difference values, a velocity averaging means for obtaining a velocity average value through the pulsation cycle of the heart Difference averaging means for obtaining a difference average value through a pulsation cycle of the heart; pulsation detecting means for detecting pulsation intensity of the moving speed by calculation using the velocity average value and the difference average value; An ultrasonic imaging apparatus, comprising: an image generating unit that generates an image representing the detected intensity of the pulsation. 9. The ultrasonic imaging apparatus according to claim 7, wherein the pulsation detecting means performs the calculation using a value of the moving speed in a current time phase. 10. The ultrasonic imaging apparatus according to claim 8 or 9, wherein the pulsation detecting means performs the calculation using a value of the difference value in a current time phase. 11. An ultrasonic wave transmitting / receiving means for repeatedly scanning an imaging range with ultrasonic waves to receive an echo, a speed detecting means for detecting a moving speed of an echo source based on a Doppler shift of the received echo, and the moving speed. A maximum velocity detecting means for obtaining a maximum velocity value through a heart beat cycle, a difference means for obtaining a difference value between the value of the moving velocity in the present time phase and the value in the past time phase, and the velocity maximum A pulsation detection unit that detects the intensity of the pulsation of the moving speed by calculation using the value and the difference value; and an image generation unit that generates an image representing the detected intensity of the pulsation. A characteristic ultrasonic imaging device. 12. An ultrasonic wave transmitting / receiving unit for repeatedly scanning an imaging range with ultrasonic waves to receive an echo, a speed detecting unit for detecting a moving speed of an echo source based on a Doppler shift of the received echo, and the moving speed. A maximum velocity detecting means for obtaining a maximum velocity value through the heart beat cycle, a difference means for obtaining a difference value between the value of the moving velocity in the current time phase and the value in the past time phase, and the difference value A maximum difference detecting means for obtaining a maximum difference value through the pulsation cycle of the heart, and a pulsation detecting means for detecting the pulsation intensity of the moving speed by a calculation using the maximum speed value and the maximum difference value. And an image generating unit configured to generate an image representing the detected intensity of the pulsation, the ultrasonic imaging apparatus. 13. The ultrasonic imaging apparatus according to claim 11 or 12, wherein the pulsation detecting means performs the calculation by using a value of the moving speed in a current time phase. 14. The ultrasonic imaging apparatus according to claim 12, wherein the pulsation detection means performs the calculation using a value of the difference value in a current time phase. 15. An electrocardiographic signal detecting means for detecting an electrocardiographic signal of an imaging target is provided, and the pulsation detecting means obtains the pulsation cycle based on the electrocardiographic signal. The ultrasonic imaging apparatus according to any one of claims 7 to 14. 16. The pulsation detecting means obtains the pulsation cycle based on a periodic change of the Doppler shift, according to any one of claims 7 to 14. The ultrasonic imaging device according to. 17. The pulsation detecting means obtains the pulsation cycle based on a periodical change in the strength of the pulsation detected by the pulsation detecting means. The ultrasonic imaging device according to any one of 1. 18. The beat detecting means performs the calculation using an output signal in the past time phase output by itself.
The ultrasonic imaging apparatus according to any one of claims 1 to 17, characterized in that. 19. The superimposing apparatus according to claim 1, wherein the image generating unit generates an image based on an instantaneous value of the intensity of the pulsation. Sound wave imaging device. 20. The image generating means generates an image based on a temporal average value of the intensity of the pulsation, according to any one of claims 1 to 19. Ultrasonic imaging device. 21. The image generating means generates an image based on a peak hold value of the intensity of the pulsation, according to any one of claims 1 to 18. Ultrasonic imaging device. 22. The ultrasonic wave according to claim 1, further comprising a display unit that displays an image showing the intensity of the pulsation as a three-dimensional image. Imaging device. 23. B-mode image generation means for generating a B-mode image based on the received echo, and display means for superimposing and displaying the B-mode image and the image showing the intensity of the pulsation. The ultrasonic imaging apparatus according to any one of claims 1 to 21, further comprising: 24. A velocity image generating means for generating an image showing the moving velocity, and a display means for displaying the velocity image and the image showing the intensity of the beat in an overlapping manner. The ultrasonic imaging apparatus according to any one of claims 1 to 21. 25. Power Doppler image generating means for generating a power Doppler image representing the power of the Doppler shift signal, and display means for superimposing and displaying the power Doppler image and the image showing the intensity of the beat. The ultrasonic imaging apparatus according to any one of claims 1 to 21, further comprising: 26. The ultrasonic imaging apparatus according to claim 23, wherein the display unit displays the image as a three-dimensional image.