JP3238467B2 - Ultrasound Doppler diagnostic device - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an ultrasonic Doppler diagnostic apparatus for diagnosing the state of motion of a body fluid such as blood using the Doppler effect of ultrasonic waves received from a moving body.
In particular, the present invention relates to an ultrasonic Doppler diagnostic device capable of displaying a new index (index) indicating the motion state of the fluid.

[0002]

2. Description of the Related Art An ultrasonic Doppler diagnostic apparatus is a very wide-ranging apparatus because it can measure blood flow information such as blood flow velocity in a living body noninvasively and noninvasively.
Such an ultrasonic Doppler diagnostic apparatus mainly includes a so-called one-point Doppler method for measuring a blood flow velocity at an arbitrary set point in a living body and a so-called blood flow imaging method capable of displaying a blood flow state with a two-dimensional spread. It is used for Both the one-point Doppler technique and the blood flow imaging technique are similar in principle, that is, when the ultrasonic wave is reflected by a moving object, the frequency of the reflected wave shifts in proportion to the moving speed of the moving object. It was used. Various blood flow information such as blood flow velocity, variance and power can be calculated using the shift frequency due to the Doppler effect, and the state of the blood flow can be observed from various angles based on the blood flow information. it can. For example, the blood flow velocity V can be calculated from the shift frequency fd, the center frequency fc of the transmitted ultrasonic pulse, the angle θ between the ultrasonic beam and the blood vessel, and the sound velocity c according to the following equation. fd = 2 · fc · Vcos θ / c

[0003] In recent years, a new index has been proposed which provides a blood flow state in a more precise form in addition to the blood flow velocity, dispersion and power. One of the indexes is the Pulsatility Index PI
) This pulsarity index PI is an index quantifying the degree of change in blood flow velocity during one heartbeat, and reflects the peripheral circulation resistance of blood vessels, so that early detection of fetal growth failure in obstetrics and abdominal area Very effective information can be provided for the differential diagnosis of tumors in the medical field.

In order to measure the pulsarity index PI, first, a portion (sampling position) of a blood vessel to be measured is designated with reference to a B-mode image. This designation is made by operating an input device such as a trackball, for example.
This is performed while moving the sampling mark superimposed and displayed on the B-mode image. When the designation of the sampling position is completed, the Doppler spectrum obtained by performing the fast Fourier transform (FFT) on the received signal from the sampling position is displayed, for example, as shown in FIG. The operator freezes an appropriate spectrum, operates a trackball or the like, traces the waveform of the Doppler spectrum along the peak value, writes a peak line PL, and measures a time range, that is, a desired one heartbeat period, for example, Time t
When designated from 0 to t1, the pulsarity index PI of the sampling position is calculated according to the following equation. PI = (Fmax-Fmin) / Fmean Fmax: Maximum frequency of the peak line between times t0 and t1 Fmin: Minimum frequency of the peak line between times t0 and t1 Fmean: Average frequency of the peak line between times t0 and t1

[0005] The pulsatility index PI thus obtained reflects the peripheral circulatory resistance of blood vessels as described above, and is used for early detection of fetal growth deficiency in obstetrics and tumors in the abdominal region. Although it is very effective for the differential diagnosis of the above, the trace error of the peak line PL directly affects the pulsarity index PI, so that this trace requires a great deal of labor, time and skill. Further, in order to measure the pulsarity index PI at a plurality of sampling positions, the above operation has to be repeated many times, which poses a practical problem.

[0006]

SUMMARY OF THE INVENTION The present invention has been made in view of the above problems, and provides an index that quantifies the degree of variation of blood flow velocity over time with sufficient real-time performance. It is an object of the present invention to provide an ultrasonic Doppler diagnostic device capable of measuring by using a computer.

[0007]

In order to solve the above-mentioned object, the present invention provides an ultrasonic probe for transmitting and receiving ultrasonic waves to and from a living body, and an ultrasonic signal received by the ultrasonic probe. Means for obtaining speed information of the moving body in the living body at multiple points based on the speed information,
Means for generating a blood flow image based on the speed information, calculating a maximum speed and a minimum speed in at least one heartbeat period based on the speed information, and obtaining a pulsarity index from the maximum speed and the minimum speed at multiple points . The pal
The pulsarity index based on the salary index
Means for generating color two-dimensional distribution image related to index
And the color two-dimensional distribution image together with the blood flow image
Displaying means .

[0008]

According to the ultrasonic Doppler diagnostic apparatus of the present invention, the pulsarity index, that is, the index that quantifies the degree of fluctuation of blood flow velocity over time, can be sufficiently obtained from the maximum velocity and the minimum velocity in at least one heartbeat period. Measurement at multiple points under real-time performance
Color 2D distribution image of pulsarity index
The image can be displayed together with the blood flow image .

[0009]

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS A first embodiment of the present invention will be described below with reference to the drawings.

The apparatus of the present embodiment is configured as shown in FIG. That is, an electronic scanning ultrasonic probe (hereinafter, referred to as a “probe”) 11 includes a plurality of transducers arranged in parallel, and is driven by an electronic scanning device analog unit 12 to transmit an ultrasonic beam into a subject in a pulsar manner. And receives a reflected wave from a moving body (moving body) including blood cells in the subject. The electronic scanning device analog section 12 includes a preamplifier 13 for amplifying a reception signal, a pulser 14, an oscillator 15, and a delay line 16 for controlling a transmission / reception delay time for each transducer.
, An adder 17, and a detector 18 that obtains a B-mode signal by performing envelope detection on the output of the adder 17.

A scan conversion means (digital scan converter; DSC) 34 receives a B-mode signal from the detector 18 and shapes the signal into a B-mode image. The output of the scan conversion means 34 is supplied to the multiplexer 3 for controlling the display screen.
7, through the D / A (digital / analog) conversion means 38 in order, and is displayed on the display means 39 as a B-mode image.

On the other hand, the output of the adder 17 is
0 is also supplied to the mixers 24a and 24b. Along with this output, a reference signal fo from the oscillator 15 is supplied to the mixers 24a and 24b by a 90 ° phase shifter 25 with a phase shift of 90 °. The signals including the Doppler shift signal fd from the mixers 24a and 24b are subjected to low-pass filters 26a and 26b to remove high-frequency components, and the MTI
The data is supplied to the calculation unit 27.

This MTI (Moving Target Indicator)
The arithmetic unit 27 includes A / D converters 28a and 28b connected to the low-pass filters 26a and 26b, and an A / D converter 2
MTI filters 29a and 29b for inputting digital signals from 8a and 28b to remove noise from slow moving bodies and extract signals from blood cells, and MTI filters 29a and 29b
An autocorrelator 30 for inputting a signal from the device and measuring a Doppler signal, and various blood flow information using the Doppler signal; And a power calculation unit 33. The MTI calculation unit 27 is an application of a moving target indicating device developed and used mainly in the field of radar, and can detect only a specific moving target using the Doppler effect. The moving target here is “blood cells”. The autocorrelator 30 is a type of a frequency analysis device, and can perform multipoint frequency analysis of a two-dimensional area in real time.

The scan conversion means 35 receives the blood flow information from the MTI operation unit 27 and forms a two-dimensional image. The output of the scan conversion means 35 is taken into the color information change means 36,
Predetermined color processing is performed, and the multiplexer 37, D /
After passing through the A (digital / analog) conversion means 38 in order, the color blood flow distribution image is displayed on the display means 39. In performing the blood flow imaging, a computing unit that performs a fast Fourier transform process may be used instead of the MTI computing unit 27.

The index calculator 41 is a characteristic component of the present embodiment. The index calculator 41 receives the average speed V from the average speed calculator 31 of the MTI calculator 27 and is designated by using the average speed V. The pulsarity index PI is calculated for each of the multiple points in the area, and the scan conversion means 35
And supplied to the D / A conversion means 38, and displayed as a color two-dimensional distribution image of the pulsarity index PI as shown in FIG. 3 or as numerical data of a designated point. This pulsarity index PI is calculated according to the following equation (1). PI = (Vmax-Vmin) / Vmean (1)

Vmax is the maximum fluctuation speed of the average speed V continuously supplied from the average speed calculation unit 31 in the same fluctuation period, that is, a large number of average speeds V supplied in the same heartbeat period. And Vmin is its minimum speed. Vmean is an average value of a large number of average velocities V supplied during the heartbeat cycle. The fluctuation period may be detected based on the fluctuation of the average speed V, or may be obtained from an external heart rate measuring device. Further, the index calculating unit 41 may perform a process of determining a turn based on the temporal and spatial continuity of the average speed V and correcting the turn.
As described above, the pulsarity index PI is calculated using the output of the MTI calculation unit 27, whereby the pulsarity index PI can be obtained while maintaining a certain degree of real-time performance. And the state of its temporal change can be visually or quantitatively observed. Next, the calculation operation of the pulsarity index PI of the apparatus of the embodiment configured as described above will be described.

FIG. 2 is a diagram showing the output timing of the pulsarity index PI with respect to a change over time of the average speed V supplied from the average speed calculation unit 31 to the index calculation unit 41 for one sample point.

As shown in FIG. 2A, the average speed V is continuously supplied from the average speed calculation unit 31 to the index calculation unit 41 as a digital signal. At time t0
, T1, t2, t3... Indicate beat timing.

First, as soon as the first cycle (time t0 to t1) elapses, the index calculation unit 41 immediately sets the maximum speed Vmax of the number of average velocities V supplied in the first cycle.
And the minimum speed Vmin are detected, and the average value Vmean is calculated. Then, the first pulsarity index PI1 is calculated from Vmax, Vmin and Vmean according to the above equation (1), and the end time t1 of the cycle is calculated.
At time t1 ', which is a little later, the first pulsarity index PI1 becomes
It is supplied to the A conversion means 38. Similarly for the other sample points, the first pulsarity index PI1
Is calculated, and the scan conversion means 35 and the D / A conversion means 3
8 is supplied. Then, the first pulsarity index PI1 for many sample points is generated in the first two-dimensional distribution image by the scan conversion means 35, and color information is added by the color information conversion means 36 according to a predetermined color scale. Thus, a first color two-dimensional distribution image as shown in FIG. 3 is obtained, and the first color two-dimensional distribution image is supplied to the multiplexer 37. The first color two-dimensional distribution image waits for the display instruction of the observer, and the
From the display means 3 via the D / A conversion means 38
9 is displayed.

Similar processing is performed for the second period (time t1 to t2), and a second color two-dimensional distribution image is displayed instead of the first color two-dimensional distribution image. The same applies to the third period (time t2 to t3), the fourth period (time t3 to t4) and the subsequent periods, and the third color two-dimensional distribution image, the fourth color two-dimensional distribution image... Are sequentially switched. It is displayed while changing. As shown in FIG. 3, according to the color two-dimensional distribution image, an abnormal portion having a large fluctuation in blood flow velocity due to stenosis or the like is different from other normal portions in terms of hue or brightness.

As described above, according to the present embodiment, the pulsarity index PI can be calculated based on sufficient real-time performance, and its color two-dimensional distribution image can be displayed. Useful information can be provided.

[0022] Here, the index calculation unit 41 by averaging a plurality of pulse Sati Rithy index PI determined successively in time, a new one 1 <br/> Pal sati Rithy index PI of May be calculated, and the average speed (V) within a plurality of cycles is set as a measurement range of one pulsarity index PI, and Vmax and Vmin of the average speed (V) are detected therefrom, and The average (Vmean) may be obtained by adding and averaging the average velocities (V) within the plurality of periods, and then the pulsarity index PI may be calculated. A predetermined number of spatially adjacent pulsarity indexes P
A new pulsarity index PI may be calculated by averaging I.

In the method of detecting the fluctuation period (heartbeat period) in the above embodiment, the fluctuation period (heartbeat period) is detected from the state of fluctuation of the average speed V from the average speed calculation unit 31. The fluctuation cycle may be detected by using the electrocardiogram data.

In the above embodiment, the pulsarity index PI is calculated according to the above equation (1). However, this equation need not be limited to the equation (1).
Any formula that reflects the change in the blood flow velocity may be used. For example, the degree of the change in the average velocity V within a predetermined period is determined by the variance σ ² Or may be expressed by the following equations (2), (3), and (4). PI = (Vmax−Vmin) / Vmax (2) PI = Vmax−Vmin (3) PI = Vmax / | Vmin | (4)

In the above embodiment, the average speed calculating section 31
The pulsarity index PI is calculated using only the average speed V from the variance calculation unit 32 and the variance σ ² , The maximum speed vmax may be calculated once according to the following equation (5), and the maximum speed vmax may be handled in the same manner as the above-mentioned average speed V to calculate the pulsarity index PI. Vmax = V + 0.5σ ² … (5)

In the above embodiment, the method of converting the pulsarity index PI into a color signal by the color information conversion means 36 follows the level of the pulsarity index PI. The color signal may be converted according to a combination of the blood flow direction (positive or negative of the average velocity V) or the combination of the level of the pulsarity index PI and the average velocity V.

Further, the value of the pulsarity index PI at the position designated by the operator operating the marker on the color two-dimensional distribution image of the pulsarity index PI may be numerically displayed on the screen.

Further, the pixel value of the blood flow imaging image based on the conventional average velocity V is correlated with the value of the pulsarity index PI at the corresponding position. When the value is equal to or larger than the threshold, the brightness, hue, or saturation of each pixel may be changed in accordance with the threshold to highlight the pixel. The threshold level at this time may be adjusted automatically or manually.

Further, as shown in FIG. 4, if the color two-dimensional distribution image IPI of the pulsarity index PI is divided and displayed together with the blood flow imaging image Ic, the two can be easily compared with each other. Performance can be improved. Next, a second embodiment will be described. FIG. 5 is a block diagram illustrating the configuration of the present embodiment.
Note that the same parts in FIG. 5 and FIG.
Detailed description is omitted.

As can be seen from a comparison between FIG. 5 and FIG. 1, the present embodiment has a spectrum Doppler section 70 for a so-called one-point Doppler, and uses this output to generate a pulsarity index PI. Is calculated. Hereinafter, the configuration and output of the spectrum Doppler unit 70 will be briefly described.

As shown in FIG. 8, the spectrum Doppler unit 70 operates an input device such as a trackball or a mouse on the B-mode image IB to change the positions of the sampling lines SL and the sample points SP and the width of the sample volume SV. When set, a signal corresponding to the shift frequency due to the Doppler effect from within that range (hereinafter referred to as “Doppler signal”)
Is output. Therefore, the spectrum Doppler unit 70
Are gated to the outputs of the low-pass filters 26a and 26b at timings corresponding to the depths of the sample points to hold the signals from the sample volume SV, and the sample hold units 71a and 71b. High-pass filters 72a and 72b for removing low-frequency components and low-pass filters 73a and 73b for removing high-frequency components in order to extract only the blood flow component from the signal of the sample volume SV input from the sampler SV.
, Amplifiers 74a and 74b for amplifying the outputs of the low-pass filters 73a and 73b, and A / D converters 75a and 75
5b and a high-speed Fourier transformer (FF) for performing a Fourier transform as a frequency analysis by inputting the received signals converted into complex signals output from the A / D converters 75a and 75b.
T) 76. The output of the fast Fourier transformer 76 is, for example, as shown in FIG. 6A, a Doppler signal corresponding to the shift frequency due to the Doppler effect of the sample point. , Supplied to the index calculation unit 61,
The calculation result, that is, the pulsarity index PI is displayed on the display means 39 via the D / A converter 38 as shown in FIG.
Numerical values are displayed as shown in.

Next, the index calculator 42 will be described. The index calculating unit 42 is a processing unit for calculating the pulsarity index PI, as in the first embodiment. However, while the first embodiment uses the output signal of the MTI processing unit 27, Since the output of the spectrum Doppler unit 70 is used in the example, the index calculation unit 42 traces the waveform of the Doppler signal from the spectrum Doppler unit 70 as shown in FIG. Then, a frequency line FL similar to the conventional peak line is created. This trace, for example, traces the highest frequency of each spectrum.

Using this frequency line FL, similarly to the first embodiment, its fluctuation period (heartbeat period) is detected, and the maximum value Fmax and the minimum value Fmin of the frequency line FL within the same period are detected. The average value Fmean within the cycle is calculated, and using these, the following equation (6) similar to the above-described equation (1) is used.
Is calculated according to the following equation. PI = (Fmax-Fmin) / Fmean (6) In this manner, the pulsarity index PI can be calculated from the output of the spectrum Doppler unit 70. Next, the calculation operation of the pulsarity index PI of the apparatus of the embodiment configured as described above will be described.

FIG. 6 is a diagram showing the output timing of the pulsarity index PI with respect to the change over time of the Doppler signal supplied from the spectrum Doppler unit 70 to the index calculation unit 42 for a certain sample point SP designated by the operator. FIG. 7 is a diagram showing an example of the ultrasonic transmission timing for the pulsarity index PI with respect to the ultrasonic transmission timing for blood flow imaging.

[0035] As shown in FIG. 7 (a), this blood flow Image
When the sample point SP and sample volume SV on a desired position on managing image Ru set Teisu, transmission and reception operations of the ultrasonic beam by electronic scanning devices analog section 12 as shown in FIG. 7 (b), as a reference signal In synchronization with the ultrasonic pulse, an ultrasonic pulse for blood flow imaging and an ultrasonic pulse for the pulsarity index PI are transmitted alternately. The ultrasonic pulse for blood flow imaging is
For example, scanning is performed while changing the direction from A to Z every four transmissions / receptions, while the ultrasonic pulse for the pulsarity index PI is transmitted in the same direction C.
The received signals obtained by the ultrasonic pulses for blood flow imaging are combined for each direction, that is, arithmetic processing is performed by the MTI arithmetic unit 27 every four pulses, and blood flow imaging data for one scanning line is created. The received signal obtained by the ultrasonic pulse for the pulsarity index PI is combined into a predetermined number of pulses, for example, every 64 pulses, and is subjected to the fast Fourier operation of the spectrum Doppler unit 70. The frequency is analyzed by the unit 76 and is continuously supplied to the index calculating unit 42.

As shown in FIG. 6A, the Doppler signal is continuously supplied to the index calculation unit 42 from the fast Fourier calculation unit 76. Note that at times t0, t1, t2,
t3... indicate beat timing.

First, as soon as the first cycle (time t0 to t1) has elapsed, the frequency line FL of the Doppler signal supplied in the first cycle is traced by the index calculator 42, and the maximum frequency within the first cycle is traced. The value Fmax and the minimum value Fmin are detected, and the average value Fmean is calculated. Then, the first pulsarity index PI1 is calculated using Fmax, Fmin, and Fmean according to the above equation (6), and the first pulse at a time t1 '' slightly delayed from the end time t1 of the cycle. The satellite index PI1 is supplied to the D / A conversion means 38, and its value is displayed on the display means 39 as shown in FIG.

The same processing is performed after the second cycle (time t1 to t2), and the display is switched to the currently displayed pulsarity index PI in synchronization with the completion of the calculation of the pulsarity index PI. The operator
The blood flow state at the designated sample point can be inferred from the value of the pulsarity index PI and how the value changes.

As described above, according to the present embodiment, the pulsarity index PI of a desired sample point can be calculated from the result of the fast Fourier operation based on sufficient real-time performance, and the diagnosis of the blood flow state can be performed. Useful information can be provided.

Although the pulsarity index PI is numerically displayed in the second embodiment, the display method may be changed as appropriate. For example, as shown in FIG. Is displayed over time, or the level scale L is displayed as shown in FIG.
The value of S may be indicated by an arrow Y.

The index calculator 42 may average a plurality of pulsarity indices PI obtained successively in time to calculate a new pulsarity index PI. Alternatively, a Doppler signal within a plurality of cycles may be used as the measurement range of one pulsarity index PI.

In the second embodiment, the method of detecting the fluctuation cycle (heart rate cycle) is based on the state of the fluctuation of the frequency line of the Doppler signal. This fluctuation cycle may be detected by using data.

In the above embodiment, the pulsarity index PI is calculated in accordance with the above equation (6). However, this equation need not be limited to the equation (6).
Any expression that reflects the change in the blood flow velocity may be used. For example, the degree of the change in the frequency line within a predetermined period is represented by the variance σ ² Or may be expressed by the following equations (7), (8), and (9). PI = (Fmax−Fmin) / Fmax (7) PI = Fmax−Fmin (8) PI = Fmax / | Fmin | (9)

In the above embodiment, the frequency line is obtained by tracing the highest frequency of each spectrum of the Doppler signal. However, the frequency line may be obtained by tracing the average frequency of each spectrum. Ingredient (Fo
rward), reverse flow (Reverse), or all components (Net), or the detected maximum frequency is corrected manually or automatically by a flow angle or aperture length that is set automatically. It may be.

In the above embodiment, the ultrasonic pulse for blood flow imaging was transmitted between the ultrasonic pulses for the pulsarity index, and a blood flow imaging image was obtained together with the pulsarity index. An ultrasonic pulse for a B-mode image may be transmitted instead of an ultrasonic pulse for flow imaging to obtain a B-mode image together with a pulsarity index, or an ultrasonic pulse for a pulsarity index may be transmitted. At times, the transmission of the ultrasonic pulse for the blood flow imaging or the ultrasonic pulse for the B-mode image may be stopped, and only the transmission of the ultrasonic pulse for the pulsarity index may be performed. Next, a third embodiment will be described.
FIG. 10 is a block diagram illustrating the configuration of the present embodiment. The same parts as those in FIG. 10 and FIG.
Detailed description is omitted.

In the present embodiment, as in the second embodiment, a sample point SP is set, and the pulsarity index PI of the sample point SP is calculated. In this embodiment, similarly to FIG. 7B of the second embodiment, the ultrasonic pulse for blood flow imaging and the ultrasonic pulse for the pulsarity index PI are transmitted alternately, and The reception signal obtained by the ultrasonic pulse for blood flow imaging and the reception signal obtained by the ultrasonic pulse for the pulsarity index PI are separately processed. The received signal obtained by the ultrasonic pulse for blood flow imaging is summarized for each direction,
Here, the MTI calculation unit 27 performs a calculation process every four pulses to create blood flow imaging data for one scanning line,
It is sent to the scan conversion means 35. On the other hand, the received signals obtained by the ultrasonic pulses for the pulsarity index PI are grouped every predetermined number of pulses, for example, every 64 pulses, and are processed by the MTI calculation unit 27. The speed V is calculated by the index calculation unit 43
Supplied continuously.

The index calculator 43 inputs the average speed V for the designated sample point, detects the heartbeat cycle, and, as in the first embodiment, calculates a number of average speeds supplied within the same heartbeat cycle. V, the maximum speed Vmax and the minimum speed Vmin are detected, and the average value Vmean of the average speed V is detected.
Are calculated and the pulsarity index PI is calculated according to the above equation (1). This pulsarity index PI is displayed on the display means 39 as in FIGS. 8 and 9. As described above, according to the present embodiment, similarly to the second embodiment, the pulsarity index PI for a desired sample point can be calculated and displayed.

The index calculating unit may calculate a new pulsarity index PI by averaging a plurality of pulsarity indexes PI obtained successively in time. Using the average speed (V) within a plurality of cycles as a measurement range of one pulsarity index PI, Vmax and Vmin of the average speed (V) are detected therefrom, and the average speed (V) within the plurality of cycles is detected. May be added and averaged to obtain an average (Vmean), and then the pulsarity index PI may be calculated.

In the method of detecting the fluctuation cycle (heart rate cycle) in the above embodiment, the fluctuation is detected from the state of fluctuation of the average speed V from the average speed calculation unit 31. The fluctuation cycle may be detected by using the electrocardiogram data.

In the above embodiment, the pulsarity index PI is calculated in accordance with the above equation (1). However, this equation need not be limited to the equation (1). may be a formula, as reflected, for example, the variance sigma ² the degree of variation of the average speed V in a predetermined time period , Or may be the above equations (2), (3), and (4).

In the above embodiment, the average speed calculating section 31
The pulsarity index PI is calculated using only the average speed V from the variance calculation unit 32 and the variance σ ² May be used to calculate the maximum speed vmax once in accordance with the above equation (5), and treat the maximum speed vmax in the same manner as the above average speed V to calculate the pulsarity index PI.

The average velocity V supplied to the index calculating section 43 is calculated by the MTI calculating section 27 for each predetermined number of ultrasonic pulses for the pulsarity index PI, as shown in FIG. Alternatively, the calculation target may be shifted as shown in FIG.

Further, as shown in FIG. 12, the transmission timing of the ultrasonic pulse for blood flow imaging and the ultrasonic pulse for the pulsarity index PI is set to the number of times necessary for one scanning line of blood flow imaging. The transmission / reception operation for the blood flow imaging may be performed by freezing the transmission / reception of the ultrasonic pulse as many times as necessary to calculate the pulsarity index PI at the transmission / reception interval of the sound pulse. May be interrupted to perform only the transmission / reception operation for the pulsarity index PI. Next, a fourth embodiment will be described. FIG. 13 or FIG. 14 is a block diagram showing the configuration of the present embodiment. The same parts as those in FIG. 1 or FIG. 5 are denoted by the same reference numerals, and detailed description is omitted.

In this embodiment, as shown in FIGS. 13 and 14, the average speed calculator 31 and the spectrum Doppler 70 of the MTI calculator 27 are each provided with an index calculator 44 for performing a fast Fourier transform (FFT). This is a configuration in which the above-described frequency line tracing process and the index calculation unit 45 that performs the fast Fourier transform process (FFT) on the frequency line are connected. By expressing the frequency line or the waveform of the average speed V on the frequency axis, It is possible to output an index according to the fluctuation of the frequency line or the waveform of the average speed V. According to this embodiment, the same effects as those of the first and second embodiments can be obtained.

As described above, according to the ultrasonic Doppler diagnostic apparatus according to the present embodiment, the index representing the time change of the Doppler shift frequency with the passage of time or the color 2 of the index.
The dimensional distribution image can be displayed together with the blood flow imaging image and the tomographic image, so that abnormalities in blood flow dynamics can be easily found, and diagnostic performance can be improved. The present invention is not limited to the above embodiment, but can be implemented with various modifications without departing from the spirit of the invention.

[0056]

As described above, according to the present invention, the pulsarity index, that is, an index that quantifies the degree of fluctuation of blood flow velocity over time, from the maximum velocity and the minimum velocity in at least one heartbeat period, is obtained. Measurements at multiple points with sufficient real-time performance
Blood flow drawing of color two-dimensional distribution image related to e-index
Since it can be displayed together with the image , abnormalities in blood flow dynamics can be easily found.

[Brief description of the drawings]

FIG. 1 is a block diagram showing a configuration of a first embodiment.

FIG. 2 is a view for explaining the operation of an index calculation unit shown in FIG. 1;

FIG. 3 is a view showing an example of a two-dimensional distribution image of a pulsarity index displayed on the display means shown in FIG. 1;

FIG. 4 is a diagram showing a divided display of a two-dimensional distribution image of a pulsarity index and a blood flow imaging image shown in FIG. 3 as an example of a display method of the display means shown in FIG. 1;

FIG. 5 is a block diagram showing a configuration of a second embodiment.

FIG. 6 is a view for explaining the operation of the index calculator shown in FIG. 5;

FIG. 7 is a diagram showing an example of ultrasonic transmission / reception timing for a pulsarity index.

FIG. 8 is a view showing a display example of a pulsarity index displayed on the display means shown in FIG. 5;

FIG. 9 is a view showing another display example of the pulsarity index displayed on the display means shown in FIG. 5;

FIG. 10 is a block diagram showing a configuration of a third embodiment.

FIG. 11 is a diagram illustrating an example of a calculation target range of the MTI calculation unit illustrated in FIG. 10;

FIG. 12 is a diagram showing an example of ultrasonic transmission / reception timing for a pulsarity index.

FIG. 13 is a block diagram showing one configuration of a fourth embodiment.

FIG. 14 is a block diagram showing another configuration of the fourth embodiment.

FIG. 15 is a view for explaining a conventional pulsarity index calculation method.

[Explanation of symbols]

11: Probe, 12: Analog section of electronic scanning device, 24
a, 24b: mixer, 26a, 26b: low-pass filter, 27: MTI calculation unit, 41: index calculation unit,
34, 35: scanning conversion means, 36: color information changing means, 37: multiplexer, 38: D / A conversion means, 3
9 Display means.

Continuation of the front page (56) References JP-A-5-95947 (JP, A) JP-A 5-200025 (JP, A) Katsuhide Endo, "Fetal management by umbilical artery blood flow velocity waveform analysis", Keio Medical 1989, Vol. 66, No. 2, pp. 433-443 (58) Fields investigated (Int. Cl. ⁷ , DB name) A61B 8/00-8/15 JICST file (JOIS)

Claims (4)

(57) [Claims] Respect 1. A vivo ultrasonic probe for transmitting and receiving ultrasonic waves, on the basis of the ultrasonic signal reception by the ultrasound probe, multi-speed information of the moving body in said in vivo Point snow
Means for determining standing, means for generating a blood flow image based on the speed information, obtains the maximum speed and the minimum speed at least one heartbeat period on the basis of the speed information, pulser Rithy from this maximum speed and minimum speed Means for determining an index at multiple points, and the pulsarity index based on the pulsarity index.
Generate color 2D distribution image for tea index
Means for displaying the two-dimensional color distribution image together with the blood flow image
An ultrasonic Doppler diagnostic apparatus comprising: 2. The ultrasonic Doppler diagnostic apparatus according to claim 1, wherein the pulsarity index is a difference between the maximum speed and the minimum speed. 3. The pulsarity index according to claim 1, wherein a difference between the maximum speed and the minimum speed is normalized by an average speed or a maximum speed in the heartbeat period. Acoustic Doppler diagnostic device. 4. The ultrasonic Doppler diagnostic apparatus according to claim 1, wherein the pulsarity index is a ratio between the maximum speed and the minimum speed.